Subjective eye examination device

Abstract

The subjective ophthalmological examination device includes a subjective measurement unit and an objective measurement unit. The subjective measurement unit subjectively measures the optical characteristics of the eye to be examined and includes: a light projection optical system that projects a sight mark beam toward the eye to be examined; a corrective optical system that includes a right-eye corrective optical system and a left-eye corrective optical system arranged as a pair of left and right parts and is disposed in an optical path of the light projection optical system to change the optical characteristics of the sight mark beam; an optical component that is shared by the right-eye optical path including the right-eye corrective optical system and the left-eye optical path including the left-eye corrective optical system and that guides the sight mark beam corrected by the corrective optical systems toward the eye to be examined; the objective measurement unit includes a measurement optical system that emits measurement light toward the fundus of the eye to be examined and receives reflected light from the fundus. The objective measurement unit objectively measures the optical characteristics of the eye to be examined via the optical component disposed in the optical path of the measurement optical system.

Description

[0001] This application is a divisional application of patent application No. 201610959315.8, filed on November 3, 2016, and entitled “Subjective Eye Examination Device.” Technical Field

[0002] The present invention relates to a subjective eye examination device. Background Art

[0003] Subjective ophthalmology devices, for example, subjectively measure the optical characteristics of the eye being examined. In the subjective ophthalmology device disclosed in Japanese Patent Laid-Open No. 5-176893, for example, a corrective optical system capable of adjusting the diopter is separately arranged in front of the eye of the examinee. Using the light projected by the corrective optical system, an image of the inspection target is formed on the fundus of the eye being examined. Upon receiving the examinee's response, the examiner adjusts the corrective optical system until the examinee can properly see the target, thereby determining the correction value. The examiner measures the refractive power of the eye being examined based on this correction value. Furthermore, in the subjective ophthalmology device disclosed in U.S. Patent No. 3,874,774, for example, an image of the inspection target is formed in front of the eye of the examinee via the corrective optical system. In this device, the refractive power of the eye being examined is measured without placing the corrective optical system in front of the eye.

[0004] When measuring the optical properties of the subject's eye, if a device is used that places a portion of the device in front of the eye, the subject's eye may adjust to the portion of the device placed in front of the eye, resulting in reduced measurement accuracy. Therefore, when measuring the optical properties of the subject's eye, it is preferable to measure the optical properties through subjective measurement in a natural state (open state without the device portion placed in front of the eye), as the subject observes objects in daily life, or through objective measurement. Summary of the Invention

[0005] An object of the present invention is to provide a subjective eye examination apparatus that can perform subjective and objective measurements in a natural state and can perform measurements with high accuracy.

[0006] Furthermore, in previous subjective ophthalmology devices, optical aberrations were generated by the various components that comprised the device. Therefore, corrections were made to these aberrations. However, when subjectively measuring the optical characteristics of the eye being examined, optical aberrations vary depending on the measurement conditions (e.g., ocular refractive power, examination distance, and angle of convergence). Therefore, using a constant correction amount for optical aberrations can make it difficult to suppress these aberrations.

[0007] Another object of the present invention is to provide a subjective eye examination apparatus that can suppress optical aberrations and measure the optical characteristics of an eye to be examined with high accuracy.

[0008] Furthermore, in subjective ophthalmology devices, the action of adjusting the positional relationship between the examined eye and the subjective ophthalmology device (calibration) is particularly important when subjectively measuring the optical characteristics of the examined eye. For example, if the calibration action is not performed properly, the accuracy of the measurement results of the optical characteristics of the examined eye may be reduced when the optical characteristics of the examined eye are subjectively measured. Furthermore, for example, there are cases where adjusting the positional relationship between the examined eye and the subjective ophthalmology device is time-consuming. In such cases, the calibration action may not be performed efficiently when subjectively measuring the optical characteristics of the examined eye.

[0009] Another object of the present invention is to provide a subjective eye examination apparatus that can accurately measure the optical characteristics of an eye under examination while subjectively measuring the optical characteristics of the eye under examination. Furthermore, the subjective eye examination apparatus can efficiently perform a calibration operation.

[0010] To achieve the above-mentioned object, a subjective ophthalmological examination device according to a first embodiment of the present invention comprises: a subjective measurement unit having a light-projecting optical system, a corrective optical system, and an optical component, and subjectively measuring the optical characteristics of an eye to be examined, wherein the light-projecting optical system projects a target light beam toward the eye to be examined, the corrective optical system having a right-eye corrective optical system and a left-eye corrective optical system arranged as a pair on the left and right, and being arranged in an optical path of the light-projecting optical system, and changing the optical characteristics of the target light beam, the optical component being shared by the right-eye optical path including the right-eye corrective optical system and the left-eye optical path including the left-eye corrective optical system, and guiding the target light beam corrected by the corrective optical system toward the eye to be examined; and an objective measurement unit having a measurement optical system that emits measurement light toward the fundus of the eye to be examined and receives reflected light from the fundus, and objectively measuring the optical characteristics of the eye to be examined via the optical component arranged in the optical path of the measurement optical system.

[0011] A second aspect of the subjective ophthalmological apparatus is the subjective ophthalmological apparatus of the first aspect, wherein an optical axis between the optical component and the examined eye in the subjective measurement section and an optical axis between the optical component and the examined eye in the objective measurement section are coaxial.

[0012] The subjective ophthalmological apparatus of the third embodiment is based on the subjective ophthalmological apparatus of the first embodiment, wherein the optical component includes a concave mirror, and the subjective measuring section guides the visual target light beam corrected by the corrective optical system toward the eye to be examined by reflecting the visual target light beam toward the eye to be examined by the concave mirror, and guides the image of the visual target light beam corrected by the corrective optical system toward the eye to be examined in such a manner that the distance between the formation position of the image detected by the examinee and the eye to be examined becomes an optically prescribed inspection distance.

[0013] The subjective ophthalmological apparatus of the fourth embodiment is, in addition to the subjective ophthalmological apparatus of the first embodiment, further comprising: an offset detection unit for detecting a positional offset of the image of the corrective optical system relative to the eye to be examined; a deflection member disposed between the corrective optical system and the eye to be examined, the deflection member being provided as a left and right pair; a drive unit for driving the deflection member; and a correction unit for optically correcting the formation position of the image by controlling the drive unit based on a detection result detected by the offset detection unit.

[0014] The subjective ophthalmological apparatus of the fifth embodiment is further provided with, in addition to the subjective ophthalmological apparatus of the first embodiment, a correction setting unit that sets a correction amount for correcting the optical aberration generated in the subjective measurement unit based on the correction power of the corrective optical system; and an aberration correcting unit that corrects the optical aberration generated in the subjective measurement unit based on the correction amount set by the correction setting unit.

[0015] The subjective ophthalmological apparatus of the sixth embodiment is further provided with, in addition to the subjective ophthalmological apparatus of the first embodiment, a control unit that changes the presentation distance of the sight mark generated by the sight mark light beam by changing the formation position of the image of the sight mark light beam; a correction setting unit that sets a correction amount for correcting the optical aberration generated in the subjective measurement unit based on the presentation distance; and an aberration correction unit that corrects the optical aberration generated in the subjective measurement unit based on the correction amount set by the correction setting unit.

[0016] The subjective ophthalmological apparatus of the seventh embodiment is further provided with, in addition to the subjective ophthalmological apparatus of the first embodiment, a convergence angle changing unit that changes the convergence angle of the above-mentioned sight mark light beam emitted from the above-mentioned right-eye optical path and the above-mentioned left-eye optical path; a correction setting unit that sets a correction amount for correcting the optical aberration generated in the above-mentioned subjective measurement unit based on the above-mentioned convergence angle; and an aberration correcting unit that corrects the above-mentioned optical aberration generated in the above-mentioned subjective measurement unit based on the above-mentioned correction amount set by the above-mentioned correction setting unit.

[0017] The subjective ophthalmological examination device of the eighth embodiment is based on the subjective ophthalmological examination device of the fifth embodiment and further includes: a judgment unit that judges whether an auxiliary optical component is needed based on the eye refractive power obtained by the above-mentioned objective measurement unit; and a control insertion and removal unit that controls the insertion or removal of the above-mentioned auxiliary optical component in the optical path of the above-mentioned subjective measurement unit based on the judgment result of the above-mentioned judgment unit.

[0018] The subjective ophthalmological examination device of the 9th embodiment is based on the subjective ophthalmological examination device of the 5th embodiment and further includes: a judgment unit, which judges whether auxiliary optical components are needed based on the eye refractive power obtained by the above-mentioned objective measurement unit; and a display unit, which displays report information based on the judgment result of the above-mentioned judgment unit on a monitor.

[0019] The subjective ophthalmological examination device of the tenth embodiment is further provided with, in addition to the subjective ophthalmological examination device of the first embodiment, an acquisition unit for acquiring the objectively measured refractive power of the above-mentioned examined eye; and a setting unit for setting a calibration allowable range for determining the calibration status of the above-mentioned examined eye and the above-mentioned subjective measurement unit based on the above-mentioned refractive power. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] Figure 1 This is an external view of the subjective eye examination device according to this embodiment.

[0021] Figure 2 A diagram for explaining the structure of a measuring unit.

[0022] Figure 3 This is a schematic diagram showing the internal structure of the subjective eye examination apparatus according to the present embodiment as viewed from the front.

[0023] Figure 4 This is a schematic diagram showing the internal structure of the subjective eye examination apparatus according to the present embodiment as viewed from the side.

[0024] Figure 5 This is a schematic diagram showing the internal structure of the subjective eye examination apparatus according to the present embodiment as viewed from above.

[0025] Figure 6 This figure shows an example of a situation where a sight mark is presented at a distance.

[0026] Figure 7 This figure shows an example of a situation where a sight mark is presented at near distance.

[0027] Figure 8A as well as Figure 8B A diagram for explaining a change in the distance between optical axes caused by the movement of the deflecting mirror.

[0028] Figure 9 The anterior segment observation screen displays an anterior segment image captured by the imaging element.

[0029] Figure 10 A diagram for explaining calibration control.

[0030] Figures 11A to 11C This is a diagram for explaining changes in the calibration allowable range.

[0031] Description of Reference Numerals

[0032] 1 Subjective eye examination device

[0033] 2 Frame

[0034] 3 Presentation Window

[0035] 4 monitors

[0036] 5. Chin Rest

[0037] 6 abutment

[0038] 7 Measurement Unit

[0039] 10 Objective measurement optical system

[0040] 25 Subjective Measurement Optical System

[0041] 30 Light projection optical system

[0042] 45 No. 1 logo projection optical system

[0043] 46. Second logo projection optical system

[0044] 50 Observation Optical System

[0045] 60 Corrective Optical System

[0046] 70 Control Department

[0047] 72 Memory

[0048] 81 Deflecting mirror

[0049] 84 Half-transparent half-reflective mirror

[0050] 85 Concave Mirror

[0051] 90 Corrected Optical System

[0052] 100 Shooting Optical System

[0053] In the following detailed description, for purposes of illustration, numerous specific details are set forth in order to provide a thorough understanding of the disclosed embodiments. However, it will be apparent that one or more embodiments may be practiced without these specific details. In other instances, well-known structures and devices are schematically shown for simplicity of drawing. DETAILED DESCRIPTION

[0054] In the following detailed description, for ease of explanation, numerous specific details are set forth to provide a deeper understanding of the disclosed embodiments. However, it is apparent that one or more embodiments can still be implemented without these specific details. In addition, known structures and devices are schematically illustrated to simplify the drawings.

[0055] Hereinafter, one of the typical embodiments will be described with reference to the accompanying drawings. In addition, in the following description, the depth direction of the subjective eye examination device 1 (the front-to-back direction of the subject when the subject is being measured) is set as the Z direction. The horizontal direction on the plane perpendicular to the depth direction (the left-right direction of the subject when the subject is being measured) is set as the X direction. Furthermore, the vertical direction (the up-down direction of the subject when the subject is being measured) is set as the Y direction. In addition, R marked in the following figure marks indicates the right eye, and L indicates the left eye.

[0056] Figure 1 This is an external view of the subjective eye examination device 1 of this embodiment. The subjective eye examination device 1 of this embodiment includes a housing 2, a presentation window 3, an operation unit (monitor) 4, a chin rest 5, a base 6, and an imaging optical system 100. For example, the housing 2 accommodates components. For example, the housing 2 includes a right eye measurement unit 7R and a left eye measurement unit 7L ( Figure 1 (Details will be described later.) Hereinafter, when there is no need to distinguish between the right-eye measurement unit 7R and the left-eye measurement unit 7L, they may be collectively referred to as the measurement unit 7. In this embodiment, the right-eye measurement unit 7R and the left-eye measurement unit 7L have identical components. That is, the subjective eye examination apparatus 1 includes a pair of left and right subjective measurement units and a pair of left and right objective measurement units. Of course, the right-eye measurement unit 7R and the left-eye measurement unit 7L may differ in at least some of their components.

[0057] For example, the presentation window 3 is used to present an optotype to the examinee. For example, the optotype light beams from the right eye measurement unit 7R and the left eye measurement unit 7L are directed to the right eye ER and the left eye EL (see FIG. Figure 3 ) projection. In the following text, when there is no need to distinguish between the right eye ER and the left eye EL, they may be collectively referred to as the examined eye E.

[0058] For example, the monitor (display) 4 is a touch panel. That is, in this embodiment, the monitor 4 functions as an operating unit. The monitor 4 outputs a signal corresponding to the input operation instruction to the calculation control unit 70 described later. Of course, the monitor 4 and the operating unit can also be provided separately. For example, the operating unit can use at least one of a mouse, a joystick, a keyboard, and other operating units.

[0059] For example, the monitor 4 may be a display mounted on the main body of the subjective ophthalmological apparatus 1 or a display connected to the main body of the subjective ophthalmological apparatus 1. Of course, the monitor 4 does not have to be a touch panel. For example, a display of a personal computer (hereinafter referred to as a "PC") may be used as the monitor 4. Furthermore, for example, multiple displays may be used simultaneously as the monitor 4. For example, the measurement results may be displayed on the monitor 4.

[0060] For example, the chin rest 5 is used to maintain a constant distance between the eye to be examined E and the subjective ophthalmology apparatus 1, or to suppress large facial deviations. For example, the chin rest 5 and the housing 2 are fixed to the base 6. Furthermore, in this embodiment, the chin rest 5 is used to maintain a constant distance between the eye to be examined E and the subjective ophthalmology apparatus 1. However, the structure for maintaining a constant distance between the eye to be examined E and the subjective ophthalmology apparatus 1 is not limited to the chin rest 5. Examples of structures for maintaining a constant distance between the eye to be examined E and the subjective ophthalmology apparatus 1 include a forehead pad and a face rest.

[0061] For example, the photographing optical system 100 includes an imaging element and a lens (not shown). For example, the photographing optical system 100 is used to photograph the face of the eye to be examined.

[0062] <Measurement Department>

[0063] Figure 2 This figure illustrates the structure of the measurement unit 7. In this embodiment, the left-eye measurement unit 7L is used as an example. In this embodiment, the right-eye measurement unit 7R and the left-eye measurement unit 7L have the same structure, so their description is omitted. For example, the left-eye measurement unit 7L includes a subjective measurement optical system 25, an objective measurement optical system 10, a first index projection optical system 45, a second index projection optical system 46, and an observation optical system 50.

[0064] <Subjective measurement optical system>

[0065] For example, the subjective measurement optical system 25 is used as part of the structure of a subjective measurement unit that subjectively measures the optical characteristics of the eye under examination (details will be described later). Examples of the optical characteristics of the eye under examination include ocular refractive power, contrast sensitivity, and binocular visual acuity (e.g., strabismus and stereoscopic vision). Furthermore, in this embodiment, a subjective measurement unit that measures the refractive power of the eye under examination is described as an example. For example, the subjective measurement optical system 25 includes a light projection optical system (visual target projection system) 30, a correction optical system 60, and a correction optical system 90.

[0066] For example, the light projection optical system 30 projects a sight mark beam toward the inspected eye E. For example, the light projection optical system 30 includes a display 31, a light projection lens 33, a light projection lens 34, a reflector 36, a dichroic mirror 35, a dichroic mirror 29, and an objective lens 14. For example, the sight mark beam projected from the display 31 is projected toward the inspected eye E via a plurality of optical components, namely, the light projection lens 33, the light projection lens 34, the reflector 36, the dichroic mirror 35, the dichroic mirror 29, and the objective lens 14 in sequence.

[0067] For example, an inspection target such as a Rondo ring target is displayed on the display 31, or a fixation target (for example, when used in objective measurements described later) is displayed to help the examinee's eye E fixate its gaze. For example, a target light beam from the display 31 is projected toward the examinee's eye E. For example, an LCD (Liquid Crystal Display) or an organic EL (ElectroLuminescence) display is used as the display 31. In this embodiment, the following description uses an LCD as the display 31 as an example.

[0068] Furthermore, in the present embodiment, a display 31 is used as a light source for projecting an optotype light beam. However, the light source is not limited to the display 31. The light source only needs to be configured to project an optotype light beam. For example, a DMD (Digital Micromirror Device) can be used as the light source. Generally speaking, a DMD has a high reflectivity and is brighter. Therefore, compared with the case of using a display (liquid crystal display) 31 that uses polarized light, the light amount of the optotype light beam can be maintained. In addition, the light source can be, for example, a structure having a visible light source for presenting an optotype and an optotype plate having a fixation target. In this case, for example, the optotype plate is a rotatable disk plate having a plurality of optotypes. The plurality of optotypes include, for example, a fixation target for fogging the examinee's eye E during the objective measurement described later, and an optotype for visual acuity testing used during subjective measurement. For example, as an optotype for visual acuity testing, an optotype for each visual acuity value (marks corresponding to visual acuity values 0.1, 0.3, . . . , 1.5) is prepared. For example, the sight mark plate is rotated by a motor or the like to switch the sight mark arrangement on the optical axis L2 of the light projection optical system 30. The sight mark light beam representing the sight mark illuminated by the visible light source is emitted to the eye E to be examined via the optical components from the light projection lens 33 to the dichroic mirror 29.

[0069] For example, the corrective optical system 60 includes an astigmatism corrective optical system 63 and a drive mechanism 39 .

[0070] For example, the astigmatism correction optical system 63 is arranged between the projection lens 34 and the projection lens 33. For example, the astigmatism correction optical system 63 is used to correct the sight mark beam according to the cylindrical power and cylindrical axis of the eye to be examined. For example, the astigmatism correction optical system 63 has two positive cylindrical lenses 61a and 61b with equal focal lengths. The cylindrical lenses 61a and 61b are independently rotated around the optical axis L2 by the drive of the rotation mechanisms 62a and 62b, respectively. In addition, in this embodiment, as an example, the astigmatism correction optical system 63 having two positive cylindrical lenses 61a and 61b is shown. However, the astigmatism correction optical system 63 is not limited to this. The astigmatism correction optical system 63 only needs to be configured to correct the sight mark beam according to the cylindrical power and cylindrical axis of the eye to be examined. The astigmatism correction optical system 63 can be configured, for example, to move the correction lens out of or into the optical path of the projection optical system 30.

[0071] For example, the display 31 is moved integrally along the direction of the optical axis L2 by a driving mechanism 39 including a motor and a sliding mechanism. For example, during subjective measurement, the display 31 is moved to optically change the presentation position (presentation distance) of the sight mark relative to the eye under examination. As a result, the sight mark light beam is corrected according to the spherical refractive power (spherical power) of the eye under examination. That is, the spherical power correction optical system includes a movable display 31. In addition, for example, during objective measurement, the display 31 is moved to cause the eye under examination E to be fogged. In addition, the spherical power correction optical system is not limited to the above-mentioned structure. For example, the spherical power correction optical system can have a plurality of optical elements and correct the sight mark light beam by configuring the optical elements in the optical path. In addition, the spherical power correction optical system can, for example, move a lens configured in the optical path along the optical axis direction.

[0072] In this embodiment, as an example, a corrective optical system is shown that corrects the sight mark beam based on the spherical power, cylindrical power, and cylindrical axis of the examined eye. However, the corrective optical system is not limited to this. For example, a corrective optical system can be provided that corrects the sight mark beam based on the prism value of the examined eye. By providing a corrective optical system that corrects the sight mark beam based on the prism value, the sight mark beam can be corrected so that the sight mark beam can be projected toward the examined eye even if the examinee has strabismus.

[0073] In addition, in this embodiment, as an example, a structure is shown in which an astigmatism correction optical system 63 for cylindrical power and cylindrical axis and a correction optical system for spherical power (for example, a drive mechanism (drive unit) 39) are respectively provided. However, this is not limiting. For example, it is sufficient as long as a correction optical system is provided that corrects the sight mark beam according to the spherical power, cylindrical power, and cylindrical axis of the eye to be examined. For example, the correction optical system can be an optical system that modulates the wavefront. In addition, for example, the correction optical system can also be an optical system that corrects the sight mark beam according to the spherical power, cylindrical power, and cylindrical axis of the eye to be examined. In this case, for example, the correction optical system can include a lens disk including a plurality of optical elements (spherical lenses, cylindrical lenses, dispersion prisms, etc.) arranged on the same circumference. In this case, by rotating and controlling the lens disk by a drive unit (actuator, etc.), the optical element desired by the examiner is arranged on the optical axis L2.

[0074] Furthermore, the optical element (e.g., a cylindrical lens, a cross cylindrical lens, or a rotating prism) disposed along the optical axis L2 is rotationally controlled by the drive unit so that the optical element is disposed along the optical axis L2 at a rotation angle desired by the inspector. The inspector can switch the optical element disposed along the optical axis L2 by operating an input unit (operating unit) such as the monitor 4.

[0075] There may be one or more lens discs. When multiple lens discs are configured, a drive unit corresponding to each lens disc is provided. For example, each lens disc has an opening (or 0D lens) as a lens disc group and a plurality of optical elements. Representative types of lens discs are a spherical lens disc having a plurality of spherical lenses with different degrees, a cylindrical lens disc having a plurality of cylindrical lenses with different degrees, and an auxiliary lens disc having a plurality of types of auxiliary lenses. The auxiliary lens disc is provided with at least one of a red filter / green filter, a prism, a cross cylindrical lens, a polarizing plate, a Maddox rod lens, and an automatic cross cylindrical lens. In addition, the cylindrical lens is configured to be rotatable around the optical axis L2 by a drive unit. The rotating prism and the cross cylindrical lens can also be configured to be rotatable around each optical axis by a drive unit.

[0076] For example, the correction optical system 90 is arranged between the objective lens 14 and the deflection mirror 81 described later (see Figure 3). For example, the correcting optical system 90 is used to correct optical aberrations generated in the subjective measurement unit. For example, the correcting optical system 90 is used to correct astigmatism among optical aberrations. For example, the correcting optical system 90 includes two positive cylindrical lenses 91a and 91b with equal focal lengths. For example, the correcting optical system 90 corrects astigmatism by adjusting the cylindrical power and cylindrical axis. The cylindrical lenses 91a and 91b are driven by the rotating mechanisms 92a and 92b, respectively, and are independently rotated around the optical axis L3. In addition, in this embodiment, as an example, the correcting optical system 90 includes two positive cylindrical lenses 91a and 91b. However, this is not limiting, and the correcting optical system 90 only needs to be configured to correct astigmatism. For example, the correcting optical system 90 can be configured so that the correcting lens is moved out of or into the optical axis L3. In addition, in this embodiment, as an example, the correcting optical system 90 is configured as a component separate from the correcting optical system 60. However, this is not limiting; the corrective optical system 60 can also serve as the correction optical system 90. In this case, the cylindrical power and cylindrical axis of the examined eye are corrected based on the amount of astigmatism. Specifically, the corrective optical system 60 is driven to take into account (correct) the amount of astigmatism and to correct the sight mark beam based on the cylindrical power and cylindrical axis of the examined eye. By allowing the corrective optical system 60 to also serve as the correction optical system 90, for example, complex control is eliminated, and a separate optical system for correcting optical aberrations is no longer required. Consequently, optical aberrations can be corrected with a simple structure.

[0077] <Objective measurement optical system>

[0078] For example, the objective measurement optical system 10 is used as part of an objective measurement unit that objectively measures the optical characteristics of the eye under examination (details will be described later). Examples of the optical characteristics of the eye under examination include ocular refractive power, ocular axial length, and corneal shape. Furthermore, in this embodiment, an objective measurement unit that measures the ocular refractive power of the eye under examination is described as an example.

[0079] For example, the objective measurement optical system 10 includes a projection optical system 10a, a light receiving optical system 10b, and a correction optical system 90. For example, the projection optical system (light projection optical system) 10a projects a dot-shaped measurement marker onto the fundus of the eye E through the center of the pupil of the eye E. For example, the light receiving optical system 10b extracts fundus reflected light, which is reflected by the fundus, as a ring-shaped fundus reflected image through the pupil periphery. The two-dimensional imaging element 22 of the light receiving optical system 10b captures this ring-shaped fundus reflected image.

[0080] For example, the projection optical system 10a includes a measurement light source (light source) 11, a relay lens 12, an aperture mirror 13, a prism 15, a drive unit (motor) 23, a dichroic mirror 35, a dichroic mirror 29, and an objective lens 14, which are arranged on the optical axis L1 of the objective measurement optical system 10. For example, the prism 15 is a light beam deflecting component. For example, the drive unit 23 is a rotating unit that drives the prism 15 to rotate about the optical axis L1. For example, the light source 11 is conjugate with the fundus of the eye to be examined. For example, the aperture of the aperture mirror 13 is conjugate with the pupil. For example, the prism 15 is arranged at a position deviated from the position conjugate with the pupil of the eye to be examined. For example, the prism 15 decenters the passing light beam relative to the optical axis L1. In addition, instead of the prism 15, a parallel plane plate serving as a light beam deflecting component may be arranged obliquely on the optical axis L1.

[0081] For example, the dichroic mirror 35 is common to both the subjective measurement optical system 25 and the objective measurement optical system 10. Specifically, for example, the dichroic mirror 35 makes the optical axis L2 of the subjective measurement optical system 25 coaxial with the optical axis L1 of the objective measurement optical system 10. For example, the dichroic mirror (polarization beam splitter) 29, which serves as an optical path branching component, reflects the light beam generated by the subjective measurement optical system 25 and the measurement light generated by the projection optical system 10a, and guides them to the examinee's eye.

[0082] For example, the light-receiving optical system 10b shares the objective lens 14, dichroic mirror 29, dichroic mirror 35, prism 15, and aperture mirror 13 of the projection optical system 10a with the projection optical system 10a. The light-receiving optical system 10b includes a relay lens 16 and a mirror 17 arranged in the optical path in the reflection direction of the aperture mirror 13, as well as a light-receiving aperture 18, a collimating lens 19, an annular lens 20, and a two-dimensional imaging element 22 such as a CCD (hereinafter referred to as the imaging element 22) arranged in the optical path in the reflection direction of the mirror 17. For example, the light-receiving aperture 18 and the imaging element 22 are in a conjugate relationship with the fundus of the eye to be examined. For example, the annular lens 20 includes a lens portion formed in an annular shape and a light-shielding portion. The light-shielding portion is the area outside the lens portion. A coating for light shielding is applied to the light-shielding portion. The annular lens 20 is in an optically conjugate positional relationship with the pupil of the eye to be examined. For example, the output signal from the imaging element 22 is received by the calculation control unit 70 (hereinafter referred to as the control unit 70).

[0083] For example, the dichroic mirror 29 reflects the reflected light (fundus reflected light) obtained by reflecting the measurement light from the projection optical system 10a off the fundus of the eye to be examined, toward the light receiving optical system 10b. Furthermore, for example, the dichroic mirror 29 transmits the anterior segment observation light and the collimating light and guides them to the observation optical system 50. Furthermore, for example, the dichroic mirror 35 reflects the aforementioned fundus reflected light toward the light receiving optical system 10b.

[0084] The structure of the objective measurement optical system 10 is not limited to the one described above. The objective measurement optical system 10 may also have other known structures. For example, the objective measurement optical system 10 may project a ring-shaped measurement mark from the periphery of the pupil onto the fundus. In this case, the objective measurement optical system 10 can receive the ring-shaped fundus reflected light from the center of the pupil using the two-dimensional imaging element 22.

[0085] The structure of the objective measurement optical system 10 is not limited to the one described above. Any objective measurement optical system 10 may include a light-projecting optical system and a light-receiving optical system. The light-projecting optical system projects measurement light onto the fundus of the eye being examined. The light-receiving optical system receives reflected light from the fundus using a light-receiving element. For example, the refractive power measurement optical system may include a Shack-Hartmann sensor. Of course, other measurement methods (e.g., a phase difference method using a projected slit) may also be used.

[0086] For example, the light source 11 of the projection optical system 10a, the light receiving aperture 18, the collimating lens 19, the annular lens 20, and the imaging element 22 of the light receiving optical system 10b are capable of moving integrally along the optical axis. In this embodiment, for example, the light source 11 of the projection optical system 10a, the light receiving aperture 18, the collimating lens 19, the annular lens 20, and the imaging element 22 of the light receiving optical system 10b are moved integrally along the optical axis L1 by a drive mechanism 39 that drives the display 31. In other words, the display 31, the light source 11 of the projection optical system 10a, the light receiving aperture 18, the collimating lens 19, the annular lens 20, and the imaging element 22 of the light receiving optical system 10b move synchronously and integrally as a drive unit 95. Of course, these components may also be driven separately.

[0087] For example, the drive unit 95 moves a portion of the objective measurement optical system 10 along the optical axis so that the outer annular light beam is incident on the imaging element 22 in each meridian direction. That is, by moving a portion of the objective measurement optical system 10 along the optical axis L1 according to the spherical refractive error (spherical refractive power) of the eye under examination, the spherical refractive error is corrected. Furthermore, the light source 11, the light receiving aperture 18, and the imaging element 22 are thereby optically conjugated with respect to the fundus of the eye under examination. The movement position of the drive mechanism 39 is detected by a potentiometer (not shown). In addition, the aperture mirror 13 and the annular lens 20 are configured so as to be unaffected by the amount of movement of the portion (movable unit) of the objective measurement optical system 10 described above and to be conjugated with the pupil of the eye under examination at a constant magnification.

[0088] In the above structure, the measuring light emitted from the light source 11 forms a point light source image on the fundus of the eye to be examined via the relay lens 12, the aperture mirror 13, the prism 15, the dichroic mirror 35, the dichroic mirror 29, and the objective lens 14. At this time, the pupil projection image (the projection light beam on the pupil) of the aperture portion of the aperture mirror 13 is rotated eccentrically at high speed by the prism 15 rotating around the optical axis. The point light source image projected on the fundus is reflected and scattered, and then emitted from the eye to be examined, and is focused by the objective lens 14. Subsequently, the light is focused again at the position of the light receiving aperture 18 via the dichroic mirror 29, the dichroic mirror 35, the high-speed rotating prism 15, the aperture mirror 13, the relay lens 16, and the mirror 17. The focused light passes through the collimating lens 19 and the annular lens 20, and forms an annular image on the imaging element 22.

[0089] For example, prism 15 is placed in the common optical path between projection optical system 10a and light-receiving optical system 10b. Therefore, the reflected light beam from the fundus passes through the same prism 15 as the light beam from projection optical system 10a. Therefore, in the optical system after prism 15, reverse scanning is performed so that the projection light beam and the reflected light beam (light-receiving light beam) are not eccentric with respect to the pupil.

[0090] For example, the correcting optical system 90 of the objective measurement optical system 10 also serves as the correcting optical system 90 of the subjective measurement optical system 25. Of course, a correcting optical system used in the objective measurement optical system 10 may be provided separately.

[0091] <First Mark Projection Optical System and Second Mark Projection Optical System>

[0092] In this embodiment, the first index projection optical system 45 and the second index projection optical system 46 are arranged between the correction optical system 90 and the deflection mirror 81. Of course, the arrangement positions of the first index projection optical system 45 and the second index projection optical system 46 are not limited to this.

[0093] In the first mark projection optical system 45, a plurality of infrared light sources are arranged on concentric circles at intervals of 45 degrees with the optical axis L3 as the center. The plurality of infrared light sources are arranged to be left-right symmetrical across a vertical plane passing through the optical axis L3. The first mark projection optical system 45 generates near-infrared light for projecting a calibration mark onto the cornea of the eye to be examined. The second mark projection optical system 46 is arranged at a position different from the first mark projection optical system 45 and has 6 infrared light sources. In this case, the first mark projection optical system 45 projects an infinitely far mark onto the cornea of the eye to be examined E from the left and right directions. The second mark projection optical system 46 projects a finitely far mark onto the cornea of the eye to be examined E from the up and down directions or the oblique direction. In addition, Figure 2For simplicity, only a portion of the first marker projection optical system 45 and a portion of the second marker projection optical system 46 are shown. The second marker projection optical system 46 is used as an anterior segment illumination system for illuminating the anterior segment of the eye being examined. Furthermore, the second marker projection optical system 46 can also be used as a marker for corneal shape measurement. The light sources of the first marker projection optical system 45 and the second marker projection optical system 46 are not limited to point-shaped light sources. These light sources can also be, for example, ring-shaped or linear light sources.

[0094] Observation optical system

[0095] The observation optical system (photographing optical system) 50 shares the subjective measurement optical system 25 and the objective measurement optical system 10, the objective lens 14, and the dichroic mirror 29. Furthermore, the observation optical system 50 includes a photographing lens 51 and a two-dimensional photographing element 52. For example, the two-dimensional photographing element 52 has a photographing surface that is arranged at a position that is approximately conjugate with the anterior segment of the eye to be examined. For example, the output signal from the two-dimensional photographing element 52 is received by the control unit 70. Thus, the image of the anterior segment of the eye to be examined is photographed by the two-dimensional photographing element 52 and displayed on the monitor 4. In addition, the observation optical system 50 also serves as an optical system for detecting the calibration mark image formed on the cornea of the eye to be examined through the first mark projection optical system 45 and the second mark projection optical system 46. The position of the calibration mark image is detected by the control unit 70.

[0096] Internal structure of the subjective eye examination device

[0097] Hereinafter, the internal structure of the subjective eye examination apparatus 1 will be described. Figure 3 From the front direction ( Figure 1 A schematic diagram showing the internal structure of the subjective eye examination apparatus 1 according to the present embodiment as viewed in the A direction. Figure 4 From the side direction ( Figure 1 A schematic diagram showing the internal structure of the subjective eye examination apparatus 1 according to the present embodiment as viewed in the B direction. Figure 5 From the top direction ( Figure 1 The schematic structure diagram of the interior of the subjective eye examination device 1 of this embodiment is observed in the C direction. Figure 3 In the figure, the optical axis of the reflected light in the half mirror 84 is omitted for the sake of convenience. Figure 4 In FIG. 1 , for the sake of convenience, the optical axis of the left-eye measurement unit 7L is shown, while the optical axis of the right-eye measurement unit 7R is omitted. Figure 5 In FIG. 1 , for convenience of explanation, the optical axis of the left-eye measurement section 7L is shown, while the optical axis of the right-eye measurement section 7R is omitted.

[0098] For example, the subjective ophthalmological examination device 1 includes a subjective measurement unit and an objective measurement unit. For example, the subjective measurement unit includes a measurement unit 7, a deflecting mirror 81, a drive unit 83, a drive unit 82, a half mirror 84, and a concave mirror 85. Of course, the structure of the subjective measurement unit is not limited to the above. For example, the objective measurement unit includes a measurement unit 7, a deflecting mirror 81, a half mirror 84, and a concave mirror 85. Of course, the structure of the objective measurement unit is not limited to this structure.

[0099] The subjective eye examination device 1 also includes a right-eye drive unit 9R and a left-eye drive unit 9L. The right-eye drive unit 9R and the left-eye drive unit 9L can respectively move the right-eye measurement unit 7R and the left-eye measurement unit 7L in the X direction. For example, by moving the right-eye measurement unit 7R and the left-eye measurement unit 7L, the distance between the deflecting mirror 81 and the measurement unit 7 is changed. As a result, the presentation position of the sight mark beam in the Z direction is changed. This allows the sight mark beam corrected by the corrective optical system 60 to be directed toward the eye being examined. In other words, the position of the corrected sight mark beam in the Z direction can be adjusted so that the image of the sight mark beam corrected by the corrective optical system 60 is formed on the fundus of the eye being examined.

[0100] For example, the deflecting mirror 81 includes a pair of right-eye deflecting mirrors 81R and left-eye deflecting mirrors 81L, respectively. For example, the deflecting mirror 81 is positioned between the corrective optical system 60 and the eye being examined. That is, the corrective optical system 60 includes a right-eye corrective optical system and a left-eye corrective optical system, respectively. The right-eye deflecting mirror 81R is positioned between the right-eye corrective optical system and the right eye ER. The left-eye deflecting mirror 81L is positioned between the left-eye corrective optical system and the left eye EL. For example, the deflecting mirror 81 is preferably positioned at a pupil-conjugate position.

[0101] For example, the right-eye deflecting mirror 81R reflects the light beam projected from the right-eye measurement unit 7R and guides it toward the right eye ER. Furthermore, the right-eye deflecting mirror 81R reflects, for example, the light reflected from the right eye ER and guides it toward the right-eye measurement unit 7R. For example, the left-eye deflecting mirror 81L reflects the light beam projected from the left-eye measurement unit 7L and guides it toward the left eye EL. Furthermore, the left-eye deflecting mirror 81L reflects, for example, the light reflected from the left eye EL and guides it toward the left-eye measurement unit 7L. In this embodiment, the deflecting mirror 81 is shown as an example of a deflecting member that reflects the light beam projected from the measurement unit 7 and guides it toward the examined eye E. However, the deflecting member is not limited to the deflecting mirror 81. Any deflecting member may be used as long as it reflects the light beam projected from the measurement unit 7 and guides it toward the examined eye E. Examples of other deflecting members include prisms and lenses.

[0102] For example, the drive unit 83 includes a motor (drive unit) and the like. For example, the drive unit 83 includes a drive unit 83R for driving the right-eye deflecting mirror 81R and a drive unit 83L for driving the left-eye deflecting mirror 81L. For example, the drive unit 83 drives the deflecting mirror 81 in the X direction. For example, by moving the right-eye deflecting mirror 81R and the left-eye deflecting mirror 81L, the distance between the right-eye deflecting mirror 81R and the left-eye deflecting mirror 81L can be changed. This allows the X-direction distance between the right-eye optical path and the left-eye optical path to be changed to match the interpupillary distance of the examined eye.

[0103] For example, the driving unit 82 includes a motor (driving unit) and the like. For example, the driving unit 82 includes a driving unit 82R for driving the deflecting mirror 81R for the right eye and a driving unit 82L for driving the deflecting mirror 81L for the left eye. For example, the deflecting mirror 81 is rotated and moved by the driving unit 82. For example, the driving unit 82 rotates the deflecting mirror 81 relative to the rotation axis in the horizontal direction (X direction) and the rotation axis in the vertical direction (Y direction). That is, the driving unit 82 rotates the deflecting mirror 81 in the XY direction. In addition, the rotation direction of the deflecting mirror 81 may also be the horizontal direction or the vertical direction. In addition, multiple deflecting mirrors may be provided in the optical path for the right eye and the optical path for the left eye, respectively. For example, two deflecting mirrors may be provided in the optical path for the right eye and the optical path for the left eye, respectively. For example, two deflecting mirrors may be provided in the optical path for the right eye. In this case, one deflecting mirror may rotate in the X direction, and the other deflecting mirror may rotate in the Y direction. For example, the apparent light beam formed in front of the eye to be examined can be deflected by rotationally moving the deflecting mirror 81. This allows the formation position of the image generated by the corrective optical system 60 to be optically corrected.

[0104] For example, the concave mirror 85 is shared by both the right-eye measurement unit 7R and the left-eye measurement unit 7L. For example, the concave mirror 85 is shared by both the right-eye optical path, which includes the right-eye corrective optical system, and the left-eye optical path, which includes the left-eye corrective optical system. That is, the concave mirror 85 is positioned so that both the right-eye optical path, which includes the right-eye corrective optical system, and the left-eye optical path, which includes the left-eye corrective optical system, pass through. Of course, the concave mirror 85 can also be shared by both optical paths. Concave mirrors can be provided separately for the right-eye optical path, which includes the right-eye corrective optical system, and for the left-eye optical path, which includes the left-eye corrective optical system. For example, the concave mirror 85 guides the optical target beam after passing through the corrective optical system to the examined eye and forms an image of the optical target beam after passing through the corrective optical system in front of the examined eye. While this embodiment illustrates a configuration using the concave mirror 85, various optical components can be used in place of the concave mirror 85. For example, lenses or plane mirrors can be used as optical components.

[0105] For example, the concave mirror 85 serves both as a subjective measurement unit and an objective measurement unit. For example, the sight mark beam projected from the subjective measurement optical system 25 is projected toward the examined eye via the concave mirror 85. Furthermore, for example, the measurement light projected from the objective measurement optical system 10 is projected toward the examined eye via the concave mirror 85. Furthermore, for example, the reflected light from the objective measurement optical system 10 is guided toward the light-receiving optical system 10b of the objective measurement optical system 10 via the concave mirror 85. Furthermore, in this embodiment, as an example, a configuration is shown in which the reflected light from the objective measurement optical system 10 is guided toward the light-receiving optical system 10b of the objective measurement optical system 10 via the concave mirror 85. However, this is not limiting, and the reflected light from the objective measurement optical system 10 may also be guided toward the light-receiving optical system 10b of the objective measurement optical system 10 without passing through the concave mirror 85.

[0106] More specifically, for example, in this embodiment, the optical axis between the concave mirror 85 and the examined eye E in the subjective measurement section is at least coaxial with the optical axis between the concave mirror 85 and the examined eye E in the objective measurement section. Furthermore, in this embodiment, the optical axis L2 of the subjective measurement optical system 25 and the optical axis L1 of the objective measurement optical system 10 are combined by the dichroic mirror 35. As a result, the optical axis L2 is coaxial with the optical axis L1.

[0107] The optical path of the subjective measurement unit is described below. For example, the subjective measurement unit uses a concave mirror 85 to reflect the sight mark beam after passing through the corrective optical system 60 toward the eye being examined, thereby guiding the sight mark beam toward the eye being examined. The subjective measurement unit forms an image of the sight mark beam after passing through the corrective optical system 60 in front of the eye being examined, so that the distance between the position where the image is formed and the eye being examined, as detected by the examinee, optically reaches a predetermined inspection distance. That is, the concave mirror 85 reflects the sight mark beam so that it becomes a substantially parallel beam. Therefore, to the examinee, the sight mark image appears to be farther than the actual distance from the eye being examined E to the display 31. That is, by using the concave mirror 85, the image of the sight mark beam (sight mark image) can be presented to the examinee so that the sight mark image appears to be located at a position corresponding to the predetermined inspection distance.

[0108] The optical path of the subjective measurement unit will be described in more detail. The following description uses the left-eye optical path as an example. The right-eye optical path also has the same structure as the left-eye optical path. For example, in the subjective measurement unit for the left eye, the sight mark beam projected from the display 32 of the left-eye measurement unit 7L enters the astigmatism correction optical system 63 via the projecting lens 33. After passing through the astigmatism correction optical system 63, the sight mark beam passes through the reflecting mirror 36, the dichroic mirror 35, the dichroic mirror 29, and the objective lens 14 and enters the correction optical system 90. After passing through the correction optical system 90, the sight mark beam exits the left-eye measurement unit 7L and is projected onto the left-eye deflecting mirror 81L. After exiting the left-eye measurement unit 7L and being reflected by the left-eye deflecting mirror 81L, the sight mark beam is reflected by the half mirror 84 toward the concave mirror 85. The sight mark beam reflected by the concave mirror passes through the half mirror 84 and reaches the left eye EL.

[0109] Thus, with the position of the left eye EL where the glasses are mounted (for example, about 12 mm from the corneal apex) as a reference, the image of the sight mark corrected by the corrective optical system 60 is formed on the fundus of the left eye EL. Therefore, the astigmatism correction optical system 63 appears to be positioned in front of the eye, and further, the adjustment of the spherical power by the spherical power correction optical system (driven by the drive mechanism 39 in this embodiment) also appears to be performed in front of the eye. The examinee can collimate the sight mark image in a natural state via the concave mirror 85. In addition, in this embodiment, the optical path for the right eye also has the same structure as the optical path for the left eye. With the position of the glasses where the two examinee eyes ER and EL are mounted (for example, about 12 mm from the corneal apex) as a reference, the image of the sight mark corrected by the pair of left and right corrective optical systems 60 is formed on the fundus of the two examinee eyes. In this way, the examinee can respond to the examiner while looking directly at the sight mark in a natural and level state. The examinee is corrected by the corrective optical system 60 until the examinee can properly see the test target. Based on the correction value, the optical characteristics of the examinee's eye are subjectively measured.

[0110] Next, the optical path of the objective measurement unit will be described. The following description uses the left-eye optical path as an example. The right-eye optical path also has the same structure as the left-eye optical path. For example, in the objective measurement unit for the left eye, the measurement light emitted from the light source 11 of the projection optical system 10a in the objective measurement optical system 10 passes through the relay lens 12 and the objective lens 14, and then enters the correction optical system 90. After passing through the correction optical system 90, the measurement light is emitted from the left-eye measurement unit 7L and projected onto the left-eye deflecting mirror 81L. The measurement light emitted from the left-eye measurement unit 7L and reflected by the left-eye deflecting mirror 81L is then reflected by the half mirror 84 toward the concave mirror 85. The measurement light reflected by the concave mirror passes through the half mirror 84 and reaches the left eye EL, forming a point light source image on the fundus of the left eye EL. At this time, the pupil projection image (the projection light beam on the pupil) generated by the aperture portion of the aperture mirror 13 is rotated eccentrically at high speed by the prism 15 rotating around the optical axis.

[0111] The light of the point light source image formed on the fundus of the left eye EL is reflected and scattered by the left eye EL and then emitted from the left eye EL. The light is focused by the objective lens 14 via the optical path through which the measurement light passes. The focused light is reflected by the mirror 17 via the dichroic mirror 29, the dichroic mirror 35, the prism 15, the aperture mirror 13, and the relay lens 16. The reflected light from the mirror 17 is focused again on the opening of the light receiving aperture 18. The focused light is formed into a roughly parallel light beam by the collimating lens 19 (in the case of an emmetropic eye). The roughly parallel light beam is taken out as a ring light beam through the annular lens 20. The ring light beam is received by the shooting element 22 as a ring image. By analyzing the received ring image, the optical characteristics of the eye being examined can be objectively measured.

[0112] Thus, for example, the subjective ophthalmological examination device 1 in this embodiment forms an image of the corrective optical system in front of the examinee's eye. Furthermore, the subjective ophthalmological examination device 1 in this embodiment includes an objective measurement unit in addition to a subjective measurement unit. This eliminates the need for placing a corrective optical system in front of the examinee's eye, enabling both subjective and objective measurements to be performed in an open state. This allows for measurements to be performed while the examinee is viewing objects naturally in their daily lives, resulting in superior measurements. Furthermore, since both subjective and objective optical characteristics can be measured using a single device, the optical characteristics of the examinee's eye can be smoothly measured.

[0113] Furthermore, for example, in the subjective ophthalmological apparatus 1 of this embodiment, the subjective and objective measurement units share optical components. This reduces the number of components, simplifying the subjective ophthalmological apparatus 1. Furthermore, this reduces unnecessary space, minimizing the subjective ophthalmological apparatus 1.

[0114] For example, in the subjective ophthalmology apparatus 1 of this embodiment, the optical axis between the subjective examination unit and the examined eye is coaxial with the optical axis between the objective examination unit and the examined eye. Therefore, when measuring the examined eye, adjusting one examination unit also allows adjustment of the other. This makes it easy to adjust the examination units during measurement. In other words, by adjusting the objective measurement unit, the subjective measurement unit can also be easily adjusted.

[0115] For example, the subjective ophthalmological examination device 1 in this embodiment uses a concave mirror 85 to form the sight mark beam into a substantially parallel beam. Consequently, the subjective measurement unit can present the sight mark to the examinee at a position corresponding to the optically prescribed inspection distance (prescribed inspection position). Consequently, there is no need for components to actually present the sight mark at the prescribed inspection position. This eliminates the need for redundant components and space, allowing the subjective ophthalmological examination device 1 to be miniaturized.

[0116] <Control Department>

[0117] For example, the control unit 70 includes a CPU (processor), RAM, and ROM. For example, the CPU of the control unit 70 controls the various components of the subjective ophthalmology apparatus 1. For example, the RAM temporarily stores various information. The ROM of the control unit 70 stores various programs for controlling the operation of the subjective ophthalmology apparatus 1, as well as optotype data and initial values used for various examinations. Furthermore, the control unit 70 may include multiple CPUs.

[0118] For example, the control unit 70 is electrically connected to a nonvolatile memory (storage unit) 72, a monitor (which also serves as an operating unit in this embodiment) 4, and various components. The nonvolatile memory (hereinafter referred to as memory) 72 is a non-transitory storage medium that retains stored content even when power is cut off. For example, a hard disk drive, a flash read-only memory, an OCT device, or a USB memory removably attached to the subjective ophthalmological apparatus 1 can be used as the memory 72. For example, the memory 72 stores a control program for controlling the subjective measurement unit and the objective measurement unit.

[0119] <Changes in the Convergence Angle Due to Adjustment of the Concave Mirror's Deflection Angle>

[0120] In this embodiment, the control unit 70 can also control the light deflection components (e.g., deflection mirrors 81R and 81L) disposed in the right-eye optical path and the left-eye optical path, respectively, to change the horizontal deflection angles of the right-eye measurement optical axis L4R and the left-eye measurement optical axis L4L. For example, the control unit (convergence angle changer) 70 can change the convergence angles of the sight mark light beams emitted from the right-eye optical path and the left-eye optical path by changing the incident angles of the measurement optical axes L4R and L4L with respect to the concave mirror 85. This allows the convergence angles to be appropriately changed according to the distance at which the sight mark is presented.

[0121] In this case, the angle of the measurement optical axes L4R and L4L is changed in the horizontal direction (X direction), so that the position of the intersection point C of the right-eye measurement optical axis L4R and the left-eye measurement optical axis L4L is changed (see Figure 6 、 Figure 7 The sight mark beam from the right-eye measurement unit 7R is projected toward the right eye ER, with the measurement optical axis L4R as its principal ray. Consequently, the line of sight of the right eye ER becomes coaxial with the right-eye measurement optical axis L4R. Similarly, the sight mark beam from the left-eye measurement unit 7L is projected toward the left eye EL, with the left-eye measurement optical axis L4L as its principal ray. Consequently, the line of sight of the left eye EL becomes coaxial with the left-eye measurement optical axis L4L. As a result, the convergence angle of the sight mark beam is changed, thereby changing the convergence angle of the left and right eyes.

[0122] More specifically, for example, the control unit 70 can move (change) the deflection angle of the measurement optical axes L4R, L4L by controlling the driving unit 82 to adjust the reflection angle of the deflecting mirrors 81R, 81L. Of course, the deflecting mirrors 81R, 81L are not limited thereto, and other light deflecting components may also be used.

[0123] Figure 6 This figure shows an example of presenting a sight mark at the distance. For example, the control unit 70 can set a convergence angle corresponding to the distance by deflecting the measurement optical axes L4R and L4L so that they pass through the focal position of the concave mirror 85. Furthermore, it is not necessary for the optical axis to pass through the precise focal position. The convergence angle can be any angle corresponding to the distance.

[0124] For example, after being reflected by the concave mirror 85, the measuring optical axes L4R and L4L are parallel to each other and are in the same direction as the Z direction. The intersection C is formed at infinity or the far vision position (for example, a position that is apparently 5m away from the eye to be examined). The far vision position is, for example, the presentation position of the mark when the sight mark is presented at the far vision distance. In this case, the control unit 70 can adjust the presentation position of the sight mark to image the sight mark at the far vision position of the eye to be examined. As a result, the sight mark is apparently presented from a distance relative to the eye to be examined. Furthermore, the left and right sight mark light beams are set to a convergence angle corresponding to the far vision distance.

[0125] Figure 7 An example of presenting a sight mark at near distance is shown. For example, the control unit 70 can deflect the measurement optical axes L4R and L4L so that the angle between the measurement optical axis L4R (L4L) and the measurement optical axis of the measurement unit 7R (7L) is smaller than that at distance distance. This shifts the convergence angle (intersection point C) toward near distance.

[0126] For example, the control unit 70 can deflect the measuring optical axes L4R and L4L so that the measuring optical axes L4R and L4L are parallel to each other just before being reflected by the concave mirror 85. The measuring optical axes L4R and L4L reflected by the concave mirror 85 pass through the focal position of the concave mirror 85 and reach the left and right eyes. Thus, apparently, an intersection C is formed at the focal position of the concave mirror 85. In this case, the control unit 70 can image the sight mark at the near position corresponding to the intersection C by adjusting the presentation position of the sight mark. As a result, the sight mark is apparently presented from the near position relative to the eye being examined. Furthermore, the left and right sight mark light beams are set to a convergence angle corresponding to the set near distance. The near position is, for example, the presentation position of the mark when the sight mark is presented at the near distance.

[0127] Of course, the distance at which the sight mark is presented is not limited to the distances described above. In other words, the control unit 70 can arbitrarily change the convergence angle of the sight mark light beam by deflecting the measurement optical axes L4R and L4L to change the position of the intersection point C relative to the eye being examined. In this case, the correspondence between the deflection angle (drive angle) of the light deflection component and the sight mark presentation distance can be pre-set and stored in the memory 72. Specifically, the reflection angle of the deflecting mirrors 81R and 81L can be pre-established to correspond to the sight mark presentation distance. In this case, a correspondence table or calculation formula can be stored in the memory 72.

[0128] For example, the control unit 70 can receive the presentation distance of the optotype based on an operation signal from the monitor (operation unit) 4. Furthermore, the control unit 70 can obtain the deflection angle corresponding to the presentation distance from the memory 72. Furthermore, the control unit 70 can drive the light deflecting member so as to have an angle corresponding to the obtained deflection angle.

[0129] Thus, by changing the distance of the sight mark presentation and switching the deflection angles relative to the measurement optical axes L4R and L4L of the concave mirror 85, it is possible to present the sight mark in a state close to natural horizontal vision. As a result, good measurement results can be obtained.

[0130] Furthermore, when controlling the light projection optical system 30 and changing the presentation distance of the sight mark, the control unit 70 can change the presentation distance of the sight mark by changing the spherical power of the corrective optical system 60. For example, when the sight mark is presented at a predetermined near distance (e.g., 33 cm), the control unit 70 can position the display 31 closer to a power corresponding to the near distance (e.g., 3.0 D) based on the position of the correction power (the distance correction power determined by objective refractive power measurement or visual acuity measurement) for distance use (when the sight mark is presented at the distance).

[0131] <PD adjustment based on changes in the distance between the left and right measurement optical axes>

[0132] In this embodiment, the control unit 70 can change the inter-optical axis distance LPD between the right-eye measurement optical axis L4R and the left-eye measurement optical axis L4L in the horizontal direction (X direction) by controlling the optical deflection components (e.g., deflection mirrors 81R and 81L) respectively arranged in the right-eye optical path and the left-eye optical path (see FIG8 ). In this case, the right-eye optical path and the left-eye optical path can be arranged at positions corresponding to the subject's interpupillary distance (the distance between the left and right eyes) by adjusting the positions of the optical deflection components in the horizontal direction based on the subject's interpupillary distance. Furthermore, the subject's interpupillary distance can be obtained by calculating the distance between the left and right eyes through image processing using the aforementioned binocular imaging optical system. Alternatively, the measurement result of the subject's interpupillary distance, previously measured by a pupillometer or the like, can be obtained from the memory 72.

[0133] As a result, the left and right pair of measurement optical systems are positioned at positions corresponding to the interpupillary distance. For example, the measurement optical axes of the left and right pair of subjective measurement optical systems 25 are positioned at positions corresponding to the interpupillary distance. Consequently, the corrective optical system 60 and the light projection optical system 30 are positioned at positions corresponding to the interpupillary distance. Furthermore, for example, the measurement optical axes of the left and right pair of objective measurement optical systems 10 are positioned at positions corresponding to the interpupillary distance. Furthermore, adjustment of the inter-optical axis distance LPD can be performed automatically, for example, before performing calibration operations on the examined eye, before conducting objective measurements, or before conducting subjective measurements. Alternatively, adjustment of the inter-optical axis distance LPD can be performed based on an operation signal from the monitor 4.

[0134] Alternatively, the positions of the measurement optical axes L4R and L4L can be changed in the horizontal direction (X direction) by horizontally driving the drive unit (e.g., drive unit 83) of each light deflection component. Regarding a specific method for changing the inter-optical axis distance LPD, for example, the control unit 70 can control the drive unit 83 to adjust the horizontal position of the deflection mirrors 81R and 81L, thereby moving the positions of the measurement optical axes L4R and L4L. Of course, this is not limited to the deflection mirrors 81R and 81L; other light deflection components may also be used.

[0135] Figure 8A as well as Figure 8B FIG. 8 is a diagram for explaining the change of the optical axis distance LPD caused by the movement of the deflection mirror 81. In this embodiment, the LPD can be changed by moving the deflection mirror 81 in the X direction. For example, Figure 8A The deflecting mirror 81R is moved so that the distance between the right-eye measurement unit 7R and the deflecting mirror 81R is shortened (so that the deflecting mirror 81R approaches the right-eye measurement unit 7R in the X direction). Alternatively, for example, the deflecting mirror 81L is moved so that the distance between the measurement unit 7L and the deflecting mirror 81L is shortened (so that the deflecting mirror 81L approaches the measurement unit 7L in the X direction). Figure 8B As shown, the deflection mirror 81 moves. Therefore, Figure 8A The optical axis distance LPD1 shown is changed to Figure 8B The optical axis distance LPD2 is shown.

[0136] Regarding the change in the above-mentioned inter-optical axis distance LPD, the correspondence between the horizontal position of the light deflecting member and the interpupillary distance PD can be pre-set and stored in the memory 72. Specifically, the horizontal positions of the deflecting mirrors 81R and 81L can be pre-associated with the interpupillary distance. In this case, a correspondence table or calculation formula can be stored in the memory 72.

[0137] For example, the control unit 70 may acquire the horizontal position (drive position) of the light deflection member corresponding to the interpupillary distance of the eye to be examined obtained by the interpupillary distance measuring unit from the memory 72. The control unit 70 may then move the light deflection member to the acquired horizontal position.

[0138] Aberration Correction

[0139] The control unit (correction setting unit) 70 can set the correction amount for correcting the optical aberrations generated in the optical path of the measurement optical system (e.g., the left-eye optical path and the right-eye optical path). Furthermore, the control unit 70 can correct the optical aberrations generated in the optical path of the measurement optical system by correcting the correction optical system 90 based on the set correction amount. Furthermore, the aberration correction amount in the correction optical system 90 is preferably set to an amount that can eliminate the generated optical aberrations. However, the aberration correction amount is not limited to this, as long as it does not interfere with the inspection. Furthermore, the aberration correction unit may also include the control unit 70 and the correction optical system 90.

[0140] Astigmatism, a major optical aberration generated in the optical path of the measurement optical system, is, for example, the astigmatism of the light beam generated by concave mirror 85. This astigmatism can affect at least one of the subjective measurement optical system 25 and the objective measurement optical system 10. Furthermore, astigmatism is a directional aberration. Correction of astigmatism can be performed, for example, by eliminating the direction in which the astigmatism occurs.

[0141] <Aberration correction according to the degree of correction>

[0142] The amount of optical aberration may change due to changes in the reflection position or reflection area (beam diameter) of the light beam on the concave mirror 85. As an example, the reflection area of the sight mark light beam changes due to changes in the correction power of the corrective optical system 60. As a result, the amount of aberration changes.

[0143] In other words, the focusing state of the light beam relative to the concave mirror 85 varies depending on the correction degree set in the correcting optical system 60. For example, when the correction degree is 0D, the sight mark light beam enters the concave mirror 85 as a parallel beam from infinity. As the correction degree increases toward the positive side, the sight mark light beam enters the concave mirror 85 as a strongly diffuse light beam, so the reflection area becomes larger and the aberration becomes larger. As the correction degree increases toward the negative side, the sight mark light beam enters the concave mirror 85 as a strongly converging light beam, so the reflection area becomes smaller and the aberration becomes smaller. Depending on this difference in reflection area, the amount of astigmatism caused by the concave mirror 85 varies.

[0144] Therefore, in this embodiment, the aberration correction amount in the correcting optical system 90 can be changed according to the correction power of the correcting optical system 60. This allows for the presentation of an aberration-free sight mark with reduced astigmatism, regardless of the correction power. This enables both subjective and objective measurements with high precision.

[0145] In this case, a table can be created in advance that associates correction powers with correction amounts corresponding to each correction power, thereby correcting the astigmatism generated by concave mirror 85. This created table can be stored in memory 72. The correction amount for each correction power can be determined, for example, through optical simulation or experimentation. Furthermore, it is not necessary to use a table. An equation for deriving the correction amount corresponding to each correction power can be stored in memory 72, and the correction amount can be determined using the equation.

[0146] The correction amount for each correction degree can also be made for each spherical degree. Furthermore, the differences in the spherical degrees, astigmatism degrees and axis angles can be taken into account, and correction amounts can be made for each astigmatism degree and / or each axis angle of each spherical degree. In addition, according to the simulation of the present inventors, the change in the amount of astigmatism is greatly affected by the change in spherical degree. Therefore, it is considered to obtain a constant effect by changing the correction amount for each spherical degree (changing the correction amount according to the change in spherical degree). In addition, when setting the correction amount for each correction degree, the correction amount can be made gradually different relative to each correction degree. For example, a constant correction amount can be set for each specified level (for example, 1.0D level such as 0 to 1.0D, 1.0 to 2.0). That is, the correction amount can be changed in units of levels.

[0147] In addition, when the correction power of the correcting optical system 60 is set based on the objective eye refractive power (spherical power S, astigmatism power C, astigmatism axis angle A), the control unit 70 can obtain the aberration correction amount corresponding to the correction power corresponding to the objective eye refractive power (objective refractive error) from the memory 72, and control the correcting optical system 90 based on the obtained aberration correction amount.

[0148] Specifically, the control unit 70 can set the aberration correction amount based on the objective ocular refractive power obtained by the objective ocular refractive power measurement device (e.g., the objective measurement optical system 10). Furthermore, the control unit 70 can perform aberration correction by controlling the correcting optical system 90 based on the set aberration correction amount.

[0149] Furthermore, when the aberration correction amount is set based on the correction power, it is not necessary to necessarily associate the numerical data of the correction power with the aberration correction amount. For example, an operation signal corresponding to the correction power input to the monitor 4 may be associated with the aberration correction amount. Alternatively, the drive information of the corrective optical system 60 (e.g., the position of the display 31) may be associated with the aberration correction amount. Alternatively, as described above, the measurement results of the objective eye refractive power measurement device may be associated with the aberration correction amount.

[0150] In addition, when the apparent presentation distance of the sight mark is changed, the aforementioned astigmatism is generated. In this case, the control unit 70 can present a sight mark with reduced aberration regardless of the change in presentation distance by changing the aberration correction amount according to the presentation distance of the sight mark. The control unit 70 can also change the aberration correction amount of the correcting optical system 90 according to the presentation distance of the sight mark presented by the projection optical system 30 to the examinee's eye. In this case, the sight mark presentation distance and the aberration correction amount can be established in correspondence. Alternatively, the driving information of the projection optical system 30 (for example, the position of the display 31, etc.) can be established in correspondence with the aberration correction amount. In addition, when the presentation distance of the sight mark is changed by controlling the correction degree of the correcting optical system 60, the aberration correction amount corresponding to the correction degree of the presentation distance to which the sight mark is attached can be set.

[0151] Furthermore, examples in which the amount of aberration varies depending on changes in the reflection area of the light beam on the concave mirror 85 are not limited to the examples described above. If the reflection area of the measurement light beam from the fundus projected by the objective measurement optical system 10 on the concave mirror 85 changes depending on changes in the refractive power of the eye being examined, the amount of aberration changes. In this case, there is a possibility that the measurement image (e.g., a ring image) produced by the objective measurement optical system 10 will be distorted. Therefore, the aberration correction amount of the correction optical system 90 can be changed based on the objective eye refractive power obtained in advance by the objective measurement optical system 10. This results in a measurement image with reduced aberration. As a result, the eye refractive power can be measured with high precision. Furthermore, since the same method as for the correction degree described above can be used for setting the aberration correction amount, the table or calculation formula will not be specifically described. Furthermore, the same parameter (SCA) can be used for the objective eye refractive power and the correction degree. Therefore, the same table or calculation formula can be used when performing the correction described above.

[0152] <Aberration Correction Depending on the Deflection Angle or Position of the Light Deflecting Component>

[0153] Furthermore, the reflection position of the light beam (e.g., the sight mark beam, the measurement beam of the objective measurement optical system 10) on the concave mirror 85 changes depending on changes in at least one of the deflection angle of the light deflection member (e.g., the deflection mirrors 81R and 81L) and the horizontal position of the light deflection member. As a result, the amount of aberration changes.

[0154] Therefore, in this embodiment, the control unit 70 can adjust the aberration correction amount of the optical system 90 based on changes in at least one of the deflection angle of the light deflection component (e.g., deflecting mirrors 81R, 81L) and the horizontal position of the light deflection component. This allows, for example, the presentation of a good sight mark with reduced astigmatism, regardless of the deflection angle or horizontal position of the light deflection component. Furthermore, a good measurement image with reduced astigmatism can be obtained, regardless of the deflection angle or horizontal position of the light deflection component. This enables high-precision subjective or objective measurement.

[0155] In this case, a table can be prepared that pre-sets the correction amount for correcting the astigmatism generated by the concave mirror 85 for each parameter (deflection angle and horizontal position). The prepared table can be stored in the memory 72. The correction amount can be obtained, for example, by optical simulation or experiment. It is not necessary to use a table. The calculation formula for deriving the aberration correction amount can also be stored in the memory 72, and the correction amount can be obtained using the calculation formula. In this case, the correction amount can be made different according to each parameter. For example, a constant correction amount can be set within a specified level of the parameter. In other words, the correction amount can be changed at each level.

[0156] In addition, when the aberration correction amount is set according to the deflection angle of the light deflection component, it is not necessary to establish a correspondence between the numerical data of the deflection angle and the aberration correction amount. It is also possible to establish a correspondence between the drive angle information of the light deflection component (for example, the drive signal of the drive unit 82) and the aberration correction amount. In addition, as described above, when the convergence angle of the sight mark light beam is changed according to the sight mark presentation distance, the convergence angle and the aberration correction amount can be established in correspondence. In other words, the control unit 70 can change the aberration correction amount of the correction optical system 90 according to the convergence angle of the sight mark light beam changed by the drive of the light deflection component. In addition, as described above, when the position (calibration position) of the measurement optical axis L1R, L1L relative to the subject's eye is adjusted by adjusting the deflection angle of the light deflection component, the calibration position of the subject's eye can be established in correspondence with the aberration correction amount.

[0157] Furthermore, when the aberration correction amount is set based on the position of the light deflection component, it is not necessary to necessarily associate the position data with the aberration correction amount. Alternatively, the aberration correction amount may be associated with the drive position information of the light deflection component (e.g., the drive signal of the drive unit 82). Furthermore, as described above, when the pair of measurement optical systems are aligned with the interpupillary distance by adjusting the horizontal position of the light deflection component, the interpupillary distance may be associated with the aberration correction amount. In other words, the control unit 70 may change the aberration correction amount of the correction optical system 90 based on the interpupillary distance of the eye being examined.

[0158] <Support for multiple parameters>

[0159] Furthermore, the aforementioned aberration correction corresponding to the correction power can be performed simultaneously with the aberration correction corresponding to the deflection angle or position of the light deflection component, for example, during subjective measurement. In this case, the aberration correction amount can be set by separately obtaining each aberration correction amount and adding them together. The aberration correction amount corresponding to the correction power changes according to the deflection angle and position of the light deflection component. Therefore, it is more preferable to pre-store in the memory 72 a table or an arithmetic expression for deriving the optimal aberration correction amount, wherein the optimal aberration correction amount is derived from three parameters consisting of the correction power, the deflection angle of the light deflection component, and the position of the light deflection component. In this case, the aberration correction amount of the correction optical system 90 can be changed according to the change of at least one parameter.

[0160] In other words, when determining aberration correction amounts based on multiple parameters, a table or calculation formula for deriving the optimal aberration correction amount from these multiple parameters can be pre-stored in memory 72. For example, aberration correction based on the objective eye's refractive power can be performed simultaneously with aberration correction based on the deflection angle or position of the light deflection member during objective measurement. In this case, the aberration correction amount can be set by separately obtaining each aberration correction amount and summing them. The aberration correction amount based on the objective eye's refractive power changes with changes in the deflection angle and position of the light deflection member. Therefore, more preferably, a table or calculation formula for deriving the optimal aberration correction amount derived from three parameters: the objective eye's refractive power, the deflection angle of the light deflection member, and the position of the light deflection member can be pre-stored in memory 72. In this case, the aberration correction amount of the correcting optical system 90 can be changed based on changes in at least one parameter.

[0161] <Control Action>

[0162] The following describes the control operations of the subjective eye examination apparatus 1. The examiner instructs the examinee to place their chin on the chin rest 5 and observe the presentation window 3. The examiner instructs the examinee to fixate their gaze on the fixation mark displayed on the display 31. Subsequently, calibration of the examinee's eye (adjustment of the position of the examinee's eye) is performed. After the examinee selects the calibration start switch, the control unit 70 begins automatic calibration.

[0163] For example, the control unit 70 detects the pupil positions of the left and right eyes under examination from the facial image captured by the imaging optical system 100. For example, after detecting the pupil positions, the control unit 70 controls the subjective ophthalmological apparatus 1 to display an image of the anterior ocular segment on the monitor 4. For example, the control unit 70 drives the right-eye deflecting mirror 81R and the left-eye deflecting mirror 81L, respectively, to rotate them in the X and Y directions. Furthermore, after detecting the pupil positions, the control unit 70 can move the right-eye measurement unit 7R and the left-eye measurement unit 7L, respectively, in the X direction. Specifically, the control unit 70 performs calibration in the X and Y directions by driving the deflecting mirror 81 and performs calibration in the Z direction by driving the measurement unit 7.

[0164] Furthermore, in this embodiment, as an example, XYZ calibration is performed by driving the deflecting mirror 81 and the measuring unit 7. However, this is not limiting; any embodiment of the present invention may be used as long as the positional relationship between the examined eye and the subjective and objective measuring units can be adjusted. Specifically, any embodiment of the present invention may be used as long as calibration in the XYZ directions is performed so that the image corrected by the corrective optical system 60 is formed on the fundus of the examined eye. For example, a component may be provided that can move the subjective ophthalmological device 1 in the XYZ directions relative to the chin rest 5, thereby moving the subjective ophthalmological device 1 for calibration. Alternatively, for example, calibration in the XYZ directions may be performed solely using the deflecting mirror 81. In this case, for example, a component may be provided that moves the deflecting mirror 81 in the Z direction, thereby driving the deflecting mirror 81 to rotate and changing the distance between the deflecting mirror 81 and the measuring unit.

[0165] Figure 9 An anterior ocular segment observation screen showing an anterior ocular segment image captured by the two-dimensional imaging element 52 is shown. In addition, in the present embodiment, the calibration control of one of the two inspected eyes is described. In addition, the control described below is also performed for the other inspected eye. In addition, for example, during the calibration control, the two inspected eyes can be displayed on the monitor 4, and the calibration control of the two inspected eyes can be performed on the same screen. In addition, for example, during the calibration control, the inspected eye of one side can be displayed on the monitor 4, and after the calibration control of the inspected eye of one side is completed, the inspected eye of the other side can be displayed on the monitor 4, and the calibration control of the inspected eye of the other side can be performed. In addition, for example, the calibration control of the inspected eye of one side can also be performed based on the calibration control result of the inspected eye of the other side.

[0166] For example, the control unit (offset detection unit, correction unit) 70 detects the positional offset of the image of the corrective optical system 60 relative to the eye to be examined. For example, the control unit 70 controls the driving unit based on the detection result to deflect the apparent light beam used to guide the image of the corrective optical system 60 toward the eye to be examined. Thus, the control unit 70 optically corrects the position of image formation. In this way, in the subjective eye examination device 1 of this embodiment, the control unit 70 detects the positional offset between the eye to be examined and the corrective optical system, and optically corrects the position of image formation. Thus, by correcting the positional offset between the eye to be examined and the corrective optical system, the device can be used with the eye to be examined arranged in an appropriate position. Therefore, measurement can be performed with high precision.

[0167] More specifically, for example, during calibration, the light sources of the first mark projection optical system 45 and the second mark projection optical system 46 are turned on. For example, the control unit 70 detects the XY center coordinates (refer to Figure 9 The cross mark (shown on the left) is roughly used as the corneal vertex position Mo. For example, in order to determine the calibration status, a calibration reference position O1 in the XY direction is set. For example, in this embodiment, the calibration reference position O1 is set to a position where the corneal vertex position coincides with the optical axis L4 (L4R, L4L) of the subjective ophthalmological device 1 (the optical axis of the optical path through which the light beam reflected by the concave mirror 85 passes). For example, the calibration reference position O1 is the calibration reference position used in the subjective ophthalmological device 1. In addition, for example, a calibration allowable range A1 for determining whether the calibration is appropriate is set in a predetermined area centered on the calibration reference position O1.

[0168] Figure 10 This figure is used to explain calibration control. For example, the control unit 70 calculates the calibration offset Δd between the calibration reference position O1 and the corneal vertex position Mo. The control unit 70 drives the deflection mirror 81 to perform calibration in the XY directions so that the calibration offset Δd falls within the calibration allowable range A1.

[0169] The control unit 70 also calculates the calibration offset Δd in the Z direction by calculating (comparing) the image ratio (a / b) between the image spacing a of the marker images Ma and Me at infinity and the image spacing b of the marker images Mh and Mf at finite distance. When the operating distance (distance in the Z direction) between the examinee's eye and the subjective ophthalmology apparatus 1 shifts, the spacing between the infinity markers Ma and Me remains largely unchanged, while the spacing between the marker images Mh and Mf changes. The control unit 70 utilizes this characteristic to calculate the calibration offset in the direction of the examinee's operating distance (for details, see Japanese Patent Application Laid-Open No. 6-46999).

[0170] In the Z direction, similarly to the XY directions, the control unit 70 also determines the calibration offset Δd relative to the calibration reference position in the Z direction. The control unit 70 drives and controls the measuring unit 7 so that the calibration offset Δd falls within the calibration allowable range A1 in the Z direction, thereby performing Z-direction calibration.

[0171] Here, when the calibration offset Δd in the X, Y, and Z directions enters the calibration tolerance range A1, the control unit 70 stops driving the deflecting mirror 81 and the measuring unit 7 and outputs a calibration completion signal. Furthermore, after calibration is complete, the control unit 70 continuously monitors the calibration offset Δd. If the calibration offset Δd exceeds the calibration tolerance range A1, the control unit 70 restarts automatic calibration. Specifically, the control unit 70 controls (tracks) the imaging unit (deflecting mirror 81 and measuring unit 7) to follow the eye E so that the calibration offset Δd remains within the calibration tolerance range A1.

[0172] Furthermore, in this embodiment, an example is shown in which the control unit 70 automatically performs calibration control. However, the calibration method is not limited to this. For example, the control unit 70 may perform calibration as follows. Specifically, the control unit 70 may display a mark on the monitor 4 that electronically indicates the calibration reference position. The examiner adjusts the positional relationship between the calibration reference position and the eye under examination by operating the monitor 4. In this case, for example, the control unit 70 may display a message on the monitor 4 when calibration in the X, Y, and Z directions is complete.

[0173] Alternatively, for example, the examiner may guide the examinee until the calibration state is appropriate (calibration is completed). In this case, the control unit 70 may determine that calibration in the XYZ directions is completed when the corneal vertex position enters the calibration allowable range and display this information on the monitor 4.

[0174] Objective measurement

[0175] Based on the calibration completion signal, the control unit 70 issues a trigger signal to start objective measurement (objective measurement). After issuing the trigger signal to start objective measurement, the control unit 70 emits a measuring beam from the objective measurement optical system 10. Each measuring beam passes through the deflecting mirrors 81R and 81L, is reflected by the concave mirror 85, and then projected onto the fundus of the eye being examined. The measuring light reflected from the fundus is then reflected by the deflecting mirror 81R (81L) via the concave mirror 85. The imaging element 22 then receives the measuring beam and captures a measurement image.

[0176] For example, when measuring the objective ocular refractive power, a preliminary measurement of the ocular refractive power can first be performed. Based on the results of the preliminary measurement, the display 31 can be moved along the optical axis L2 to create a cloud over the eye E being examined. That is, the display 31 can be moved once to a focused position relative to the eye E being examined. Subsequently, the ocular refractive power of the clouded eye can be measured. In this measurement, a measurement image is captured by the imaging element 22. The output signal from the imaging element 22 is stored as image data (measurement image) in the memory 72. The control unit 70 then analyzes the annular image stored in the memory 72 to determine the refractive power values in each meridian direction. The control unit 70 performs predetermined processing on this refractive power to determine the objective ocular refractive power (objective value) for far vision, including the S (spherical power), C (astigmatism), and A (axis angle of astigmatism) of the eye being examined. The obtained objective value for far vision is stored in the memory 72.

[0177] During the objective ocular refractive power measurement described above, the control unit 70 can correct optical aberrations generated in the optical path of the objective measurement optical system 10 by controlling the correcting optical system 90. In this case, the control unit 70 retrieves from the memory 72 a correction amount corresponding to the refractive power measured by the objective measurement optical system 10. The control unit 70 controls the correcting optical system 90 based on the retrieved aberration correction amount.

[0178] More specifically, a correction amount is set based on the ocular refractive power obtained in the preliminary measurement. Based on the set correction amount, the correcting optical system 90 is driven. This allows the main measurement to be performed while aberrations generated by the optical path of the objective measurement optical system 10 are corrected. Consequently, the objective ocular refractive power can be measured with high precision. Furthermore, when the ocular refractive power is measured continuously (for example, when the main measurement is performed multiple times), the correcting optical system 90 can be controlled based on the results of each measurement.

[0179] Furthermore, in the above description, the objective ocular refractive power is measured for distance vision. However, this is not limiting. The objective ocular refractive power can also be measured when a sight mark is presented at a near distance, i.e., when near vision is present. Furthermore, the objective ocular refractive power of the left and right eyes can be measured simultaneously or at different times.

[0180] Subjective measurement

[0181] After the objective refractive power measurement is completed and the monitor (which also serves as the operating unit in this embodiment) 4 is operated, the measurement mode is switched to the subjective distance vision measurement mode (subjective refractive power measurement mode). The control unit 70 can drive the corrective optical system 60 based on the objective refractive power (spherical power S, astigmatism C, astigmatism axis angle A) of the examined eye obtained from the objective refractive power measurement for distance vision to correct the refractive error of the examined eye.

[0182] More specifically, the display 31 can be moved along the optical axis L2 based on the spherical power S measured for objective farsightedness. As a result, the refractive error associated with the spherical power of the examined eye is corrected. Furthermore, the astigmatism correction optical system 63 can be driven based on the astigmatism power C and the astigmatism axis angle A. As a result, the refractive error associated with the astigmatism of the examined eye is corrected.

[0183] In the visual acuity measurement mode, the control unit (correction setting unit) 70 can change the amount of aberration correction applied by the correcting optical system 90 based on the correction power applied by the correcting optical system 60. For example, when the correction power of the correcting optical system 60 is changed based on an operation signal from the monitor 4, the control unit 70 can change the amount of aberration correction applied by the correcting optical system 90 based on the changed correction power. This allows the presentation of an optotype with reduced aberrations even when the correction power based on the measurement results of the autorefractometer is changed. In other words, the control unit 70 can set the amount of correction for correcting the optical aberrations applied in the subjective measurement unit based on the correction power of the correcting optical system 60.

[0184] Furthermore, the control unit 70 can control the display 31 to display a desired visual acuity value optotype (e.g., an optotype with a visual acuity value of 0.8) on the optical axis L2. After the initial optotype is presented to the examinee's eye, the examiner performs distance visual acuity measurement on the examinee. The visual acuity value optotype displayed is switched by pressing a predetermined switch on the monitor 4.

[0185] For example, if the examinee's answer is correct, the examiner switches the displayed symbol to an optotype with a higher visual acuity value. On the other hand, if the examinee's answer is incorrect, the displayed symbol is switched to an optotype with a lower visual acuity value. In other words, the control unit 70 can switch the displayed optotype based on a signal indicating a change in visual acuity value from the monitor 4.

[0186] In addition, the examiner can change the correction power of the corrective optical system 60 using the monitor 4 to obtain the subjective refractive power of the examined eye (subjective value of far vision (spherical power S, astigmatism power C, astigmatism axis angle A)) when the mark is presented at the far vision distance.

[0187] Furthermore, the correction power of the corrective optical system 60 can be set to different values for the left and right eyes, or it can be set to the same value for both eyes. Furthermore, the subjective refractive powers of the left and right eyes can be measured simultaneously or at different times. Furthermore, when the subjective refractive powers of the left and right eyes are measured at different times, the optotype generated by the display 31 may not be displayed to the eye not being measured. Alternatively, the blur generated by the optical system 60 may not be corrected for the eye not being measured (for example, by adding a constant refractive power to the objective value).

[0188] After obtaining the subjective value for distance vision, the measurement mode can be switched to a subjective near vision measurement mode. After the measurement mode is switched to the near vision measurement mode, the control unit 70 can control the light projection optical system 30 to change the convergence angle generated by the deflection mirror 81, thereby presenting the sight mark at the near vision position. Furthermore, the presentation distance of the sight mark during the near vision test can be arbitrarily changed based on an operation signal from the monitor 4. As a result, the sight mark presentation distance can be changed from the distance vision position to the near vision position. Furthermore, by changing the sight mark presentation distance (near vision position) during the near vision test, the addition and accommodation power can be subjectively determined.

[0189] In this case, for example, the control unit 70 can obtain the aberration correction amount corresponding to the presentation distance of the sight mark from the memory 72 and control the correcting optical system 90 based on the obtained aberration correction amount. Furthermore, if the presentation distance of the sight mark is changed, the control unit 70 can change the amount of aberration correction performed by the correcting optical system 90 based on the changed sight mark presentation distance. Thus, even if the sight mark presentation distance is changed, a sight mark with reduced aberrations can be presented. In this case, the control unit 70 can change the aberration correction amount based on the correction power for the presentation distance of the sight mark.

[0190] Furthermore, the control unit 70 can change the convergence angles of the left and right sight mark beams by controlling the light deflection component in accordance with changes in the sight mark presentation position. In this case, for example, the control unit 70 can retrieve from the memory 72 an aberration correction amount corresponding to the deflection angle of the light deflection component corresponding to the convergence angle. The control unit 70 can control the correcting optical system 90 based on the retrieved aberration correction amount. Furthermore, when the convergence angle of the sight mark beam is changed, the control unit 70 can change the amount of aberration correction applied by the correcting optical system 90 in accordance with the changed convergence angle. This allows a sight mark with reduced aberrations to be presented even when the convergence angle changes.

[0191] In a near vision test, similar to a distance vision test, the examiner can, for example, change the correction power of the corrective optical system 60 using a predetermined switch on the monitor 4, and measure the subjective refractive power of the eye (near vision subjective value) when the sight mark is presented at the near vision distance. During the near vision test, the control unit 70 can change the aberration correction amount of the corrective optical system 90 in response to the change in correction power.

[0192] As described above, the overall inspection can be improved by changing the aberration correction amount during both objective and subjective inspections. Furthermore, in the above description, aberration correction is performed during both objective and subjective inspections. However, this is not limiting, and the amount of aberration generated by the correction optical system 90 can also be changed during either objective or subjective inspections.

[0193] In the above description, a correcting optical system 90 is provided, separate from the correcting optical system 60. However, the above embodiment is also applicable even when the correcting optical system 60 also serves as the correcting optical system 90. For example, an astigmatism correction optical system (astigmatism correction optical system) 63 may be used as the correcting optical system 90. In this case, for example, an aberration correction amount may be added to the astigmatism correction power and the axis angle. In other words, the control unit 70 (aberration correction unit) can use the correcting optical system 60 to correct the optical aberrations generated in the subjective measurement unit.

[0194] Furthermore, in the above-described configuration, the optical system is designed so that the optical axis of the measuring optical system is positioned on the optical axis of the concave mirror 85. This suppresses aberrations caused by the concave mirror 85. Consequently, the amount of aberration correction by the aforementioned correction optical system 90 can be reduced. However, this embodiment is also applicable to configurations in which the optical axis of the measuring optical system is positioned off-axis from the concave mirror 85.

[0195] <Auxiliary optical components>

[0196] In addition, when the eye under examination is an eye with strong refractive error, the subjective measurement optical system 25 can be configured with auxiliary optical components in its optical path. The auxiliary optical components can be, for example, lenses, prisms, and reflectors. When the refractive power value of the eye under examination is large, there is a case where the optical aberration cannot be corrected by relying solely on the correction optical system 90. Therefore, the optical aberration that cannot be corrected by relying solely on the correction optical system 90 can be corrected by using auxiliary optical components. As a result, the measurement can be performed with high precision. In more detail, for example, when the refractive power value of the eye under examination is 13.0D, the subject is given a 10.0D auxiliary optical component (for example, a false frame). The control unit 70 corrects the measurement result obtained by measurement in this state in consideration of the correction power of the auxiliary optical component. For example, when the measurement result is 3.0D, the control unit 70 corrects the measurement result and outputs a result such as the refractive power value of the subject is 13.0D.

[0197] In this case, the control unit (determination unit) 70 can perform a determination process to determine whether an auxiliary optical component is needed based on the refractive power of the eye obtained by the objective measurement unit. Furthermore, the control unit (insertion and removal unit) 70 can control the insertion or removal of the auxiliary optical component in the optical path relative to the subjective measurement optical system 25 based on the result of the determination process. Thus, the auxiliary optical component is automatically inserted or removed, so that the measurement can be performed easily and with high precision. In addition, the auxiliary optical component is particularly effective for small devices, such as the subjective eye examination device 1 in this embodiment. That is, for example, when the distance from the concave mirror 85 to the eye to be examined is small, the change in the amount of aberration caused by the correction degree is likely to be large. Therefore, it is better to use auxiliary optical components to correct optical aberrations that cannot be corrected by the correction optical system 90 alone.

[0198] Furthermore, and not limited to this, the control unit (display unit) 70 may display a report based on the results of the determination process on the monitor 75. When the subjective measurement optical system 25 displays a report indicating the need for auxiliary optical components, the examiner may be prompted to place auxiliary optical components in its optical path. In this case, the examinee may install the auxiliary lens. In this case, the examinee may be informed of the necessity of the auxiliary optical components. Therefore, the examinee can easily recognize the need for the auxiliary optical components. This prevents the examinee from forgetting to use the auxiliary optical components.

[0199] Furthermore, in the above-described configuration, optical aberrations generated by the optical path of the measurement optical system are optically corrected by the correction optical system 90. However, this is not limiting, and other correction processes may also be performed. For example, aberrations of the measurement image of the objective measurement optical system 10 may be corrected based on the optical aberrations generated by the optical path of the measurement optical system. Furthermore, objective values of the objective measurement optical system 10 may also be corrected based on the optical aberrations generated by the optical path of the measurement optical system.

[0200] Furthermore, the aberration correction technology in this embodiment can also be applied to a subjective ophthalmology device that does not have an objective measurement unit. Furthermore, for example, the aberration correction technology in this embodiment can also be applied to a subjective ophthalmology device that does not have a corrective optical system and a concave mirror 85. The corrective optical system includes a pair of right and left corrective optical systems for the right eye and the left eye, and the concave mirror 85 is shared by both the right-eye optical path, which includes the right-eye corrective optical system, and the left-eye optical path, which includes the left-eye corrective optical system. In other words, the aberration correction technology in this embodiment can be applied to a subjective ophthalmology device that includes a subjective measurement unit that subjectively measures the optical properties of the eye being examined. This subjective ophthalmology unit includes a light projection optical system that projects a target beam toward the eye being examined, a corrective optical system disposed in the optical path of the light projection optical system and that modifies the optical properties of the target beam, and optical components that guide the target beam corrected by the corrective optical system toward the eye being examined and form an image of the corrected target beam in front of the eye being examined. The subjective ophthalmological apparatus may include: a correction setting unit that sets a correction amount for correcting optical aberrations generated in the subjective measurement unit based on the correction power of the corrective optical system; and an aberration correcting unit that corrects the optical aberrations generated in the subjective measurement unit based on the correction amount set by the correction setting unit.

[0201] <Changes to the calibration tolerance range>

[0202] The control unit 70 can set the calibration allowable range for determining the calibration state based on the eye's refractive power. For example, the control unit 70 sets the calibration allowable range for determining the calibration state between the eye under test and the subjective measurement unit when performing subjective eye refractive power measurement based on the objective eye refractive power (spherical power S, astigmatism power C, astigmatism axis angle A) of the eye under test obtained from the objective refractive power measurement during farsightedness. That is, for example, the control unit (acquisition unit, setting unit (calibration setting unit)) 70 can acquire the eye refractive power of the eye under test E measured objectively. Furthermore, the control unit 70 can set the calibration allowable range for determining the calibration state between the eye under test E and the subjective measurement unit based on the eye's refractive power. The following describes the setting of the calibration allowable range in the XY direction. In addition, the calibration allowable range in the Z direction is also set in the same manner.

[0203] Furthermore, in this embodiment, as an example, a configuration for changing the calibration tolerance range using the objective refractive power of the examined eye obtained by the objective measurement unit of the subjective ophthalmological apparatus 1 is described. However, the configuration for changing the calibration tolerance range is not limited to this configuration. The configuration for changing the calibration tolerance range can, for example, receive and use measurement results obtained by a different objective measurement apparatus.

[0204] This will be described in more detail. For example, in this embodiment, a calibration tolerance range is created for each spherical power. Of course, the calibration tolerance range can be set based on the eye's refractive power. For example, the differences in astigmatism and axial angles for each spherical power can be taken into account, and calibration tolerance ranges can be created for each spherical power, each astigmatism degree, and each axial angle.

[0205] Figures 11A to 11C This figure explains how to change the calibration allowable range. Figure 11A The calibration allowable range when the diopter value (D) is 0D is shown. Figure 11B The calibration allowable range when the diopter value is 2.0D is shown. Figure 11C The calibration allowable range for a diopter value of 5.0D is shown. Furthermore, the calibration allowable range is set, for example, based on the eye's refractive power. For example, the calibration allowable range is calculated and set in advance through simulations or experiments. Of course, the calibration allowable range can also be calculated and set based on the eye's refractive power before or after calibration control.

[0206] For example, the control unit 70 sets the calibration allowable range to be smaller as the diopter value increases from 0D to the positive direction (positive side) or the negative direction (negative side) with 0 diopter (0D) as the reference. Figure 11B The calibration allowable range A2 is set to be smaller than the diopter value of 2.0D. Figure 11A The calibration allowable range A1 is small when the diopter value is 0D. Figure 11C The calibration allowable range A3 is set to be smaller than the diopter value of 5.0D. Figure 11B The calibration allowable range A2 in the case of a diopter value of 2.0 D is shown to be even smaller.

[0207] For example, if the calibration allowable range is set larger than the appropriate calibration range for obtaining high-precision measurement results for an eye under examination having specified optical characteristics, the accuracy of the measurement results when subjectively measuring the optical characteristics of the eye under examination will decrease. Furthermore, if the calibration allowable range is set smaller than the appropriate calibration range for obtaining high-precision measurement results for an eye under examination having specified optical characteristics, it will be difficult to perform calibration when subjectively measuring the optical characteristics of the eye under examination. In the subjective ophthalmological examination device 1 of this embodiment, the calibration allowable range is changed based on the refractive power of the eye. Thus, when subjectively measuring the optical characteristics of the eye under examination, the optical characteristics of the eye under examination can be measured with high accuracy. Furthermore, for example, when subjectively measuring the optical characteristics of the eye under examination, calibration can be performed efficiently.

[0208] For example, the subjective ophthalmological examination apparatus 1 in this embodiment reduces the calibration tolerance when the diopter value increases from 0 diopter to a positive or negative direction. This can prevent a decrease in the accuracy of the measurement results when subjectively measuring the optical characteristics of the eye under examination. Furthermore, for example, when the diopter value approaches 0 diopter with 0 diopter as the reference, the calibration tolerance is increased. This can prevent difficulties in performing the calibration operation when subjectively measuring the optical characteristics of the eye under examination.

[0209] The subjective ophthalmological examination apparatus 1 in this embodiment also includes a corrective optical system 60. The corrective optical system 60 comprises a pair of left and right corrective optical systems for the right eye and the left eye, and is disposed in the optical path of the light projection optical system 30 to modify the optical properties of the sight mark beam. Furthermore, the subjective ophthalmological examination apparatus 1 in this embodiment includes a subjective measurement unit having a concave mirror 85 shared by both the right-eye optical path including the right-eye corrective unit and the left-eye optical path including the left-eye corrective unit. This concave mirror 85 guides the sight mark beam that has passed through the corrective optical system 60 toward the eye being examined and forms an image of the sight mark beam that has passed through the corrective optical system 60 in front of the eye being examined.

[0210] In the subjective ophthalmological examination device of this embodiment, it is particularly effective to change the calibration allowable range based on the refractive power of the eye. For example, in previous subjective measurement units, a corrective optical system is placed in front of the eye to be examined. When performing a subjective measurement, the examinee looks into the inspection window of the corrective optical system. Because the examinee looks into the inspection window, the position of the examinee's eye does not shift significantly. Therefore, the optical characteristics of the examinee's eye can be measured subjectively and with high precision. However, in the subjective measurement unit of the subjective ophthalmological examination device 1 of this embodiment, the refractive power of the examinee's eye is measured without placing the corrective optical system in front of the eye. In such a device, the position of the examinee's eye may shift significantly. Therefore, a calibration operation is required. Therefore, in a subjective measurement unit that measures the refractive power of the examinee's eye without placing the corrective optical system in the vicinity of the eye, it is preferable to perform a calibration operation efficiently, especially when subjectively measuring the optical characteristics of the examinee's eye. In addition, in a subjective ophthalmological device having a subjective measurement unit that measures the refractive power of the eye under examination without arranging a corrective optical system in front of the eye, it is preferable to set a calibration allowable range for measuring the optical characteristics of the eye under examination with high precision, especially when subjectively measuring the optical characteristics of the eye under examination.

[0211] In addition, the subjective ophthalmological examination device 1 in this embodiment includes an objective measurement unit having an objective measurement optical system 10. The objective measurement optical system 10 emits measurement light toward the fundus of the eye to be examined and receives its reflected light. The objective measurement unit objectively measures the optical characteristics of the eye to be examined. Therefore, in the subjective ophthalmological examination device 1 in this embodiment, the control unit 70 can obtain the eye's refractive power based on the measurement results measured by the objective measurement unit. Therefore, the calibration allowable range can be changed with a single device. As a result, the subjective ophthalmological examination device 1 in this embodiment can use a simple structure to measure the optical characteristics of the eye to be examined with high precision when subjectively measuring the optical characteristics of the eye to be examined. In addition, the subjective ophthalmological examination device 1 in this embodiment can use a simple structure to efficiently perform calibration operations when subjectively measuring the optical characteristics of the eye to be examined.

[0212] Furthermore, the technology for changing the calibration allowable range in this embodiment can also be applied to a subjective ophthalmological device that does not include an objective measurement unit. Furthermore, the technology for changing the calibration allowable range in this embodiment can be applied, for example, to a subjective ophthalmological device that does not include at least one of a corrective optical system and a concave mirror 85, wherein the corrective optical system includes a corrective optical system for the right eye to be examined and a corrective optical system for the left eye to be examined, arranged as a left and right pair. That is, the technology for changing the calibration allowable range in this embodiment can be applied to the following subjective ophthalmological device. This subjective ophthalmological device includes a subjective measurement unit. This subjective measurement unit includes a light projection optical system that projects a target light beam toward the eye to be examined, and a corrective optical system that is arranged in the optical path of the light projection optical system and changes the optical characteristics of the target light beam, thereby subjectively measuring the optical characteristics of the eye to be examined. The subjective ophthalmological examination apparatus may further include: an acquisition unit for acquiring the objectively measured refractive power of the examined eye; and a setting unit for setting a calibration allowable range for determining a calibration state between the examined eye and the subjective measurement unit based on the refractive power.

[0213] Furthermore, the embodiments of the present invention are not limited to the apparatus described in this embodiment. For example, subjective ophthalmological examination software (program) that performs the functions of the above-described embodiments can be provided to a system or apparatus via a network or various storage media. The control device (e.g., CPU) of the system or apparatus can then read and execute the program.

[0214] The present invention may be implemented as the following first to sixteenth subjective eye examination apparatuses and first subjective eye examination program.

[0215] A first subjective ophthalmological apparatus is a subjective ophthalmological apparatus comprising a subjective measurement unit, the subjective measurement unit comprising a light-projecting optical system, a corrective optical system, and an optical component, and subjectively measuring the optical characteristics of an eye to be examined. The light-projecting optical system projects a target light beam toward the eye to be examined. The corrective optical system comprises a right-eye corrective optical system and a left-eye corrective optical system arranged as a pair on the left and right sides, and is disposed in an optical path of the light-projecting optical system to change the optical characteristics of the target light beam. The optical component is shared by both the right-eye optical path including the right-eye corrective optical system and the left-eye optical path including the left-eye corrective optical system, and guides the target light beam corrected by the corrective optical system toward the eye to be examined. This subjective ophthalmological apparatus is characterized in that it comprises an objective measurement unit comprising a measurement optical system for emitting measurement light toward the fundus of the eye to be examined and receiving reflected light thereof, and objectively measuring the optical characteristics of the eye to be examined via the optical component disposed in the optical path of the measurement optical system.

[0216] The second subjective ophthalmological apparatus is based on the first subjective ophthalmological apparatus, wherein an optical axis between the optical component and the examined eye in the subjective measurement section and an optical axis between the optical component and the examined eye in the objective measurement section are coaxial.

[0217] The third subjective ophthalmological device is based on the first or second subjective ophthalmological device and is characterized in that the above-mentioned optical component is a concave mirror, and the above-mentioned subjective measurement part guides the above-mentioned visual target light beam toward the above-mentioned eye to be examined by reflecting the above-mentioned visual target light beam corrected by the above-mentioned corrective optical system toward the above-mentioned eye to be examined by the above-mentioned concave mirror, and guides the above-mentioned eye to be examined in a manner that makes the image of the above-mentioned visual target light beam corrected by the above-mentioned corrective optical system be at an optically prescribed inspection distance.

[0218] The fourth subjective ophthalmological device is based on any one of the first to third subjective ophthalmological devices and is characterized in that it comprises: an offset detection unit, which detects the position offset of the image of the above-mentioned corrective optical system relative to the above-mentioned eye to be examined; a deflection component, which is arranged between the above-mentioned corrective optical system and the above-mentioned eye to be examined, and is respectively provided as a left and right pair; a driving unit, which drives the above-mentioned deflection component; and a correction unit, which controls the above-mentioned driving unit based on the detection result detected by the above-mentioned offset detection unit, so as to deflect the apparent light beam used to guide the image of the above-mentioned corrective optical system toward the above-mentioned eye to be examined, thereby optically correcting the formation position of the above-mentioned image.

[0219] The fifth subjective ophthalmological device is a subjective ophthalmological device having a subjective measuring section, which has a light-projecting optical system, a correcting optical system and an optical component, and subjectively measures the optical characteristics of the above-mentioned eye to be examined, wherein the above-mentioned light-projecting optical system projects a sight mark beam toward the eye to be examined, the above-mentioned correcting optical system is arranged in the optical path of the above-mentioned light-projecting optical system to change the optical characteristics of the above-mentioned sight mark beam, and the above-mentioned optical component guides the above-mentioned sight mark beam corrected by the above-mentioned correcting optical system toward the above-mentioned eye to be examined. The above-mentioned subjective ophthalmological device is characterized in that it comprises: a correction setting section, which sets a correction amount for correcting the optical aberration generated in the above-mentioned subjective measuring section based on the correction power of the above-mentioned correcting optical system; and a correction section, which corrects the above-mentioned optical aberration generated in the above-mentioned subjective measuring section based on the above-mentioned correction amount set by the above-mentioned correction setting section.

[0220] The sixth subjective ophthalmological apparatus is a subjective ophthalmological apparatus including a subjective measuring unit, the subjective measuring unit including a light-projecting optical system, a correcting optical system, and an optical component, and subjectively measuring the optical characteristics of the eye to be examined, wherein the light-projecting optical system projects a sight mark beam toward the eye to be examined, the correcting optical system is arranged in an optical path of the light-projecting optical system to change the optical characteristics of the sight mark beam, and the optical component guides the sight mark beam corrected by the correcting optical system toward the eye to be examined. The subjective ophthalmological apparatus is characterized in that it includes: a control unit that changes the presentation distance of the sight mark generated by the sight mark beam by changing the formation position of the image of the sight mark beam; a correction setting unit that sets a correction amount for correcting optical aberrations generated in the subjective measuring unit based on the presentation distance; and a correction unit that corrects the optical aberrations generated in the subjective measuring unit based on the correction amount set by the correction setting unit.

[0221] A seventh subjective ophthalmological apparatus is a subjective ophthalmological apparatus comprising a subjective measuring unit, the subjective measuring unit comprising a light-projecting optical system, a correcting optical system, and an optical component, and subjectively measuring the optical characteristics of the eye to be examined, wherein the light-projecting optical system projects a target light beam toward the eye to be examined, the correcting optical system is arranged in an optical path of the light-projecting optical system to change the optical characteristics of the target light beam, and the optical component guides the target light beam corrected by the correcting optical system toward the eye to be examined. The subjective ophthalmological apparatus is characterized in that it comprises: a convergence angle changing unit that changes the convergence angle of the target light beam emitted from the right-eye optical path and the left-eye optical path; a correction setting unit that sets a correction amount for correcting optical aberrations generated in the subjective measuring unit based on the convergence angle; and a correction unit that corrects the optical aberrations generated in the subjective measuring unit based on the correction amount set by the correction setting unit.

[0222] An eighth subjective eye examination apparatus is the subjective eye examination apparatus according to any one of the fifth to seventh subjective eye examination apparatuses, wherein the corrective optical system also serves as the correction unit.

[0223] The ninth subjective eye examination apparatus is characterized in that, in addition to the fifth subjective eye examination apparatus, it includes an inserting and removing unit that controls insertion and removal of an auxiliary optical component in the optical path of the subjective measurement unit.

[0224] The tenth subjective ophthalmological device is based on the ninth subjective ophthalmological device and is characterized in that it comprises: a determination unit that determines whether an auxiliary optical component is needed based on the eye refractive power obtained by the objective measurement unit, and the above-mentioned insertion and removal unit controls the insertion or removal of the above-mentioned auxiliary optical component in the optical path of the above-mentioned subjective measurement unit based on the determination result of the above-mentioned determination unit.

[0225] The 11th subjective ophthalmological apparatus is characterized in that it comprises, based on the 5th subjective ophthalmological apparatus, a determination unit for determining whether auxiliary optical components are necessary based on the eye refractive power obtained by the objective measurement unit; and a display unit for displaying report information based on the determination result of the determination unit on a monitor.

[0226] The 12th subjective ophthalmological examination device is based on any one of the 5th to 11th subjective ophthalmological examination devices, and is characterized in that the above-mentioned corrective optical system has a corrective optical system for the right eye to be examined and a corrective optical system for the left eye to be examined, which are arranged as a left and right pair, and the above-mentioned optical components are shared by the right eye optical path including the above-mentioned corrective optical system for the right eye and the left eye optical path including the above-mentioned corrective optical system for the left eye.

[0227] The 13th subjective ophthalmological device is a subjective ophthalmological device equipped with a subjective measuring unit, the subjective measuring unit having a light-projecting optical system for projecting a sight mark beam toward an eye to be examined and a corrective optical system located in the optical path of the light-projecting optical system for changing the optical characteristics of the sight mark beam, and subjectively measuring the optical characteristics of the eye to be examined, and is characterized in that it comprises: an acquiring unit for acquiring the objectively measured refractive power of the eye to be examined; and a setting unit for setting a calibration allowable range for determining the calibration state of the eye to be examined and the subjective measuring unit based on the refractive power of the eye.

[0228] The 14th subjective ophthalmological apparatus is based on the 13th subjective ophthalmological apparatus, wherein the setting unit is set to reduce the calibration allowable range as the diopter value increases from 0 diopter in a positive or negative direction, with 0 diopter as the reference.

[0229] The 15th subjective ophthalmological device is based on the 13th or 14th subjective ophthalmological device, and is characterized in that the above-mentioned corrective optical system has a corrective optical system for the right eye to be examined and a corrective optical system for the left eye to be examined, which are arranged as a left and right pair, are arranged in the optical path of the above-mentioned light projection optical system, and change the optical characteristics of the above-mentioned sight mark light beam; the above-mentioned subjective measurement part has an optical component, which is shared by the right eye optical path including the above-mentioned corrective optical system for the right eye and the left eye optical path including the above-mentioned corrective optical system for the left eye, and guides the above-mentioned sight mark light beam corrected by the above-mentioned corrective optical system to the above-mentioned eye to be examined.

[0230] The 16th subjective ophthalmological device is based on any one of the 13th to 15th subjective ophthalmological devices, and is characterized in that it has an objective measuring unit, which has a measuring optical system that emits measurement light to the fundus of the eye to be examined and receives its reflected light, and objectively measures the optical characteristics of the above-mentioned eye to be examined, and the above-mentioned acquisition unit obtains the eye refractive power of the above-mentioned eye to be examined based on the measurement result generated by the above-mentioned objective measuring unit.

[0231] The first subjective ophthalmological examination program is used in a subjective ophthalmological examination device, which includes a subjective measuring unit, the subjective measuring unit having a light-projecting optical system that projects a sight mark beam toward a subject's eye, and a corrective optical system that is located in the optical path of the light-projecting optical system and changes the optical characteristics of the sight mark beam, and subjectively measures the optical characteristics of the subject's eye. The subjective ophthalmological examination program is characterized in that it causes the subjective ophthalmological examination device to execute the following steps: an acquisition step for acquiring the refractive power of the subject's eye by executing a processor of the subjective ophthalmological examination device, and a setting step for setting a calibration allowable range for performing a calibration operation between the subject's eye and the subjective measuring unit based on the refractive power of the eye.

[0232] The above detailed description is provided for purposes of illustration and description. However, many modifications and variations are possible based on this description. This is not intended to be an exhaustive list of various descriptions of the subject matter. Although the subject matter is described in detail with respect to structural features and / or methods, it should not be construed that the subject matter of the claims is necessarily limited to these specific features or methods. In other words, the specific features and methods disclosed above are an example of implementing the claims.

[0233] The detailed description has been presented for purposes of illustration and description. Numerous variations and modifications are possible in light of the above teachings. The detailed description is not intended to be exhaustive or to limit the subject matter described herein. Although the subject matter has been described in terms of specific structural features and / or methodological procedures, it should be understood that the subject matter defined in the claims is not necessarily limited to the specific features or procedures described. Rather, the specific features and procedures described are described as examples of implementing the claims.

Claims

1. A subjective eye examination device, characterized in that: have: a subjective measurement unit comprising a light-projecting optical system, a corrective optical system, and optical components, and subjectively measuring the optical characteristics of an eye to be examined, wherein the light-projecting optical system projects a target light beam from a display toward the eye to be examined, the corrective optical system comprising a right-eye corrective optical system and a left-eye corrective optical system arranged as a pair on the left and right sides, and disposed in an optical path of the light-projecting optical system, and altering the optical characteristics of the target light beam, and the optical components being shared by both the right-eye optical path including the right-eye corrective optical system and the left-eye optical path including the left-eye corrective optical system, and guiding the target light beam corrected by the corrective optical systems toward the eye to be examined; and an objective measuring unit comprising a measuring optical system including a projection optical system for emitting measuring light toward the fundus of the eye to be examined and a light receiving optical system for receiving reflected light from the fundus, and objectively measuring the optical characteristics of the eye to be examined via the optical component arranged in the optical path of the measuring optical system; The above-mentioned optical components include a concave mirror, The subjective measurement unit guides the optical target beam corrected by the corrective optical system toward the eye to be examined by reflecting the optical target beam toward the eye to be examined by the concave mirror, and guides the image of the optical target beam corrected by the corrective optical system toward the eye to be examined in such a manner that the distance between the position where the image is formed and the eye to be examined, as detected by the examinee, becomes an optically prescribed inspection distance. The projection optical system of the objective measurement section projects the measurement light from a measurement light source different from the display onto the fundus of the eye under examination via the concave mirror. The light-receiving optical system of the objective measurement section takes out fundus reflected light obtained by reflecting the measurement light off the fundus as a fundus reflected image via the concave mirror, and captures the fundus reflected image with a camera.

2. The subjective eye examination device according to claim 1, wherein An optical axis between the optical component and the eye to be examined in the subjective measurement section and an optical axis between the optical component and the eye to be examined in the objective measurement section are coaxial.

3. The subjective eye examination device according to claim 1, wherein Also features: a deviation detecting unit configured to detect a positional deviation of the image of the corrective optical system relative to the eye to be examined; a pair of deflection members disposed between the corrective optical system and the eye to be examined, the deflection members being provided on the left and right sides; a driving unit that drives the deflection member; The correction unit controls the driving unit based on the detection result of the deviation detection unit to deflect the apparent light beam used to guide the image of the corrective optical system toward the inspected eye, thereby optically correcting the formation position of the image.

4. The subjective eye examination device according to claim 1, wherein Also features: a correction setting unit that sets a correction amount for correcting the optical aberration generated in the subjective measurement unit based on the correction power of the corrective optical system; and An aberration correcting section corrects the optical aberration generated in the subjective measurement section based on the correction amount set by the correction setting section.

5. The subjective eye examination device according to claim 1, wherein Also features: a control unit that changes a presentation distance of the sight mark generated by the sight mark beam by changing a formation position of an image of the sight mark beam; a correction setting unit that sets a correction amount for correcting the optical aberration generated in the subjective measurement unit based on the presentation distance; as well as An aberration correcting section corrects the optical aberration generated in the subjective measurement section based on the correction amount set by the correction setting section.

6. The subjective eye examination device according to claim 1, wherein Also features: a convergence angle changing unit configured to change the convergence angles of the sight mark light beams emitted from the right-eye optical path and the left-eye optical path; a correction setting unit configured to set a correction amount for correcting the optical aberration generated in the subjective measurement unit based on the convergence angle; as well as An aberration correcting section corrects the optical aberration generated in the subjective measurement section based on the correction amount set by the correction setting section.

7. The subjective eye examination device according to claim 4, wherein: Also features: a determination unit that determines whether an auxiliary optical component is necessary based on the eye refractive power obtained by the objective measurement unit; and An inserting and removing section controls insertion or removal of the auxiliary optical component in the optical path of the subjective measurement section based on the determination result of the determination section.

8. The subjective eye examination device according to claim 4, wherein Also features: a determination unit that determines whether an auxiliary optical component is necessary based on the eye refractive power obtained by the objective measurement unit; and A display unit displays report information based on the determination result of the determination unit on a monitor.

9. The subjective eye examination device according to claim 1, wherein Also features: an acquisition unit that acquires the objectively measured refractive power of the eye to be examined; and A setting unit sets a calibration allowable range for determining a calibration state between the eye to be examined and the subjective measurement unit based on the eye refractive power.

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