Ophthalmic device

Abstract

The present application provides a new technology for measuring characteristics of both eyes with high precision at low cost and with saving space. An ophthalmic apparatus includes an objective lens, an OCT optical system, an optical axis switching member, a control section, and an intraocular parameter calculation section. The OCT optical system projects measurement light onto a left eye to be examined arranged on a first measurement optical axis or a right eye to be examined arranged on a second measurement optical axis via the objective lens, and detects interference light of return light of the measurement light from the left eye to be examined or the right eye to be examined and reference light via a reference light path. The optical axis switching member switches the optical axis of the OCT optical system to substantially coincide with the first measurement optical axis or the second measurement optical axis. The control section controls the optical axis switching member. The intraocular parameter calculation section calculates an intraocular parameter of the left eye to be examined or the right eye to be examined based on a detection result of the interference light obtained in a state where the optical axis of the OCT optical system is switched to substantially coincide with the first measurement optical axis or the second measurement optical axis.

Description

TECHNICAL FIELD

[0001] The present application relates to an ophthalmic apparatus. BACKGROUND

[0002] An ophthalmic apparatus capable of performing a plurality of examinations and measurements on an eye to be examined is known. The examinations and measurements on the eye to be examined include subjective examinations and objective measurements. In the subjective examinations, results are obtained based on responses from the examinee. In the objective measurements, information on the eye to be examined is acquired mainly using physical methods without reference to the responses from the examinee.

[0003] For example, an ophthalmic apparatus capable of performing subjective examinations and objective measurements is disclosed in Patent Literature 1. In the ophthalmic apparatus, as the objective measurements, refraction power measurement, corneal shape measurement, and imaging and measurement using optical coherence tomography are capable of being performed. The ophthalmic apparatus is provided with an optical system common to the left and right eyes, and using the optical system, one of the left and right eyes is capable of being subjected to the subjective examinations and the objective measurements.

[0004] Further, for example, an ophthalmic apparatus capable of performing refraction power measurement on one of the left and right eyes using one optical system while presenting a fixation target to the left and right eyes independently is disclosed in Patent Literature 2.

[0005] In contrast thereto, for example, an ophthalmic apparatus provided with two optical systems independently provided for the left and right eyes and capable of performing refraction power measurement and corneal shape measurement on the left and right eyes simultaneously using the two optical systems is disclosed in Patent Literature 3.

[0006] Further, for example, an ophthalmic apparatus capable of simultaneously acquiring Hartmann images of the left and right eyes and simultaneously measuring wavefront aberrations of the left and right eyes is disclosed in Patent Literature 4.

[0007] Patent Literature 1: Japanese Patent Application Publication No. 2016-187461

[0008] Patent Literature 2: Japanese Patent Application Publication No. H6-304139

[0009] Patent Literature 3: Japanese Patent Application Publication No. 2019-062939

[0010] Patent Literature 4: U.S. Patent No. 8506079 SUMMARY

[0011] However, the structures disclosed in Patent Literature 1 and Patent Literature 2 have a structure of measuring one of the left and right eyes respectively, and cannot measure the characteristics of both eyes in a state where both eyes are open. In contrast, in the structure disclosed in Patent Literature 3, both eyes can be measured simultaneously in a state where both eyes are open, but this results in a large size and high cost of the apparatus. Further, the structure disclosed in Patent Literature 4 results in a large size of the apparatus in a case where measurement other than wavefront aberration measurement is performed, or results in a decrease in measurement accuracy in a preferred state in a case where measurement other than wavefront aberration measurement is performed.

[0012] The present application has been achieved in view of such circumstances, and one of the objects thereof is to provide a new technique capable of measuring characteristics of both eyes with high accuracy at low cost and with a small size.

[0013] One embodiment of the present application is an ophthalmic apparatus including: an objective lens; an OCT optical system that splits light from a light source into measurement light and reference light, and projects the measurement light to a left eye to be examined arranged on a first measurement optical axis or a right eye to be examined arranged on a second measurement optical axis via the objective lens, and detects interference light of the measurement light returned from the left eye to be examined or the right eye to be examined and the reference light via a reference light path; an optical axis switching member that switches an optical axis of the OCT optical system to substantially coincide with either one of the first measurement optical axis and the second measurement optical axis; a control section that controls the optical axis switching member; and an intraocular parameter calculation section that calculates an intraocular parameter of the left eye to be examined based on a detection result of the interference light obtained in a state where the optical axis of the OCT optical system is switched to substantially coincide with the first measurement optical axis, and calculates an intraocular parameter of the right eye to be examined based on a detection result of the interference light obtained in a state where the optical axis of the OCT optical system is switched to substantially coincide with the second measurement optical axis.

[0014] According to the present application, it is possible to provide a new technique capable of measuring characteristics of both eyes with high accuracy at low cost and with a small size. BRIEF DESCRIPTION OF DRAWINGS

[0015] Figure 1 is a schematic diagram showing a structure example of an optical system of an ophthalmic apparatus of the first embodiment.

[0016] Figure 2 is a schematic diagram showing a structure example of an optical system of an ophthalmic apparatus of the first embodiment.

[0017] Figure 3 is a schematic diagram for explaining an optical system of an ophthalmic apparatus of the first embodiment.

[0018] Figure 4 is a schematic diagram for explaining an optical system of an ophthalmic apparatus of the first embodiment.

[0019] Figure 5 is a schematic diagram showing a structure example of an optical system of the ophthalmic apparatus of the first embodiment.

[0020] Figure 6 is a schematic diagram showing a structure example of an optical system of the ophthalmic apparatus of the first embodiment.

[0021] Figure 7 is a schematic diagram for explaining an optical system of the ophthalmic apparatus of the first embodiment.

[0022] Figure 8 is a schematic diagram for explaining an optical system of the ophthalmic apparatus of the first embodiment.

[0023] Figure 9A is a schematic diagram for explaining an optical system of the ophthalmic apparatus of the first embodiment.

[0024] Figure 9B is a schematic diagram for explaining an optical system of the ophthalmic apparatus of the first embodiment.

[0025] Figure 10 is a schematic diagram showing a structure example of a processing system of the ophthalmic apparatus of the first embodiment.

[0026] Figure 11 is a schematic diagram showing a structure example of a processing system of the ophthalmic apparatus of the first embodiment.

[0027] Figure 12 is a schematic diagram showing a flow of an operation example of the ophthalmic apparatus of the first embodiment.

[0028] Figure 13 is a schematic diagram showing a flow of an operation example of the ophthalmic apparatus of the first embodiment.

[0029] Figure 14 is a schematic diagram showing a structure example of an optical system of the ophthalmic apparatus of the second embodiment.

[0030] Figure 15 is a schematic diagram showing a structure example of an optical system of the ophthalmic apparatus of the second embodiment.

[0031] Figure 16 is a schematic diagram for explaining an optical system of the ophthalmic apparatus of the second embodiment.

[0032] Figure 17 is a schematic diagram for explaining an optical system of the ophthalmic apparatus of the second embodiment.

[0033] Figure 18 is a schematic diagram showing a structure example of an optical system of the ophthalmic apparatus of the second embodiment.

[0034] Figure 19 is a schematic diagram showing a configuration example of a processing system of an ophthalmic apparatus of a second embodiment.

[0035] Figure 20 is a schematic diagram showing a configuration example of an optical system of an ophthalmic apparatus of a third embodiment.

[0036] Figure 21 is a schematic diagram showing a configuration example of a processing system of an ophthalmic apparatus of the third embodiment.

[0037] (Explanation of Reference Numerals)

[0038] 1, 1a, 1b: ophthalmic apparatus

[0039] 2: XY alignment system

[0040] 3: corneal measurement system

[0041] 4, 4L, 4R: fixation projection system

[0042] 5: anterior eye portion observation system

[0043] 6: reflection measurement projection system

[0044] 7: reflection measurement light receiving system

[0045] 8: OCT optical system

[0046] 9, 9a, 9b: processing section

[0047] 40, 40L, 40R: fixation unit

[0048] 41, 41L, 41R: liquid crystal panel

[0049] 42, 43, 44, 42L, 43L, 44L, 42R, 43R, 44R: relay lens

[0050] 51: objective lens

[0051] 210, 210a, 210b: control section

[0052] 211, 211a, 211b: main control section

[0053] 300, 300a: measurement optical system

[0054] 400: target presentation section

[0055] CLr, CRr: cornea

[0056] EL: left eye to be examined

[0057] ELf, ERf: fundus

[0058] ER: right eye to be examined

[0059] ML, MR: dichroic mirror

[0060] ML1, MR1: reflecting mirror

[0061] OL, OR: measurement optical axis

[0062] SW: optical axis switching member DETAILED DESCRIPTION

[0063] Examples of embodiments of the ophthalmic apparatus of the present application are described in detail with reference to the accompanying drawings. Furthermore, the contents of the documents cited in this specification, any publicly known techniques, can be employed in the embodiments below.

[0064] The ophthalmic apparatus of the embodiments can perform predetermined examinations, measurements on both eyes in turn in a state where both eyes are open, while sharing an objective lens among a plurality of optical systems for performing a plurality of measurements of different kinds. In particular, the ophthalmic apparatus of the embodiments can perform OCT measurements on both eyes in turn using a single OCT optical system, and calculate intraocular parameters of each of both eyes. By sharing the OCT optical system and the objective lens in the OCT measurements of both eyes, miniaturization and cost reduction of the apparatus can be achieved.

[0065] In several embodiments, the ophthalmic apparatus further includes at least one of a subjective measurement optical system for performing a subjective measurement different from the OCT measurement and a subjective examination optical system for performing a subjective examination. In such an ophthalmic apparatus, by sharing the objective lens among a plurality of optical systems corresponding to the kinds of examinations, measurements, miniaturization and cost reduction of the apparatus can be achieved.

[0066] The subjective measurement is a measurement method of acquiring information about an eye to be examined mainly using a physical method without reference to a response from the examinee. The subjective measurement includes a measurement for acquiring a characteristic of the eye to be examined and a photographing for acquiring an image of the eye to be examined. Other subjective measurements include an intraocular pressure measurement, a fundus photographing, and the like. In several embodiments, the ophthalmic apparatus can perform a refractive power measurement (reflex measurement) and an OCT measurement as the subjective measurement. In several embodiments, the ophthalmic apparatus can perform a refractive power measurement, a corneal shape measurement, and an OCT measurement as the subjective measurement.

[0067] Hereinafter, a case where the ophthalmic apparatus of the embodiments performs OCT measurements on the anterior eye portion and the fundus is described. Hereinafter, in the embodiments, a case where a method using a spectral domain type OCT is described in particular detail. However, the structure of the embodiments can be applied to an ophthalmic apparatus using other types (for example, a swept source type, a time domain type) of OCT as well.

[0068] Self-examination is a measurement method that uses responses from the examinee to obtain information. Self-examination includes self-examination of refractive power and visual field, such as distance vision test, near vision test, contrast test, glare test, etc.

[0069] Hereinafter, the fundus conjugate position is the position that is optically approximately conjugate to the fundus of the examined eye in the fully aligned state, referring to the position or its vicinity that is optically conjugate to the fundus of the examined eye. Similarly, the pupil conjugate position is the position that is optically approximately conjugate to the pupil of the examined eye in the fully aligned state, referring to the position or its vicinity that is optically conjugate to the pupil of the examined eye.

[0070] In addition, in the following embodiments, the horizontal direction (left-right direction) orthogonal to the optical axis of the optical system is defined as the X direction, the vertical direction (up-down direction) orthogonal to the optical axis of the optical system is defined as the Y direction, and the optical axis direction (front-back direction) of the optical system is defined as the Z direction.

[0071] [First Implementation Method]

[0072] <Structure of an Optical System>

[0073] Figure 1 and Figure 2 An example of the structure of the optical system of the ophthalmic device according to the first embodiment is shown. Figure 1 This schematically illustrates the structure of the optical system of the ophthalmic device of the first embodiment when viewed from above. Figure 2 Show Figure 1 A block diagram illustrating the structure of the optical system 300 for measurement.

[0074] The ophthalmic device 1 of the first embodiment includes a measuring optical system 300, dichroic mirrors ML and MR, an optical axis switching component SW, a fixation projection system 4L, and a fixation projection system 4R. Alternatively, the measuring optical system 300 may include dichroic mirrors ML and MR, an optical axis switching component SW, a fixation projection system 4L, and a fixation projection system 4R.

[0075] (Measurement Optical System 300)

[0076] The measurement optical system 300 includes an objective lens (not shown) and an optical system for measuring the left eye (EL) as the left eye and the right eye (ER) as the right eye of the subject via the objective lens. When performing measurements using the optical system, the measurement optical axes OL and OR, which are separately configured, are adjusted to approximately coincide with the optical axis of the measurement optical system 300 (the optical axis of the OCT optical system 8) via the objective lens. The left eye (EL) is positioned along the measurement optical axis OL. The right eye (ER) is positioned along the measurement optical axis OR.

[0077] like Figure 2As shown, the measurement optical system 300 includes, in addition to the objective lens, a corneal measurement system 3, an anterior eye portion observation system 5, a retroillumination measurement projection system 6, a retroillumination measurement light receiving system 7, and an OCT optical system 8.

[0078] The corneal measurement system 3 is an optical system for measuring information indicating the shape of the cornea CLr of the left eye EL and information indicating the shape of the cornea CRr of the right eye ER. The corneal measurement system 3 is configured to project light for corneal shape measurement to the measurement target eye without passing through the objective lens, and receive return light of the light for corneal shape measurement.

[0079] The anterior eye portion observation system 5 is configured to illuminate either of the anterior eye portions of the left eye EL and the right eye ER, and receive return light of the illumination light via the objective lens.

[0080] The retroillumination measurement projection system 6 projects light for retroillumination measurement to either of the left eye EL and the right eye ER via the objective lens, and projects a measurement pattern (annular pattern) centered on the measurement optical axis OL or the measurement optical axis OR to the fundus ELf or the fundus ERf.

[0081] The retroillumination measurement light receiving system 7 is configured to receive return light from the fundus ELf or the fundus ERf via the objective lens.

[0082] The OCT optical system 8 splits light from an OCT light source into measurement light and reference light, projects the measurement light to either of the left eye EL disposed on the measurement optical axis OL and the right eye ER disposed on the measurement optical axis OR via the objective lens, and detects interference light between the return light of the measurement light from the left eye EL or the right eye ER and the reference light via a reference light path.

[0083] (Dichroic mirrors ML, MR)

[0084] The dichroic mirrors ML, MR respectively transmit light having a wavelength component of the visible region and reflect light having a wavelength component of the near-infrared region (or the infrared region). Here, the fixation light beams projected by the fixation projection systems 4L, 4R have a wavelength component of the visible region, and the light projected by the measurement optical system 300 has a wavelength component of the near-infrared region (or the infrared region).

[0085] The dichroic mirror ML is disposed on the measurement optical axis OL. The dichroic mirror ML transmits the fixation light beam from the fixation projection system 4L to the left eye EL to be examined. In addition, the dichroic mirror ML reflects the light from the measurement optical system 300 to the left eye EL to be examined, and reflects the return light from the left eye EL to be examined to the measurement optical system 300. Similarly, the dichroic mirror MR is disposed on the measurement optical axis OR. The dichroic mirror MR transmits the fixation light beam from the fixation projection system 4R to the right eye ER to be examined. In addition, the dichroic mirror MR reflects the light from the measurement optical system 300 to the right eye ER to be examined, and reflects the return light from the right eye ER to be examined to the measurement optical system 300.

[0086] (Optical axis switching member SW)

[0087] The optical axis switching member SW is disposed between the measurement optical system 300 and the dichroic mirrors ML and MR. The optical axis switching member SW is configured to guide the optical axis of the measurement optical system 300 (i.e., the light from or to the measurement optical system 300) to either of the dichroic mirrors ML and MR.

[0088] In several embodiments, the optical axis switching member SW deflects the optical axis of the measurement optical system 300. For example, the optical axis switching member SW has one or more deflection surfaces capable of changing the deflection direction of the optical axis. In this case, the optical axis switching member SW guides the optical axis of the measurement optical system 300 to the dichroic mirror ML when the orientation of the deflection surface is a first deflection direction, and guides the optical axis of the measurement optical system 300 to the dichroic mirror MR when the orientation of the deflection surface is a second deflection direction. For example, the optical axis switching member SW is configured to have two or more deflection surfaces having different normal directions, and is capable of rotating about a rotation axis extending in the Y-axis direction. In this case, the optical axis switching member SW is capable of switching the deflection direction of the optical axis of the measurement optical system 300 by rotating about the rotation axis. Figure 1 In the embodiment, the optical axis switching member SW has two deflection surfaces formed on two surfaces, and includes a switching mirror capable of rotating about a rotation axis extending in the Y-axis direction. The deflection direction of the optical axis of the measurement optical system 300 can be switched by rotating the optical axis switching member SW about the rotation axis.

[0089] In several embodiments, the optical axis switching member SW is configured to be capable of plugging with respect to the optical axis of the measurement optical system 300. For example, the optical axis switching member SW guides the optical axis of the measurement optical system 300 to one of the dichroic mirrors ML and MR when disposed on the optical axis, and guides the optical axis to the other of the dichroic mirrors ML and MR when retracted from the optical axis.

[0090] In several embodiments, the optical axis switching member SW is configured to have a deflection surface that deflects the optical axis of the measurement optical system 300 and is movable along the optical axis. For example, the optical axis switching member SW deflects the optical axis of the measurement optical system 300 to direct to one of the dichroic mirrors ML, MR when disposed at a first deflection position on the optical axis of the measurement optical system 300, and deflects the optical axis of the measurement optical system 300 to direct to the other of the dichroic mirrors ML, MR when disposed at a second deflection position on the optical axis of the measurement optical system 300.

[0091] In several embodiments, the optical axis switching member SW switches the optical axis of the measurement optical system 300 at high speed so that the measurement optical axis OL and the measurement optical axis OR are alternately substantially coincident. That is, the optical axis switching member SW can also switch the optical axis of the measurement optical system 300 at high speed so that light from the measurement optical system 300 is projected to both eyes at substantially the same time. For example, the optical axis switching member SW projects light from the measurement optical system 300 to at least one of the both eyes, sets a time until the return light is received, and thereby can switch the optical axis of the measurement optical system 300 to the other of the both eyes.

[0092] Hereinafter, for convenience of explanation, the optical axis switching member SW has two deflection surfaces formed on both surfaces, and the optical axis of the measurement optical system 300 is directed to either of the dichroic mirrors ML, MR by changing the orientation of the deflection surface by rotation about a rotation axis.

[0093] (Fixation projection systems 4L, 4R)

[0094] The fixation projection system 4L presents a fixation target to the left eye EL by projecting a fixation light beam to the fundus EIf of the left eye EL. The fixation projection system 4L includes a fixation unit 40L, a relay lens 43L, 44L. The fixation unit 40L includes a liquid crystal panel 41L, a relay lens 42L. The liquid crystal panel 41L displays a pattern representing a fixation target under control from a control section described later. By changing the display position of the pattern on the screen of the liquid crystal panel 41L, the fixation position of the left eye EL can be changed. In addition, the fixation unit 40L is movable in the optical axis direction under control from the control section described later.

[0095] Light from the liquid crystal panel 41L passes through the relay lenses 42L, 43L, 44L, passes through the dichroic mirror ML, and is projected to the fundus EIf. In several embodiments, the fixation unit 40L is independently movable in the optical axis direction with the relay lenses 43L, 44L.

[0096] Likewise, the fixation projection system 4R presents a fixation target to the right eye ER by projecting a fixation light beam to the fundus ERf of the right eye ER. The fixation projection system 4R includes a fixation unit 40R, a relay lens 43R, 44R. The fixation unit 40R includes a liquid crystal panel 41R, a relay lens 42R. The liquid crystal panel 41R displays a pattern representing a fixation target under the control from a control section described later. By changing the display position of the pattern on the screen of the liquid crystal panel 41R, the fixation position of the right eye ER can be changed. In addition, the fixation unit 40R is movable in the optical axis direction under the control from the control section described later.

[0097] The light from the liquid crystal panel 41R passes through the relay lenses 42R, 43R, 44R, the dichroic mirror MR, and is projected to the fundus ERf. In several embodiments, the fixation unit 40R is independently movable in the optical axis direction with the relay lenses 43R, 44R.

[0098] The fixation unit 40L is independently movable in the optical axis direction with the fixation unit 40R. That is, the fixation units 40L, 40R are independently movable in the optical axis direction according to the refractive power of each of the left eye EL and the right eye ER, respectively.

[0099] The fixation position of each of the left eye EL and the right eye ER includes a position for acquiring an image centered on the macula of the fundus, a position for acquiring an image centered on the optic papilla, a position for acquiring an image centered on the center of the fundus between the macula and the optic papilla, and the like. The display position of the pattern representing the fixation target can be arbitrarily changed.

[0100] The ophthalmic apparatus 1 can perform corneal measurement, reflection measurement, and OCT measurement on the left eye EL by the measurement optical system 300 in a state where the fixation target is presented to the left eye EL by the fixation projection system 4L. In addition, the ophthalmic apparatus 1 can perform corneal measurement, reflection measurement, and OCT measurement on the right eye ER by the measurement optical system 300 in a state where the fixation target is presented to the right eye ER by the fixation projection system 4R. In several embodiments, the ophthalmic apparatus 1 sequentially performs at least one of corneal measurement, reflection measurement, and OCT measurement on each of the left eye EL and the right eye ER by the measurement optical system 300 in a state where the fixation target is presented to each of the left eye EL and the right eye ER by the fixation projection systems 4L, 4R.

[0101] Such an ophthalmic apparatus 1 includes an optical axis adjusting section that adjusts an optical axis of the OCT optical system 8 (an axis of an optical path of the measurement light). The optical axis adjusting section controls an optical member in the path of the measurement light under control from a control section described later, deflects the measurement light or moves the optical axis of the OCT optical system 8, whereby the optical axis of the OCT optical system 8 can be adjusted. The control section controls the optical axis adjusting section so that the optical axis of the OCT optical system 8 substantially coincides with either of the measurement optical axes OL, OR.

[0102] Further, the ophthalmic apparatus 1 includes an interpupillary distance adjusting section that changes the distance in the X direction between the measurement optical axes OL, OR in accordance with the interpupillary distance of the subject.

[0103] Figure 3 An explanatory diagram showing an operation example of the interpupillary distance adjusting section in the ophthalmic apparatus 1 of the first embodiment is shown. In Figure 3 the same parts are attached with the same reference numerals, and the explanation is appropriately omitted. Figure 1

[0104] The interpupillary distance adjusting section changes the distance in the X direction between the measurement optical axes OL, OR by moving the optical axis switching member SW along the measurement optical axis OL or the measurement optical axis OR (the Z direction, the optical axis of the measurement optical system 300). For example, when the optical axis switching member SW is in the initial position, the distance in the X direction between the measurement optical axes OL, OR becomes the interpupillary distance PD. Here, while constantly maintaining the deflection surface of the optical axis switching member SW, the optical axis switching member SW is moved from the initial position along the measurement optical axis OL or the measurement optical axis OR. Thereby, as Figure 3 shown in FIG. 6, the positions of the optical axes deflected by the dichroic mirrors ML, MR change, the measurement optical axis OL becomes the measurement optical axis OL', and the measurement optical axis OR becomes the measurement optical axis OR'. As a result, the distance in the X direction between the measurement optical axes OL', OR' becomes the interpupillary distance PD', and the interpupillary distance is changed.

[0105] In several embodiments, the interpupillary distance is changed by moving the optical axis switching member SW in the X direction shown. Figure 3

[0106] In several embodiments, the optical axis adjusting section moves the optical axis switching member SW along the measurement optical axis OL or the measurement optical axis OR so that the optical axis of the OCT optical system 8 substantially coincides with either of the measurement optical axes OL, OR.

[0107] ​​In several embodiments, the optical axis switching member SW is moved by a movement mechanism not shown under control from a control section to be described later. In this case, the function of the interpupillary distance adjustment section is realized by the movement mechanism (and the control section) not shown. In several embodiments, the optical axis switching member SW is moved manually by a movement mechanism not shown. In this case, the function of the interpupillary distance adjustment section is realized by the movement mechanism not shown.

[0108] Further, the ophthalmologic apparatus 1 includes a convergence angle adjustment section that matches the convergence angle of the examined eye, and changes at least one of the orientation of the measurement optical axis OL incident on the left examined eye EL through the pupil and the orientation of the measurement optical axis OR incident on the right examined eye ER through the pupil.

[0109] Figure 4 An explanatory diagram showing an operation example of the convergence angle adjustment section in the ophthalmologic apparatus 1 of the first embodiment is shown. In Figure 4 The same parts as Figure 1 the same reference numerals are attached, and the explanation is omitted as appropriate.

[0110] The convergence angle adjustment section changes the orientation of at least one of the measurement optical axes OL, OR by changing at least one of the orientation of the dichroic mirror ML and the orientation of the dichroic mirror MR. Here, the orientation of the dichroic mirror ML corresponds to the orientation (normal direction) of the optical path coupling surface of the optical path coupling member that couples the optical path (optical axis) of the measurement optical system 300 and the optical path (optical axis) of the fixation projection system 4L. Further, the orientation of the dichroic mirror MR corresponds to the orientation of the optical path coupling surface of the optical path coupling member that couples the optical path of the measurement optical system 300 and the optical path of the fixation projection system 4R.

[0111] For example, the optical path coupling surface (deflection surface) of the dichroic mirror ML is configured to be rotatable about a rotation axis extending in the Y-axis direction. For example, the optical path coupling surface (deflection surface) of the dichroic mirror MR is configured to be rotatable about a rotation axis extending in the Y-axis direction.

[0112] For example, when the orientation of the deflection surface of the dichroic mirror ML is the first direction and the orientation of the deflection surface of the dichroic mirror MR is the second direction, the orientation of each of the measurement optical axes OL, OR is a direction substantially parallel to the optical axis direction of the measurement optical system 300. Here, the orientation of the deflection surface of each of the dichroic mirrors ML, MR is changed to the inside. Thereby, as shown in Figure 4

[0113] ​In several embodiments, the dichroic mirrors ML, MR are rotated by a movement mechanism (a rotation mechanism) not shown under control from a control section not shown. In this case, the function of the convergence angle adjustment section is realized by the movement mechanism (and the control section) not shown. In several embodiments, the dichroic mirrors ML, MR are manually rotated by a movement mechanism (a rotation mechanism) not shown. In this case, the function of the convergence angle adjustment section is realized by the movement mechanism not shown.

[0114] Further, the convergence angle adjustment section can also change the orientation of at least one of the measurement optical axes OL, OR by adjusting the deflection angle of the deflection surface using the optical axis switching member SW. For example, by adjusting the deflection angle of the deflection surface using the optical axis switching member SW, it is possible to change the direction of incidence of the optical axis of the measurement optical system 300 on the deflection surface of the dichroic mirror ML, MR. As a result, the convergence angle is changed.

[0115] In several embodiments, the ophthalmic apparatus 1 includes a height adjustment section that changes the orientation (deflection direction) of the deflection surface of the optical axis switching member SW, the orientation of the deflection surface (optical path coupling surface) of the dichroic mirror ML, and the orientation of the deflection surface of the dichroic mirror MR. Thereby, the arrangement direction of the measurement optical axes OL, OR is adjusted. For example, when the arrangement direction of the left eye under examination EL and the right eye under examination ER is not the horizontal direction (X direction), it is possible to make the arrangement direction of the measurement optical axes OL, OR coincide with the arrangement direction of the left eye under examination EL and the right eye under examination ER by the height adjustment section. A movement mechanism that rotates the deflection surface of the optical axis switching member SW, the deflection surface (optical path coupling surface) of the dichroic mirror ML, and the deflection surface of the dichroic mirror MR is an example of the height adjustment section.

[0116] Further, the ophthalmic apparatus 1 includes an arithmetic processing section that calculates the intraocular parameters of the eyes under examination based on the detection results of the interference light obtained by the OCT optical system 8. Specifically, the arithmetic processing section calculates the intraocular parameters of the left eye under examination EL based on the detection results of the interference light obtained in a state in which the optical axis of the OCT optical system 8 is adjusted to be approximately coincident with the measurement optical axis OL, and calculates the intraocular parameters of the right eye under examination ER based on the detection results of the interference light obtained in a state in which the optical axis of the OCT optical system 8 is adjusted to be approximately coincident with the measurement optical axis OR.

[0117] The fixation projection system 4L is an example of the "first fixation optical system" of the embodiment. The fixation projection system 4R is an example of the "second fixation optical system" of the embodiment. The dichroic mirror ML is an example of the "first optical path coupling member" of the embodiment. The dichroic mirror MR is an example of the "second optical path coupling member" of the embodiment. The optical axis switching member SW (or the optical axis switching member SW and the moving mechanism that rotates the optical axis switching member SW) is an example of the "optical axis switching member" of the embodiment. The moving mechanism that rotates the dichroic mirrors ML, MR is an example of the convergence angle adjustment section. The convergence angle adjustment section is an example of the "first adjustment section" of the embodiment. The moving mechanism that rotates the deflection surface of the optical axis switching member SW, the deflection surface (optical path coupling surface) of the dichroic mirror ML, and the deflection surface of the dichroic mirror MR is an example of the height adjustment section. The height adjustment section is an example of the "second adjustment section" of the embodiment. The interpupillary distance adjustment section is an example of the "third adjustment section" of the embodiment.

[0118] Hereinafter, a configuration example of the measurement optical system 300 will be described. Hereinafter, the left eye EL and the right eye ER under examination will be simply referred to as the eye under examination.

[0119] Figure 5 and Figure 6 A configuration example of the measurement optical system 300 of the first embodiment will be described. Figure 5 is a configuration example of the measurement optical system 300 as viewed from the side (X direction) schematically. Figure 6 is a configuration example of the OCT unit 100 of Figure 5 . Further, in Figure 5 , the front eye portion cameras 15LA, 15RA are arranged in the X direction, and the front eye portion cameras 15LB, 15RB are arranged in the X direction for the sake of explanation, but the configuration of the embodiment is not limited thereto. In addition, for the sake of explanation, in Figure 5 , the illustration of the dichroic mirrors ML, MR shown in Figure 1 is omitted. In Figure 5 , the same reference numerals are attached to the same parts as Figure 1 , and the explanation is appropriately omitted. In Figure 6 , the same reference numerals are attached to the same parts as Figure 5 , and the explanation is appropriately omitted.

[0120] The measurement optical system 300 includes an optical system for observing either of the left eye EL and the right eye ER, an optical system for examining either of the left eye EL and the right eye ER, and a dichroic mirror that wavelength-separates the optical paths of these optical systems. As the optical system for observing either of the left eye EL and the right eye ER, the anterior eye portion observation system 5 is provided. As the optical system for examining either of the left eye EL and the right eye ER, the corneal measurement system 3, the reflection measurement optical system (refractive power measurement optical system), and the OCT optical system 8 are provided. As shown in FIG. 1, the reflection measurement optical system includes the reflection measurement projection system 6 and the reflection measurement light receiving system 7. Figure 2

[0121] In the first embodiment, the corneal measurement system 3, the reflection measurement projection system 6, the reflection measurement light receiving system 7, and the OCT optical system 8 are shared in the examination of the left eye EL and the examination of the right eye ER. In addition, the optical axis of the OCT optical system 8 is coaxially coupled with the optical axis of the reflection measurement optical system (the reflection measurement projection system 6, the reflection measurement light receiving system 7).

[0122] Specifically, the measurement optical system 300 includes the XY alignment system 2, the corneal measurement system 3, the anterior eye portion observation system 5, the reflection measurement projection system 6, the reflection measurement light receiving system 7, the OCT optical system 8, and the anterior eye portion cameras 15LA, 15RA, 15LB, 15RB. Hereinafter, for example, the anterior eye portion observation system 5 uses light of 940 nm to 1000 nm, the reflection measurement optical system (the reflection measurement projection system 6, the reflection measurement light receiving system 7) uses light of 830 nm to 880 nm, and the OCT optical system 8 uses light of 800 nm to 900 nm. In this case, Figure 1 The fixation projection systems 4L, 4R shown are capable of using light of 400 nm to 700 nm. In several embodiments, the OCT optical system 8 uses light of 1000 nm to 1100 nm.

[0123] (anterior eye portion observation system 5)

[0124] The anterior eye portion observation system 5 dynamically photographs the anterior eye portion of the left eye EL or the anterior eye portion of the right eye ER on the measurement optical axis to which the optical axis of the objective lens 51 (the measurement optical system 300) is optically coaxially coupled. In the optical system via the anterior eye portion observation system 5, the photographing surface of the photographing element 59 is disposed at the pupil conjugate position. The anterior eye portion illumination light source 50 irradiates illumination light (for example, infrared light) to the anterior eye portion of the left eye EL or the anterior eye portion of the right eye ER.

[0125] ​In several embodiments, the front eye portion illuminating light source 50 includes a pair of illuminating light sources for illuminating the front eye portion of the left eye under examination EL or the front eye portion of the right eye under examination ER from positions separated from the measurement optical axis OL, OR. In several embodiments, the front eye portion illuminating light source 50 includes a pair of illuminating light sources for illuminating the front eye portion of the left eye under examination EL from positions separated from the measurement optical axis OL and a pair of illuminating light sources for illuminating the front eye portion of the right eye under examination ER from positions separated from the measurement optical axis OR. In this case, one of the pair of illuminating light sources for illuminating the front eye portion of the left eye under examination EL and one of the pair of illuminating light sources for illuminating the front eye portion of the right eye under examination ER can also be shared.

[0126] The light reflected by the front eye portion of the left eye under examination EL and the front eye portion of the right eye under examination ER passes through the objective lens 51, the dichroic mirror 52, the aperture (telecentric aperture) 53, the half mirror 23, the relay lenses 55 and 56, and the dichroic mirror 76. The dichroic mirror 52 combines (separates) the optical paths of the reflection measuring optical system and the optical path of the front eye portion observation system 5. With respect to the dichroic mirror 52, the optical path combining surface that combines these optical paths is disposed obliquely with respect to the optical axis of the objective lens 51. The light that passes through the dichroic mirror 76 is imaged on the imaging surface of the imaging element 59 (area sensor) by the imaging lens 58. The imaging element 59 performs imaging and signal output at a predetermined frame rate. The output (image signal) of the imaging element 59 is input to the processing section 9 described later. The processing section 9 causes the display section 270 described later to display a front eye portion image of the left eye under examination EL or a front eye portion image of the right eye under examination ER based on the image signal. The front eye portion image of the left eye under examination EL and the front eye portion image of the right eye under examination ER are, for example, infrared dynamic images.

[0127] (front eye portion cameras 15LA, 15RA, 15LB, 15RB)

[0128] The front eye portion cameras 15LA and 15LB image the front eye portion of the left eye under examination EL. The front eye portion cameras 15LA and 15LB are, for example, video cameras that perform dynamic imaging at a predetermined frame rate. The front eye portion cameras 15LA and 15LB substantially simultaneously image the front eye portion from different directions. The front eye portion cameras 15LA and 15LB are, for example, used to perform optical system alignment with respect to the position of the left eye under examination EL.

[0129] The number of front eye portion cameras that image the front eye portion of the left eye under examination EL can be any number of two or more, but the configuration can be such that the front eye portion can be substantially simultaneously imaged from two different directions. Also, one front eye portion camera can be the imaging element 59 in the front eye portion observation system 5.

[0130] "Substantially simultaneously" means a case where a deviation in the timing of imaging that can be ignored in terms of the degree of eye movement is allowed in the imaging by two or more anterior eye portion cameras. Thus, it is possible to acquire images of the subject eye in the same position (orientation) by two or more anterior eye portion cameras.

[0131] The anterior eye portion cameras 15RA, 15RB image the anterior eye portion of the right subject eye ER. The anterior eye portion cameras 15RA and 15RB are, for example, video cameras that perform dynamic imaging at a predetermined frame rate. The anterior eye portion cameras 15RA and 15RB substantially simultaneously image the anterior eye portion from different directions. For example, the anterior eye portion cameras 15RA, 15RB are used to perform alignment of the position of the optical system with respect to the right subject eye ER.

[0132] The number of anterior eye portion cameras that image the anterior eye portion of the right subject eye ER can be any number of two or more, but it is sufficient to have a structure that enables substantially simultaneous imaging of the anterior eye portion from two different directions. In addition, one of the anterior eye portion cameras can also be the imaging element 59 in the anterior eye portion observation system 5.

[0133] In several embodiments, instead of the anterior eye portion cameras 15LA, 15LB, a known Z alignment system using a light lever is provided. In several embodiments, instead of the anterior eye portion cameras 15RA, 15RB, a known Z alignment system using a light lever is provided.

[0134] (XY alignment system 2)

[0135] The XY alignment system 2 irradiates light (infrared light) for performing alignment in a direction orthogonal to the optical axis of the anterior eye portion observation system 5 (left-right direction (X direction), up-down direction (Y direction)) onto the left subject eye EL or the right subject eye ER on the measurement optical axis optically coaxial with the optical axis of the objective lens 51 (measurement optical system 300). The XY alignment system 2 includes an XY alignment light source 21 and a collimator lens 22 provided in an optical path branched from the optical path of the anterior eye portion observation system 5 by the half mirror 23. Light output from the XY alignment light source 21 is collimated by the collimator lens 22, reflected by the half mirror 23, and projected onto the left subject eye EL or the right subject eye ER through the anterior eye portion observation system 5. The reflected light of the cornea CLr of the left subject eye EL or the cornea CRr of the right subject eye ER is guided to the imaging element 59 through the anterior eye portion observation system 5.

[0136] The front eye portion image of the left eye under examination EL includes an image (XY bright spot image) based on reflected light from the cornea CLr. The front eye portion image of the right eye under examination ER includes an image (XY bright spot image) based on reflected light from the cornea CRr. The processing portion 9 causes the display portion to display the front eye portion image including the XY bright spot image and the alignment mark for the left eye under examination EL or the right eye under examination ER, for example. In the case where the XY alignment is performed manually, the user performs a moving operation of the optical system so as to guide the XY bright spot image within the alignment mark. In the case where the alignment is performed automatically, the processing portion 9 controls the mechanism that moves the optical system so as to eliminate the displacement of the XY bright spot image with respect to the alignment mark. In several embodiments, the processing portion 9 controls the mechanism that moves the optical system and the mechanism that moves the Figure 1 The optical axis switching member SW, the dichroic mirror ML, and the mechanism that moves MR are shown so as to eliminate the displacement of the XY bright spot image with respect to the alignment mark.

[0137] (Corneal measurement system 3)

[0138] The corneal measurement system 3 projects a ring-shaped light beam (infrared light) for measuring the shape of the cornea CLr of the left eye under examination EL or the shape of the cornea CRr of the right eye under examination ER (corneal shape information) to the cornea CLr or the cornea CRr. The corneal plate 31 is disposed between the objective lens 51 and the left eye under examination EL and the right eye under examination ER. The corneal ring light source 32 is provided on the back surface side (the objective lens 51 side) of the corneal plate 31. A corneal pattern (transmission portion) that transmits light from the corneal ring light source 32 along a circumference centered on the optical axis of the objective lens 51 (measurement optical system 300) is formed on the corneal plate 31. In several embodiments, a corneal pattern (transmission portion) that transmits light from the corneal ring light source 32 along a circumference centered on the optical axis is formed on the corneal plate 31. Further, the corneal pattern can also be formed in a circular arc shape (a part of a circumference) centered on the optical axis. By illuminating the corneal plate 31 with light from the corneal ring light source 32, a ring-shaped light beam (a measurement pattern in a circular arc shape or a circumference shape) is projected to the cornea CLr or the cornea CRr. Reflected light (corneal ring-shaped image) from the cornea CLr or the cornea CRr is detected by the imaging element 59 together with the front eye portion image of the left eye under examination EL or the front eye portion image of the right eye under examination ER. The processing portion 9 performs a publicly known operation based on the corneal ring-shaped image, thereby calculating a corneal shape parameter indicating the shape of the cornea CLr and a corneal shape parameter indicating the shape of the cornea CRr.

[0139] (Reflection measurement projection system 6, reflection measurement light receiving system 7)

[0140] The retinoscopy optical system includes a retinoscopy projection system 6 and a retinoscopy light receiving system 7 used for the refractive power measurement. The retinoscopy projection system 6 projects a refractive power measurement light beam (for example, a ring-shaped light beam) (infrared light) onto the fundus ELf of the left eye under examination EL or the fundus ERf of the right eye under examination ER on the measurement optical axis optically coaxially coupled to the optical axis of the objective lens 51 (measurement optical system 300). The retinoscopy light receiving system 7 receives return light from the refractive power measurement light beam from the left eye under examination EL or the right eye under examination ER.

[0141] The retinoscopy projection system 6 is provided in an optical path branched by an aperture prism 65 provided in the optical path of the retinoscopy light receiving system 7. The aperture portion formed in the aperture prism 65 is disposed at the pupil conjugate position of the left eye under examination EL or the right eye under examination ER on the measurement optical axis optically coaxially coupled to the optical axis of the objective lens 51 (measurement optical system 300). In the optical system of the retinoscopy light receiving system 7, the imaging surface of the imaging element 59 is disposed at the fundus conjugate position.

[0142] In several embodiments, the retinoscopy light source 61 is an SLD (Super Luminescent Diode) light source as a high-brightness light source. The retinoscopy light source 61 is movable in the optical axis direction. The retinoscopy light source 61 is disposed at the fundus conjugate position of the left eye under examination EL or the right eye under examination ER on the measurement optical axis optically coaxially coupled to the optical axis of the objective lens 51 (measurement optical system 300).

[0143] The light output from the retinoscopy light source 61 passes through the relay lens 62, and is incident on the conical surface of the conical prism 63. The light incident on the conical surface is deflected and emitted from the bottom surface of the conical prism 63. The light emitted from the bottom surface of the conical prism 63 passes through the light-transmitting portion of the annular diaphragm 64 formed in a ring shape. The light (ring-shaped light beam) passing through the light-transmitting portion of the annular diaphragm 64 is reflected by the reflecting surface formed around the aperture portion of the aperture prism 65, passes through the rotating prism 66, and is reflected by the dichroic mirror 67. The light reflected by the dichroic mirror 67 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the left eye under examination EL or the right eye under examination ER on the measurement optical axis adjusted to be substantially coincident with the optical axis of the objective lens 51. The rotating prism 66 is used to average the light amount distribution of the ring-shaped light beam with respect to the blood vessels and disease sites of the fundus and to reduce speckle noise caused by the light source.

[0144] The returning light of the annular light beam projected to the fundus ELf of the left eye under examination EL or the fundus ERf of the right eye under examination ER is reflected by the objective lens 51, the dichroic mirror 52, and the dichroic mirror 67. The returning light reflected by the dichroic mirror 67 passes through the rotating prism 66, the aperture portion of the aperture prism 65, the relay lens 71, is reflected by the mirror 72, passes through the relay lens 73 and the focusing lens 74. The focusing lens 74 is movable along the optical axis of the reflection measurement light receiving system 7. The light passing through the focusing lens 74 is reflected by the mirror 75, reflected by the dichroic mirror 76, and imaged on the imaging surface of the imaging element 59 by the imaging lens 58.

[0145] The processing section 9 performs known operations based on the output from the imaging element 59, thereby calculating the refractive power value of the left eye under examination EL or the right eye under examination ER. Specifically, the processing section 9 specifies the annular pattern image from the left eye under examination EL or the right eye under examination ER based on the output from the imaging element 59, performs known operations on the specified annular pattern image, thereby calculating the refractive power value of the left eye under examination EL or the right eye under examination ER. By sequentially switching the optical axis of the reflection measurement optical system to the measurement optical axis OL, OR, the processing section 9 can sequentially calculate the refractive power value of the left eye under examination EL and the refractive power value of the right eye under examination ER. The refractive power value includes, for example, the spherical power, the astigmatism power and the astigmatism axis angle, or the equivalent spherical power.

[0146] In several embodiments, the measurement optical system 300 includes the fixation projection system 4L, 4R.

[0147] (OCT optical system 8)

[0148] The OCT optical system 8 is an optical system for performing OCT measurement. For example, based on the reflection measurement results implemented before the OCT measurement, the position of the focusing lens 87 is adjusted so that the end face of the optical fiber fl is conjugated with the imaging site (the fundus or the anterior eye segment) and the optical system.

[0149] The OCT optical system 8 is provided in an optical path in which the wavelength is separated from the optical path of the reflection measurement optical system by the dichroic mirror 67. The optical axis of the OCT optical system 8 can be adjusted so as to be coaxially coupled with the optical axis of the objective lens 51 (the optical axis of the reflection measurement optical system) and substantially coincide with either of the measurement optical axes OL, OR.

[0150] The OCT optical system 8 includes an OCT unit 100. As Figure 6As shown, the OCT unit 100 is provided with an optical system for OCT measurement (OCT imaging, OCT scanning) of either the left eye under examination EL or the right eye under examination ER. The optical system has the same structure as that of a conventional spectral domain type OCT device. That is, the optical system is configured to split light (low coherent light) from a wideband light source into reference light and measurement light, generate interference light by interference of the measurement light via the eye under examination (OCT measurement site) and the reference light via a reference light path, and detect a spectral component of the interference light. The detection result (detection signal) is sent to the processing unit 9.

[0151] The light source unit 101 outputs low coherent light L0 of a wide frequency band. The low coherent light L0 has, for example, a wavelength component of a wavelength band in the near infrared region (around 800 nm to 900 nm or so), and has a coherence length of several tens of micrometers or so in time. In addition, near infrared light having a wavelength band that is not visible to the human eye, for example, having a central wavelength of 1040 nm to 1060 nm or so, can be used as the low coherent light L0.

[0152] Hereinafter, the light source unit 101 outputs low coherent light L0 having a wavelength component of 840 nm.

[0153] The light source unit 101 is configured to include a light output device such as a super luminescent diode (SLD), an LED, an SOA (Semiconductor Optical Amplifier), and the like.

[0154] The low coherent light L0 output from the light source unit 101 is guided to a fiber coupler 103 through an optical fiber 102, and is split into measurement light LS and reference light LR.

[0155] The reference light LR is guided by an optical fiber 104 to an optical attenuator 105. The optical attenuator 105 automatically adjusts the amount of light of the reference light LR guided by the optical fiber 104 under the control of the processing unit 9 using a known technique. The reference light LR whose amount of light is adjusted by the optical attenuator 105 is guided by the optical fiber 104 to a polarization controller 106. The polarization controller 106 is, for example, a device that adjusts the polarization state of the reference light LR guided in the optical fiber 104 by applying stress to the optical fiber 104 formed in a ring shape from the outside. Furthermore, the structure of the polarization controller 106 is not limited thereto, and any known technique can be used. The reference light LR whose polarization state is adjusted by the polarization controller 106 reaches a fiber coupler 109.

[0156] The measurement light LS generated by the fiber coupler 103 is guided to a collimator lens 90( Figure 6), and becomes a parallel light flux by the collimator lens 90. Further, the measurement light LS reaches the dichroic mirror 67 via the optical path length changing section 89, the light scanner 88, the focusing lens 87, the relay lenses 85, 82, and the mirror 81.

[0157] In several embodiments, the focusing lens 87 and the light scanner 88 are housed in one unit that is movable in the optical axis direction. Thereby, it is possible to move in the optical axis direction while maintaining the optical positional relationship of the focusing lens 87 and the light scanner 88. This is configured so that the focusing lens 87 and the light scanner 88 are moved integrally, whereby it is possible to adjust the optical system while maintaining the conjugate relationship of the light scanner 88 and the eye under examination. Further, in the case of this configuration, it is possible to easily change the pupil of the eye under examination and the magnification relationship of the light scanner 88 by changing the focal distance f of the focusing lens 87.

[0158] In several embodiments, the focusing lens 87 and the light scanner 88 are independently moved in the optical axis direction within the unit. In several embodiments, the focusing lens 87 and the light scanner 88 are independently or integrally moved in the optical axis direction under the control from the processing section 9. For example, the focal position of the objective lens 51 is configured with the pupil of the eye under examination, and the focal position of the focusing lens 87 is configured with the deflection surface of the light scanner 88 (in the case of configuring the light scanner 88 at the focal position of the focusing lens 87, the pupil conjugate relationship is maintained, and the deflection surface of the light scanner 88 is configured at the pupil conjugate position).

[0159] The optical path length changing section 89 changes the optical path length of the measurement light LS. It is possible to change the difference between the optical path length of the reference light LR and the optical path length of the measurement light LS by changing the optical path length of the measurement light LS. For example, the optical path length changing section 89 includes a retroreflector that is movable along the optical path of the measurement light LS and the optical path of the return light of the measurement light LS, and the optical path length of the measurement light LS is changed by moving the retroreflector.

[0160] The light scanner 88 deflects the measurement light LS one-dimensionally or two-dimensionally.

[0161] In several embodiments, the light scanner 88 includes a first galvanometer mirror and a second galvanometer mirror. The first galvanometer mirror deflects the measurement light LS so that the OCT measurement site is scanned in the horizontal direction (X direction) orthogonal to the optical axis of the OCT optical system 8. The second galvanometer mirror deflects the measurement light LS deflected by the first galvanometer mirror so that the OCT measurement site is scanned in the vertical direction (Y direction) orthogonal to the optical axis of the OCT optical system 8. The scanning method of the measurement light LS of such a light scanner 88 includes, for example, horizontal scanning, vertical scanning, cross scanning, radial scanning, circular scanning, concentric circular scanning, spiral scanning, Lissajous scanning, and the like.

[0162] In several embodiments, the light scanner 88 includes a MEMS scanner (MEMS mirror scanner) that two-dimensionally deflects the measurement light LS. The MEMS scanner deflects the measurement light LS so that the OCT measurement site is scanned in the horizontal direction and the vertical direction orthogonal to the optical axis of the OCT optical system 8.

[0163] Further, the light scanner 88 is configured to include, in addition to the galvanometer mirror and the MEMS scanner, a polygon mirror, a rotating mirror, a Duffieux prism, a double Duffieux prism, a rotating prism, or the like.

[0164] The measurement light LS that has reached the dichroic mirror 67 is transmitted through the dichroic mirror 67, reflected by the dichroic mirror 52, and refracted by the objective lens 51. The measurement light LS that has been refracted by the objective lens 51 is deflected by the optical axis switching member SW toward the dichroic mirror ML or the dichroic mirror MR. The measurement light LS that has been deflected by the dichroic mirror ML or the dichroic mirror MR is irradiated to the OCT measurement site of the left eye EL or the right eye ER. The measurement light LS at the OCT measurement site is scattered (including reflection) at various depth positions. The backscattered light of the measurement light LS at the OCT measurement site is retro-advanced on the same path as the forward path, guided to the fiber coupler 103, and reaches the fiber coupler 109 via the optical fiber 108.

[0165] The fiber coupler 109 causes the backscattered light of the measurement light LS to interfere with the reference light LR via the optical attenuator 105 or the like. The interference light LC generated thereby is guided by the optical fiber 110 and emitted from the emission end 111. Further, the interference light LC becomes a parallel light flux by the collimator lens 112, is spectrally resolved by the diffraction grating (light splitter) 113, is condensed by the variable magnification optical system 114, and is projected onto the light-receiving surface of the CCD image sensor 115. Further, Figure 8 The diffraction grating 113 shown is a transmission type, but another type of light splitting element such as a reflection type diffraction grating or the like can be used.

[0166] The CCD image sensor 115 is, for example, a line sensor in which two or more light-receiving elements (detection elements) are arranged, and detects each spectral component of the spectrally resolved interference light LC to convert it into an electric charge. The CCD image sensor 115 accumulates the electric charge to generate a detection signal, which is sent to the processing section 9.

[0167] In the present embodiment, a Michelson type interferometer is employed, but any type of interferometer such as a Mach-Zehnder type or the like can be appropriately employed. In addition, instead of the CCD image sensor, another type of image sensor such as a CMOS (Complementary Metal Oxide Semiconductor) image sensor or the like can be used.

[0168] In addition, in the present embodiment, the light scanner 88 is configured to include the galvanometer mirror and the MEMS scanner, but the light scanner 88 can be configured to include a polygon mirror, a rotating mirror, a Duffieux prism, a double Duffieux prism, a rotating prism, or the like. Figure 5In the illustrated configuration, the configuration is such that the difference between the optical path length of the measurement light LS and the optical path length of the reference light LR is changed by changing the optical path length of the measurement light LS by the optical path length changing section 89, but the configuration of the embodiment is not limited thereto. For example, the configuration can be such that the difference between the optical path length of the measurement light LS and the optical path length of the reference light LR is changed by changing the optical path length of the reference light LR by a known method.

[0169] The processing section 9 can calculate the refractive power value of the left eye EL under examination from the measurement result obtained using the retroreflected measurement optical system, and based on the calculated refractive power value, move the retroreflected measurement light source 61 in the optical axis direction to a position at which the fundus ELf is conjugated with the retroreflected measurement light source 61 and the imaging element 59. In addition, the processing section 9 can calculate the refractive power value of the right eye ER under examination from the measurement result obtained using the retroreflected measurement optical system, and based on the calculated refractive power value, move the retroreflected measurement light source 61 in the optical axis direction to a position at which the fundus ERf is conjugated with the retroreflected measurement light source 61 and the imaging element 59. In some embodiments, the processing section 9 moves the focusing lens 74 to a position corresponding to a composite refractive value (e.g., intermediate power) calculated from the refractive value of the left eye EL under examination and the refractive value of the right eye ER under examination.

[0170] In some embodiments, the processing section 9 moves the focusing lens 87 and the light scanner 88 in the optical axis direction thereof in conjunction with the movement of the focusing lens 74. In some embodiments, the processing section 9 moves the liquid crystal panel 41L (fixation unit 40L) in the optical axis direction thereof in conjunction with the movement of the retroreflected measurement light source 61 and the focusing lens 74. In some embodiments, the processing section 9 moves the liquid crystal panel 41R (fixation unit 40R) in the optical axis direction thereof in conjunction with the movement of the retroreflected measurement light source 61 and the focusing lens 74.

[0171] In the described embodiment, at least one function of the focusing lenses 74, 87 can also be implemented by a liquid crystal lens or a liquid lens.

[0172] The configuration of the optical system of the ophthalmic apparatus 1 of the embodiment is not limited to Figure 1-6 the illustrated configuration.

[0173] <Configuration Example of Anterior Eye Camera>

[0174] Figure 7 A configuration example of the anterior eye cameras 15LA, 15RA, 15LB, 15RB Figure 1 is schematically illustrated.

[0175] As Figure 7As shown, for example, the front eye camera 15LA is configured to capture images of the left eye EL at a positive angle relative to the Y direction formed by the measurement optical axis OL, and the front eye camera 15LB is configured to capture images of the left eye EL at a negative angle relative to the Y direction formed by the measurement optical axis OL. Alternatively, the front eye camera 15LA may be configured to capture images of the left eye EL at a positive angle relative to the X direction formed by the measurement optical axis OL, and the front eye camera 15LB may be configured to capture images of the left eye EL at a negative angle relative to the X direction formed by the measurement optical axis OL.

[0176] Similarly, for example, the front eye camera 15RA can be configured to capture images of the right eye ER from a direction at a positive angle relative to the measurement optical axis OR forming the Y direction, and the front eye camera 15RB can be configured to capture images of the right eye ER from a direction at a negative angle relative to the measurement optical axis OR forming the Y direction. Alternatively, the front eye camera 15RA can be configured to capture images of the right eye ER from a direction at a positive angle relative to the measurement optical axis OR forming the X direction, and the front eye camera 15RB can be configured to capture images of the right eye ER from a direction at a negative angle relative to the measurement optical axis OR forming the X direction.

[0177] It is also possible to achieve some of the functions of the 15LA, 15RA, 15LB, and 15RB front-eye cameras through a single front-eye camera.

[0178] Figure 8 Schematic illustration of the effect achieved via the front-eye camera 15LR Figure 1 Example configuration of the front-eye camera 15LB, 15RB with functionality.

[0179] Anterior eye images were taken using a 15LR camera, capturing the anterior eye region of the left eye (EL) and the right eye (ER). (Example:) Figure 8 As shown, for example, the front eye camera 15LA is configured to capture images of the left eye EL at a positive angle relative to the Y direction formed by the measurement optical axis OL, and the front eye camera 15LR is configured to capture images of the left eye EL at a negative angle relative to the Y direction formed by the measurement optical axis OL. Alternatively, the front eye camera 15LA may be configured to capture images of the left eye EL at a positive angle relative to the X direction formed by the measurement optical axis OL, and the front eye camera 15LR may be configured to capture images of the left eye EL at a negative angle relative to the X direction formed by the measurement optical axis OL.

[0180] Similarly, for example, the front eye camera 15RA can be configured to capture images of the right eye ER from a direction at a positive angle relative to the measurement optical axis OR forming the Y direction, and the front eye camera 15LR can be configured to capture images of the right eye ER from a direction at a negative angle relative to the measurement optical axis OR forming the Y direction. Alternatively, the front eye camera 15LR can be configured to capture images of the right eye ER from a direction at a positive angle relative to the measurement optical axis OR forming the X direction, and the front eye camera 15RA can be configured to capture images of the right eye ER from a direction at a negative angle relative to the measurement optical axis OR forming the X direction.

[0181] The ophthalmic device 1 according to the embodiment shares at least one objective lens between the reflection measurement optical system and the OCT optical system 8, and can perform reflection measurement (refractive power measurement) using the reflection measurement optical system and OCT measurement using the OCT optical system 8. Reflection measurement and OCT measurement can be sequentially performed on either the left eye to be examined or the right eye to be examined. In several embodiments, before performing OCT measurement on one of the left eye to be examined EL and the right eye to be examined ER, the OCT optical system 8 is controlled based on the axial length and refractive power of the other of the left eye to be examined EL and the right eye to be examined ER, thereby adjusting the optical path length of the reference optical path. Thus, before performing OCT measurement on one eye to be examined, a measurement environment estimated based on the measurement environment of the other eye to be examined can be set, and the time required for OCT measurement can be shortened.

[0182] The ophthalmic device 1 according to the first embodiment can adjust the optical axis (axis of the optical path of the measurement light) of the OCT optical system 8.

[0183] <Example of adjustment of the optical axis of the OCT optical system 8>

[0184] Figure 9A The explanatory diagram showing the first adjustment example of the optical axis of the OCT optical system 8 according to the first embodiment. In Figure 9A , the same reference numerals are added to the same parts as Figure 1 and the description is appropriately omitted.

[0185] The measurement optical system 300 includes deflection members DF1 and DF2. The deflection member DF1 deflects the optical axis of the OCT optical system 8 toward the deflection member DF2, and the deflection member DF2 deflects the light deflected by the deflection member DF1 toward the optical axis switching member SW. For example, by moving the deflection member DF1 in the optical axis direction, the optical axis of the OCT optical system 8 can be adjusted so that one of the measurement optical axes OL and OR substantially coincides with the other. For example, at the position of the deflection member DF1', the optical axis of the OCT optical system 8 can be made to substantially coincide with the measurement optical axis OL, and at the position of the deflection member DF1, the optical axis of the OCT optical system 8 can be made to substantially coincide with the measurement optical axis OR.

[0186] For example, the ophthalmic device 1 moves the deflection member DF1 according to the interpupillary distance of the subject, whereby the optical axis of the OCT optical system 8 can be made to substantially coincide with either of the measurement optical axes OL and OR.

[0187] In Figure 5 , as an example of the deflection member DF1, a mirror 81 is included. As an example of the deflection member DF2, a dichroic mirror 52 is included.

[0188] Figure 9BAn explanatory diagram showing a second adjustment example of the optical axis of the OCT optical system 8 according to the first embodiment. Figure 9B In the middle, to and Figure 1 Identical parts are labeled with the same reference numerals, and descriptions are omitted where appropriate.

[0189] The measuring optical system 300 (ophthalmic device 1) includes a moving mechanism that moves the OCT optical system 8 under the control of a control unit described later. For example, this moving mechanism moves the OCT optical system 8 (specifically, the OCT unit 100) independently of the optical elements along the path from the objective lens 51 to the collimating lens 90. For example, by moving the OCT unit 100 in a direction intersecting the optical axis of the OCT optical system 8, the optical axis of the OCT optical system 8 can be adjusted so that one of the measuring optical axes OL and OR approximately coincides with the other. For example, at position 8' of the OCT optical system 8, the optical axis of the OCT optical system 8 can approximately coincide with the measuring optical axis OL, and at position 8' of the OCT optical system 8, the optical axis of the OCT optical system 8 can approximately coincide with the measuring optical axis OR.

[0190] For example, the ophthalmic device 1 can move the position of the optical axis of the OCT optical system 8 (OCT unit 100) according to the interpupillary distance of the subject, thereby making the optical axis of the OCT optical system 8 approximately coincide with either of the measurement optical axes OL or OR.

[0191] Furthermore, as a third example of adjusting the optical axis of the OCT optical system 8 in the first embodiment, the deflection direction of the optical axis of the OCT optical system 8 can be changed by measuring optical components in the light path. Examples of optical components include... Figure 5 The mirrors include reflector 81, dichroic mirror 52, and other mirrors not shown. For example, the deflection direction of the OCT optical system 8, which is deflected by optical components, is changed according to the interpupillary distance of the subject, thereby adjusting the optical axis of the OCT optical system 8.

[0192] <Structure of the Processing System>

[0193] Explain the structure of the processing system of ophthalmic device 1.

[0194] Figure 10 and Figure 11 An example of the functional structure of the processing system of ophthalmic device 1 is shown. Figure 10 An example of a functional block diagram of the processing system of ophthalmic device 1 is shown. Figure 11 Show Figure 10 An example of a functional block diagram of the OCT optical system 8. Figure 10 and Figure 11 In the middle, to and Figure 1 or Figure 5 Identical parts are labeled with the same reference numerals, and descriptions are omitted where appropriate.

[0195] The processing portion 9 controls each portion of the ophthalmic apparatus 1. In addition, the processing portion 9 can perform various kinds of arithmetic processing. The function of the processing portion 9 is realized by a processing circuit. The processing portion 9 includes one or more processors. The function of the processor is realized by, for example, a circuit of a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, a SPLD (Simple Programmable Logic Device), a CPLD (Complex Programmable Logic Device), an FPGA (Field Programmable Gate Array)), or the like. The processing portion 9 realizes the function of the embodiments, for example, by reading out and executing a program stored in a storage circuit, a storage device.

[0196] In several embodiments, the processing portion 9 includes a single processor that realizes the function of the embodiments. In several embodiments, the processing portion 9 includes a plurality of processors that respectively realize one or more functions of the embodiments.

[0197] The processing portion 9 includes a control portion 210 and an arithmetic processing portion 220. In addition, the ophthalmic apparatus 1 includes a moving mechanism 200, 310, 320, a display portion 270, an operation portion 280, and a communication portion 290.

[0198] The moving mechanism 200 is a mechanism for moving a head portion in which an optical system such as the anterior eye portion cameras 15LA, 15LB, 15RA, 15RB, the XY alignment system 2, the corneal measurement system 3, the anterior eye portion observation system 5, the reflection measurement projection system 6, the reflection measurement light receiving system 7, and the OCT optical system 8 are accommodated, in the X direction, the Y direction, and the Z direction. For example, an execution mechanism that generates a driving force for moving the head portion and a transmission mechanism that transmits the driving force are provided in the moving mechanism 200. The execution mechanism is constituted by, for example, a pulse motor. The transmission mechanism is constituted by, for example, a gear combination, a gear and rack, or the like. The control portion 210 (main control portion 211) controls the moving mechanism 200 by transmitting a control signal to the execution mechanism.

[0199] As described above, the ophthalmic apparatus 1 according to the present embodiment includes the moving mechanism 200, the control portion 210, the display portion 270, the operation portion 280, and the communication portion 290. Figure 3As shown, the moving mechanism 310 moves the optical axis switching member SW. For example, the moving mechanism 310 has the same structure as the moving mechanism 200. The control section 210 (the main control section 211) controls the moving mechanism 310 by transmitting a control signal to the actuator.

[0200] As shown, the moving mechanism 320 independently rotates the dichroic mirrors ML, MR around the rotation axes, respectively. For example, the moving mechanism 320 is provided with an actuator that generates a driving force for rotating the dichroic mirrors ML, MR, respectively, and a transmission mechanism that transmits the driving force. The control section 210 (the main control section 211) controls the moving mechanism 320 by transmitting a control signal to the actuator. Figure 4

[0201] Further, an illustration is omitted, and the ophthalmic apparatus 1 can include a mechanism for adjusting the optical axis of the OCT optical system 8. For example, the mechanism has the same structure as the moving mechanism 200 or the moving mechanism 320. The control section 210 (the main control section 211) controls the mechanism by transmitting a control signal to the actuator. Figure 9A Figure 9B The control section 210 includes a processor, and controls each section of the ophthalmic apparatus 1. The control section 210 includes a main control section 211 and a storage section 212. A computer program for controlling the ophthalmic apparatus 1 is stored in the storage section 212 in advance. The computer program includes a front eye portion camera control program, an XY alignment system control program, a corneal measurement system control program, a fixation projection system control program, a front eye portion observation control program, a reflection measurement control program, an OCT measurement control program, an arithmetic processing program, a user interface program, a communication control program, and the like. The main control section 211 is operated in accordance with such a computer program, and thus the control section 210 performs a control process.

[0202] The main control section 211 performs various controls of the ophthalmic apparatus as a measurement control section. The controls of the front eye portion cameras 15LA, 15LB, 15RA, 15RB include exposure adjustment, gain adjustment, frame rate adjustment, shooting timing adjustment, shooting range adjustment, shooting magnification adjustment, synchronization control of the front eye portion cameras 15LA, 15LB, synchronization control of the front eye portion cameras 15RA, 15RB, and synchronization control of the front eye portion cameras 15LA, 15LB, 15RA, 15RB.

[0203] The control section 210 includes a processor, and controls each section of the ophthalmic apparatus 1. The control section 210 includes a main control section 211 and a storage section 212. A computer program for controlling the ophthalmic apparatus 1 is stored in the storage section 212 in advance. The computer program includes a front eye portion camera control program, an XY alignment system control program, a corneal measurement system control program, a fixation projection system control program, a front eye portion observation control program, a reflection measurement control program, an OCT measurement control program, an arithmetic processing program, a user interface program, a communication control program, and the like. The main control section 211 is operated in accordance with such a computer program, and thus the control section 210 performs a control process.

[0204] The main control section 211 performs various controls of the ophthalmic apparatus as a measurement control section. The controls of the front eye portion cameras 15LA, 15LB, 15RA, 15RB include exposure adjustment, gain adjustment, frame rate adjustment, shooting timing adjustment, shooting range adjustment, shooting magnification adjustment, synchronization control of the front eye portion cameras 15LA, 15LB, synchronization control of the front eye portion cameras 15RA, 15RB, and synchronization control of the front eye portion cameras 15LA, 15LB, 15RA, 15RB.

[0205] ​​The front eye cameras 15LA, 15LB substantially simultaneously capture the front eye portion of the left eye EL from different directions. The main control portion 211 specifies the three-dimensional position of the left eye EL from the two captured images acquired by the front eye cameras 15LA, 15LB by controlling the data processing portion 223 described later. The data processing portion 223 analyzes the two captured images substantially simultaneously obtained by the front eye cameras 15LA and 15LB respectively and applies a known triangulation method, thereby specifying a characteristic position corresponding to a characteristic portion of the front eye portion of the left eye EL, in a manner disclosed in, for example, Japanese Patent Application Publication No. 2013-248376. The characteristic portion of the front eye portion is, for example, the center of the pupil. Also, the data processing portion 223 specifies the three-dimensional position of the left eye EL based on the specified characteristic position. In this example, the position of the center of the pupil approximates the position of the eye. Furthermore, the position of the eye can be found as the position of the corneal vertex by using the distance between the corneal vertex and the pupil in the eye under examination or the distance between the corneal vertex and the pupil in a standard eye (model eye, average, etc.).

[0206] The front eye cameras 15RA, 15RB substantially simultaneously capture the front eye portion of the right eye ER from different directions. The main control portion 211 specifies the three-dimensional position of the right eye ER from the two captured images acquired by the front eye cameras 15RA, 15RB by controlling the data processing portion 223 described later. The data processing portion 223 analyzes the two captured images substantially simultaneously obtained by the front eye cameras 15RA and 15RB respectively and applies a known triangulation method, thereby specifying a characteristic position corresponding to a characteristic portion of the front eye portion of the right eye ER. Also, the data processing portion 223 specifies the three-dimensional position of the right eye ER based on the specified characteristic position.

[0207] The main control portion 211 controls the moving mechanism 200 based on the three-dimensional position of the left eye EL and the three-dimensional position of the right eye ER specified by the data processing portion 223, thereby performing the alignment of the positions of the optical systems with respect to the left eye EL and the right eye ER. In addition, the main control portion 211 can control the moving mechanisms 310, 320 based on the specified three-dimensional position of the left eye EL and the three-dimensional position of the right eye ER, thereby performing the adjustment of the interpupillary distance and the adjustment of the convergence angle. Also, the main control portion 211 can perform the optical axis adjustment of making the optical axis of the OCT optical system 8 (i.e., the optical axis of the measurement optical system 300 or the optical axis of the objective lens 51) substantially coincide with either of the measurement optical axes OL, OR based on the specified three-dimensional position of the left eye EL and the three-dimensional position of the right eye ER.

[0208] The control of the XY alignment system 2 includes the control of the XY alignment light source 21 and the like. The control of the XY alignment light source 21 includes the lighting, the extinguishing, the light amount adjustment, the aperture adjustment, and the like of the light source. Thereby, the lighting and the non-lighting of the XY alignment light source 21 or the change of the light amount is switched. The main control section 211 receives the signal detected by the photographing element 59, controls the data processing section 223, and thereby specifies the position of the bright spot image of the return light based on the light from the XY alignment light source 21 based on the received signal. The main control section 211 controls the moving mechanism 200 to move the head in the right and left and up and down directions (XY alignment) so that the displacement of the position of the bright spot image from the predetermined target position is eliminated.

[0209] The control of the corneal measurement system 3 includes the control of the corneal ring light source 32 and the like. The control of the corneal ring light source 32 includes the lighting, the extinguishing, the light amount adjustment, the aperture adjustment, and the like of the light source. Thereby, the lighting and the non-lighting of the corneal ring light source 32 or the change of the light amount is switched. The main control section 211 causes the arithmetic processing section 220 (the data processing section 223) to perform the known arithmetic operation on the corneal ring image detected by the photographing element 59. Thereby, the corneal shape parameter of the examined eye is calculated.

[0210] The control of the fixation projection system 4L, 4R includes the control of the liquid crystal panel 41L, 41R, the moving control of the fixation unit 40L, 40R, and the like. The control of the liquid crystal panel 41L, 41R includes the on / off of the fixation target display, the switching of the fixation target according to the kind of the examination and measurement, the switching of the fixation target display position, and the like.

[0211] In addition, for example, the fixation projection system 4L, 4R is provided with a moving mechanism that moves the liquid crystal panel 41L, 41R (or the fixation unit 40L, 40R) in the optical axis direction, respectively. The moving mechanism is provided with an execution mechanism that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force, like the moving mechanism 200. The main control section 211 controls the moving mechanism to move at least the liquid crystal panel 41L, 41R in the optical axis direction by transmitting the control signal to the execution mechanism. Thereby, the positions of the liquid crystal panel 41L, 41R are adjusted so that the liquid crystal panel 41L and the fundus ELf and the liquid crystal panel 41R and the fundus ERf are optically conjugated, respectively.

[0212] The control of the front eye portion observation system 5 includes control of the front eye portion illumination light source 50, control of a lens moving mechanism that moves the relay lens 56, control of the imaging element 59, and the like. The control of the front eye portion illumination light source 50 includes lighting, extinguishing, light amount adjustment, aperture adjustment, and the like of the light source. Thereby, lighting and non-lighting of the front eye portion illumination light source 50 or the light amount is changed. The lens moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force, similarly to the moving mechanism 200. The main control section 211 controls the lens moving mechanism by transmitting a control signal to the actuator, and moves the relay lens 56 in the optical axis direction. The control of the imaging element 59 includes exposure adjustment, gain adjustment, detection rate adjustment, and the like of the imaging element 59. The main control section 211 receives a signal detected by the imaging element 59, and causes the arithmetic processing section 220 to perform processing such as formation of an image based on the received signal.

[0213] The control of the retroillumination measurement projection system 6 includes control of the retroillumination light source 61, control of the rotating prism 66, and the like. The control of the retroillumination light source 61 includes lighting, extinguishing, light amount adjustment, and the like of the light source. Thereby, lighting and non-lighting of the retroillumination light source 61 or the light amount is changed. For example, the retroillumination measurement projection system 6 includes a moving mechanism that moves the retroillumination light source 61 in the optical axis direction. The moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force, similarly to the moving mechanism 200. The main control section 211 controls the moving mechanism by transmitting a control signal to the actuator, and moves the retroillumination light source 61 in the optical axis direction. The control of the rotating prism 66 includes rotation control of the rotating prism 66 and the like. For example, a rotating mechanism that rotates the rotating prism 66 is provided, and the main control section 211 rotates the rotating prism 66 by controlling the rotating mechanism.

[0214] The control of the retroillumination measurement light receiving system 7 includes control of the focusing lens 74 and the like. The control of the focusing lens 74 includes movement control of the focusing lens 74 in the optical axis direction and the like. For example, the retroillumination measurement light receiving system 7 includes a moving mechanism that moves the focusing lens 74 in the optical axis direction. The moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force, similarly to the moving mechanism 200. The main control section 211 controls the moving mechanism by transmitting a control signal to the actuator, and moves the focusing lens 74 in the optical axis direction. The main control section 211 can move the retroillumination light source 61 and the focusing lens 74 in the optical axis direction, respectively, so that the retroillumination light source 61 and the fundus ELf or the fundus ERf are optically conjugated with the imaging element 59, for example, in accordance with the refractive power of the left eye to be examined EL, the refractive power of the right eye to be examined ER, or the combined refractive power of the refractive power of the left eye to be examined EL and the refractive power of the right eye to be examined ER.

[0215] The control of the OCT optical system 8 includes the control of the light source unit 101, the control of the light attenuator 105, the control of the polarization wave controller 106, the control of the variable focus optical system 114, the control of the CCD image sensor 115, the control of the focusing lens 87, the control of the light scanner 88, the control of the optical path length changing section 89, and the like.

[0216] The control of the light source unit 101 includes the lighting, the extinguishing, the light amount adjustment, the aperture adjustment, and the like of the light source. The control of the light attenuator 105 includes the adjustment of the light amount of the reference light LR, and the like. The control of the polarization wave controller 106 includes the adjustment of the polarization wave state of the reference light LR, and the like. The control of the variable focus optical system 114 includes the control of the optical magnification, and the like. The control of the CCD image sensor 115 includes the exposure adjustment, the gain adjustment, the detection rate adjustment, and the like of the CCD image sensor 115. The main control section 211 receives the signal detected by the CCD image sensor 115, and causes the arithmetic processing section 220 to perform the processing of the formation of the image, and the like, based on the received signal.

[0217] The control of the focusing lens 87 includes the movement control of the focusing lens 87 in the optical axis direction, and the like. For example, the OCT optical system 8 includes a movement mechanism that moves the focusing lens 87 in the optical axis direction. The movement mechanism is provided with an execution mechanism that generates a driving force for moving the movement mechanism, and a transmission mechanism that transmits the driving force, similarly to the movement mechanism 200. The main control section 211 controls the movement mechanism by transmitting the control signal to the execution mechanism, and moves the focusing lens 87 in the optical axis direction.

[0218] In several embodiments, the ophthalmic apparatus 1 is provided with a holding member that holds the focusing lenses 74 and 87, and a drive section that drives the holding member. The main control section 211 performs the movement control of the focusing lenses 74 and 87 by controlling the drive section. The main control section 211 can also move only the focusing lens 87 based on the intensity of the interference signal, for example, after moving the focusing lens 87 in conjunction with the movement of the focusing lens 74.

[0219] The control of the light scanner 88 includes the setting of the scanning pattern that scans the measurement site by the predetermined scanning pattern, the control of the scanning range, the control of the scanning speed, and the like. It is possible to control the angle range of the deflection surface that deflects the measurement light LS by controlling the scanning range (the scanning start position and the scanning end position). It is possible to control the changing speed of the angle of the deflection surface by controlling the scanning speed. The main control section 211 controls at least one of the scanning pattern, the scanning range, and the scanning speed by outputting the control signal to the light scanner 88.

[0220] The control of the optical path length changing section 89 includes control of measurement of the optical path length of the light LS, and the like. The main control section 211 causes the optical path length changing section 89 to change the optical path length of the light LS by outputting a control signal to the optical path length changing section 89.

[0221] In addition, the main control section 211 performs processing of writing data to the storage section 212 and processing of reading data from the storage section 212.

[0222] (Storage section 212)

[0223] The storage section 212 stores various data. The data stored in the storage section 212 includes, for example, a result of subjective measurement (OCT measurement result), image data of an OCT image, image data of an anterior eye image, a result of a subjective test, and information of an eye under examination. The information of the eye under examination includes information about an examinee such as a patient ID, name, and the like, and information about an eye under examination such as identification information of a left eye / right eye. In addition, various programs and data for operating the ophthalmic apparatus are stored in the storage section 212.

[0224] (Computational processing section 220)

[0225] The computational processing section 220 includes a processor and performs various computational processing. A computer program for performing the various computational processing is stored in advance in a storage section (for example, the storage section 212) not shown. The processor operates according to the computer program, whereby the functions of the respective sections for performing the various computational processing are realized.

[0226] As shown in FIG. 2, the computational processing section 220 includes an ocular refraction power calculating section 221, an image forming section 222, and a data processing section 223. Figure 10

[0227] The ocular refraction power calculating section 221 calculates a refraction power value of each of the left eye under examination EL and the right eye under examination ER based on a result of reflection measurement performed sequentially on both eyes. The image forming section 222 forms an OCT image based on a detection result of the interference light LC acquired using the OCT optical system 8. The data processing section 223 performs various data processing (image processing), analysis processing on a result of measurement obtained using the optical system provided in the ophthalmic apparatus 1 (a detection result of the interference light LC, and the like), and an OCT image formed by the image forming section 222.

[0228] (Ocular refraction power calculating section 221)

[0229] ​The ocular refractive power calculating section 221 analyzes the annular images (pattern images) obtained by the return light of the annular light beams (annular measurement patterns) projected to the fundus ELf of the left eye to be examined EL by the reflection measurement projection system 6 received by the imaging element 59, and calculates the refractive power value of the left eye to be examined EL. Also, the ocular refractive power calculating section 221 analyzes the annular images (pattern images) obtained by the return light of the annular light beams projected to the fundus ERf of the right eye to be examined ER by the reflection measurement projection system 6 received by the imaging element 59, and calculates the refractive power value of the right eye to be examined ER. For example, with respect to each annular image, the ocular refractive power calculating section 221 obtains the center of gravity position of the annular image based on the brightness distribution in the image depicting the annular image, obtains the brightness distribution along a plurality of scanning directions extending radially from the center of gravity position, and specifies the annular image from the brightness distribution. Next, the ocular refractive power calculating section 221 obtains an approximate ellipse of the specified annular image, and obtains the spherical power, the astigmatism power, and the astigmatism axis angle by substituting the major axis and the minor axis of the approximate ellipse into a known formula. Alternatively, the ocular refractive power calculating section 221 can obtain the parameters of the ocular refractive power based on the deformation and displacement of the annular image with respect to a reference pattern.

[0230] Also, the ocular refractive power calculating section 221 calculates the corneal refractive power, the corneal astigmatism power, and the corneal astigmatism axis angle of the left eye to be examined EL based on the corneal annular images of the left eye to be examined EL acquired by the anterior eye portion observation system 5. Similarly, the ocular refractive power calculating section 221 calculates the corneal refractive power, the corneal astigmatism power, and the corneal astigmatism axis angle of the right eye to be examined ER based on the corneal annular images of the right eye to be examined ER acquired by the anterior eye portion observation system 5. For example, with respect to each corneal annular image, the ocular refractive power calculating section 221 calculates the corneal curvature radii of the strong principal meridian and the weak principal meridian of the corneal front surface by analyzing the corneal annular image, and calculates the parameters based on the corneal curvature radii.

[0231] (Image forming section 222)

[0232] The image forming section 222 forms the image data of the OCT image (tomographic image) of the eye to be examined based on the detection signal of the interference light LC obtained by the CCD image sensor 115. That is, the image forming section 222 forms the image data of the eye to be examined based on the detection result of the interference light LC of the interference optical system. This processing includes a filter processing, an FFT (Fast Fourier Transform) processing, and the like as with the conventional spectral domain type OCT. The image data thus acquired is a data set including a group of image data formed by imaging the reflection intensity of a plurality of A lines (the paths of the respective measurement light LSs in the eye to be examined).

[0233] In order to improve the image quality, a plurality of data sets collected by repeatedly performing scanning a plurality of times with the same pattern can be superimposed (additive average).

[0234] (Data processing section 223)

[0235] The data processing section 223 performs various data processing (image processing), analysis processing on the tomographic images formed by the image forming section 222. For example, the data processing section 223 performs correction processing such as brightness correction, dispersion correction, and the like of the images. In addition, the data processing section 223 performs various image processing, analysis processing on the images (anterior eye portion images, and the like) obtained using the anterior eye portion observation system 5.

[0236] The data processing section 223 can form the body data (voxel data) of the eye to be examined by performing known image processing such as interpolation processing of interpolating pixels between the tomographic images. In a case where an image is displayed based on the body data, the data processing section 223 performs rendering processing on the body data to form a simulated three-dimensional image when viewed from a specified line-of-sight direction.

[0237] The data processing section 223 can form image data of a three-dimensional image of the fundus or the anterior eye portion by performing known image processing such as interpolation processing of interpolating pixels between the OCT images (tomographic images) formed by the image forming section 222. Further, the image data of the three-dimensional image refers to image data in which the positions of pixels are defined by a three-dimensional coordinate system. The image data of the three-dimensional image includes image data formed of voxels arranged three-dimensionally. This image data is referred to as body data or voxel data, and the like. In a case where an image is displayed based on the body data, the data processing section 223 performs rendering processing (stereoscopic rendering, MIP (Maximum Intensity Projection), and the like) on the body data to form image data of a simulated three-dimensional image when viewed from a specified line-of-sight direction. This simulated three-dimensional image is displayed in a display device such as the display section 270.

[0238] In addition, as the image data of the three-dimensional image, stack data of a plurality of tomographic images can also be formed. The stack data is image data obtained by three-dimensionally arranging a plurality of tomographic images obtained along a plurality of scan lines based on the positional relationship of the scan lines. That is, the stack data is image data obtained by representing (that is, embedding in one three-dimensional space) a plurality of tomographic images defined by originally separate two-dimensional coordinate systems by one three-dimensional coordinate system.

[0239] The data processing section 223 can form a B-mode image in an arbitrary cross section (longitudinal cross-sectional image, axial cross-sectional image), a C-mode image in an arbitrary cross section (transverse cross-sectional image, horizontal cross-sectional image), a projection image, a shadow image, and the like by performing various rendering on the acquired three-dimensional data set (volume data, stack data, and the like). An image of an arbitrary cross section such as a B-mode image, a C-mode image is formed by selecting pixels (pixels, voxels) on a designated cross section from the three-dimensional data set. A projection image is formed by projecting the three-dimensional data set in a predetermined direction (Z direction, depth direction, axial direction). A shadow image is formed by projecting a portion of the three-dimensional data set (for example, a portion of data corresponding to a designated layer) in a predetermined direction. An image in which the front side of the eye to be examined is regarded as a viewpoint like a C-mode image, a projection image, a shadow image is referred to as an en-face image.

[0240] The data processing section 223 can construct a B-mode image, an en-face image (vessel emphasis image, angiogram) in which retinal blood vessels, choroidal blood vessels are emphasized on the basis of data (for example, B-scan image data) collected in time series by OCT scanning. For example, time-series OCT data can be collected by repeatedly scanning substantially the same portion of the eye to be examined.

[0241] In several embodiments, the data processing section 223 compares time-series B-scan images obtained by B-scanning substantially the same portion, transforms pixel values of a portion of change in signal intensity to pixel values corresponding to the amount of change, thereby constructing an emphasis image in which the portion of change is emphasized. Also, the data processing section 223 extracts information of a predetermined thickness amount in a desired portion from the constructed plurality of emphasis images, constructs an en-face image, thereby forming an OCTA image.

[0242] The images generated by the data processing section 223 (for example, three-dimensional image, B-mode image, C-mode image, projection image, shadow image, OCTA image) are also included in the OCT image.

[0243] In addition, the data processing section 223 analyzes the two captured images acquired substantially simultaneously by the two anterior eye portion cameras as described above, respectively, and specifies characteristic positions corresponding to characteristic portions of the anterior eye portion. The data processing section 223 calculates the three-dimensional position of the characteristic portions (that is, the three-dimensional position of the eye to be examined) by applying a known triangulation method to the positions of the two anterior eye portion cameras and the characteristic positions corresponding to the characteristic portions in the two captured images. The calculated three-dimensional position can be used for position alignment of the optical system with respect to the eye to be examined.

[0244] Further, the ophthalmic apparatus 1 can measure an intraocular parameter by performing OCT scanning on the left eye EL or the right eye ER. Examples of the intraocular parameter include an axial length, a thickness of a predetermined layer region, a distance between predetermined sites, and the like.

[0245] In the first embodiment, the data processing portion 223 is provided as an intraocular parameter calculation portion that calculates an axial length. In this case, the data processing portion 223 can calculate a distance between a position corresponding to a corneal vertex and a position corresponding to a Retinal Pigment Epithelium (hereinafter, RPE) layer as the axial length based on the detection result of the interference light LC obtained by performing OCT scanning. For example, the data processing portion 223 specifies the position of the corneal vertex and the position of the RPE layer by specifying the positions of the maxima of the intensities of the interference signals corresponding to the detection result of the interference light LC, and calculates a distance between the two positions specified as the axial length. For example, the data processing portion 223 performs a segmentation process on an OCT image formed based on the detection result of the interference light LC, specifies the position of the corneal vertex and the position of the RPE layer based on a plurality of layer regions specified, and calculates a distance between the two positions specified as the axial length.

[0246] (Display portion 270, operation portion 280)

[0247] The display portion 270 displays information under the control of the control portion 210 as a user interface portion.

[0248] The operation portion 280 is used for operating the ophthalmic apparatus as a user interface portion. The operation portion 280 includes various hardware keys (joysticks, buttons, switches, and the like) provided to the ophthalmic apparatus. In addition, the operation portion 280 can include various software keys (buttons, icons, menus, and the like) displayed on a touch panel-type display screen.

[0249] At least a part of the display portion 270 and the operation portion 280 can be integrally configured. As a typical example, a touch panel-type display screen is included.

[0250] (Communication portion 290)

[0251] The communication section 290 has a function of communicating with an external device not shown. The communication section 290 has a communication interface corresponding to a connection method with the external device. As examples of the external device, there are included a spectacle lens measuring device for measuring optical characteristics of a lens. The spectacle lens measuring device measures a power and the like of a spectacle lens worn by a subject, and inputs the measurement data to the ophthalmic device 1. In addition, the external device can be a device (reader) that reads information from an arbitrary ophthalmic device, a recording medium, a device (recorder) that writes information to a recording medium, and the like. Further, the external device can be a hospital information system (HIS) server, a DICOM (Digital Imaging and Communication in Medicine) server, a doctor terminal, a mobile terminal, a personal terminal, a cloud server, and the like. The communication section 290 can be provided, for example, to the processing section 9.

[0252] The components and mechanisms that adjust the optical axis of the OCT optical system 8 in any one of the first to third adjustment examples are examples of the "optical axis adjustment section" of the embodiment. The data processing section 223 is an example of the "intraocular parameter calculation section" of the embodiment. The anterior eye section cameras 15LA, 15LB, 15RA, 15RB, and 15LR are examples of the "two or more photographing sections" of the embodiment. The anterior eye section camera 15LA is an example of the "first photographing section" of the embodiment. The anterior eye section camera 15LR is an example of the "second photographing section" of the embodiment. The anterior eye section camera 15RA is an example of the "third photographing section" of the embodiment. The catoptric measurement projection system 6 and the catoptric measurement light receiving system 7 are examples of the "refractive power measurement optical system" of the embodiment.

[0253] <WORKING EXAMPLE>

[0254] A working example of the ophthalmic device 1 of the first embodiment will be described.

[0255] Figure 12 And Figure 13 An example of the working of the ophthalmic device 1 is shown. Figure 12 A flowchart showing a working example of the ophthalmic device 1 in a case where the catoptric measurement and the OCT measurement are sequentially performed is shown. Figure 13 A flowchart showing a processing example of the step S2 of Figure 12 is shown. The computer program for implementing the processing shown in Figure 12 and Figure 13 is stored in the storage section 212. The main control section 211 performs the working in accordance with the computer program, and executes the processing shown in Figure 12 and Figure 13 .

[0256] Here, it is assumed that the processing of Figure 12The flow shown is preceded by a preliminary determination of whether to perform the inspection in either the near vision or the distance vision state.

[0257] (S1: Adjustment of convergence angle)

[0258] First, the main control section 211 controls the moving mechanism 320 to rotate the dichroic mirrors ML, MR so as to match the viewing distance corresponding to the predetermined near vision or distance vision state, and adjusts the convergence angle.

[0259] As shown in Figure 4 , the dichroic mirrors ML, MR change the deflection direction of the optical axis deflected by the optical axis switching member SW.

[0260] (S2: Alignment)

[0261] Next, the main control section 211 performs alignment. Step S2 is described in detail later.

[0262] In step S2, the alignment of the positions of the optical system 300 with respect to the left and right eyes under examination EL, ER is performed.

[0263] (S3: Acquisition of anterior eye portion images of both eyes)

[0264] Next, the main control section 211 controls the anterior eye portion observation system 5 to acquire the anterior eye portion images of both eyes.

[0265] Specifically, the main control section 211 controls the corneal measurement system 3 and turns on the corneal ring light source 32 to project a ring-shaped light beam onto the cornea CLr of the left eye under examination EL. Next, the main control section 211 controls the anterior eye portion illumination light source 50 to turn on the anterior eye portion illumination light source 50 and illuminate the anterior eye portion of the left eye under examination EL. Thereafter, the main control section 211 acquires the left eye under examination EL anterior eye portion image that depicts the anterior eye portion of the left eye under examination EL with the corneal ring image superimposed thereon, by receiving the light-receiving result of the return light of the illumination light on the imaging surface of the imaging element 59. Similarly, the main control section 211 controls the corneal measurement system 3 to turn on the corneal ring light source 32 to project a ring-shaped light beam onto the cornea CRr of the right eye under examination ER. Next, the main control section 211 controls the anterior eye portion illumination light source 50 to turn on the anterior eye portion illumination light source 50 and illuminate the anterior eye portion of the right eye under examination ER. Thereafter, the main control section 211 acquires the right eye under examination ER anterior eye portion image that depicts the anterior eye portion of the right eye under examination ER with the corneal ring image superimposed thereon, by receiving the light-receiving result of the return light of the illumination light on the imaging surface of the imaging element 59.

[0266] (S4: Corneal shape analysis)

[0267] Next, the main control section 211 analyzes the front eye portion images of both eyes acquired in step S3 by controlling the ocular power calculation section 221. As described above, the ocular power calculation section 221 specifies the corneal ring image of each of the left and right examination eyes EL and ER depicted in the front eye portion images, and calculates the respective corneal powers, corneal astigmatism degrees, and corneal astigmatism axis angles of the left and right examination eyes EL and ER from the specified corneal ring image of each.

[0268] (S5: Temporary measurement for each single eye)

[0269] Next, the main control section 211 performs a temporary measurement for each single eye for the reflection measurement. In the temporary measurement, the focusing state in the reflection measurement optical system is changed in accordance with the power of each of the left and right examination eyes EL and ER. In the reflection measurement (the present measurement), the power of each of the left and right examination eyes EL and ER is measured while promoting the clouding of the left and right examination eyes EL and ER with the focusing state changed by the temporary measurement as a reference.

[0270] For example, the reflection measurement light source 61, the focusing lenses 74, 87 are moved in the optical axis direction and disposed at positions corresponding to the power of the examination eye. The main control section 211 turns on the reflection measurement light source 61 and causes the rotating prism 66 to start rotating.

[0271] Here, the temporary measurement is performed on the right examination eye ER after the temporary measurement is performed on the left examination eye EL.

[0272] The main control section 211 causes the annular measurement pattern light beam to be projected to the left examination eye EL. The annular image based on the return light of the measurement pattern light beam from the left examination eye EL is imaged on the imaging surface of the imaging element 59.

[0273] The main control section 211 determines whether the annular image based on the return light from the fundus detected by the imaging element 59 can be acquired. For example, the main control section 211 detects the position (pixel) of the edge of the image based on the return light detected by the imaging element 59 and determines whether the width (difference between the outer diameter and the inner diameter) of the image is equal to or greater than a predetermined value. Alternatively, the main control section 211 can determine whether the annular image can be formed based on a point (pixel) equal to or greater than a predetermined height (ring diameter), thereby determining whether the annular image can be acquired.

[0274] When it is determined that the annular image can be acquired, the ocular power calculation section 221 analyzes the annular image based on the return light of the projected measurement pattern light beam by a known method and calculates the temporary spherical degree S and the temporary astigmatism degree C with respect to the left examination eye EL.

[0275] The main control section 211 moves the catoptric measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to a position of the equivalent spherical power (S+C / 2) based on the calculated temporary spherical power S and the temporary astigmatism power C.

[0276] The main control section 211 again projects the annular measurement pattern light beam to the left eye EL to be examined. The annular image based on the return light of the measurement pattern light beam from the left eye EL to be examined is imaged on the imaging surface of the imaging element 59. The main control section 211 determines whether or not the annular image based on the return light from the fundus ELf detected by the imaging element 59 can be acquired.

[0277] When it is determined that the annular image can be acquired, the main control section 211 calculates the temporary spherical power S and the temporary astigmatism power C by analyzing the annular image based on the return light of the projected measurement pattern light beam by a known method with respect to the left eye EL to be examined.

[0278] Next, with respect to the right eye ER to be examined, similarly, the temporary spherical power S and the temporary astigmatism power C are calculated. At this time, as described above, the optical axis of the catoptric measurement optical system is switched by the optical axis switching member SW.

[0279] The main control section 211 controls the refractive power calculating section 221 to calculate the intermediate power position of the left eye EL to be examined and the right eye ER to be examined. For example, the intermediate power position can be a position corresponding to the intermediate power ((ESR+ESL) / 2) of the equivalent spherical power ESL of the left eye EL to be examined and the equivalent spherical power ESR of the right eye ER to be examined.

[0280] The main control section 211 moves the catoptric measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to the intermediate power position. The moved position is a position corresponding to the temporary far point.

[0281] In several embodiments, the main control section 211 does not calculate the intermediate power position, and moves the catoptric measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to the equivalent spherical power position in the temporary measurement of each of the left eye EL to be examined and the right eye ER to be examined.

[0282] (S6: Promoting the clouding of both eyes)

[0283] Next, the main control section 211 promotes the clouding of both eyes by moving the liquid crystal panel 41 further to the clouding position from the position calculated in the temporary measurement at step S5.

[0284] (S7: Performing the refractive power measurement for each single eye)

[0285] Next, the main control section 211 performs the catoptric measurement for each single eye.

[0286] Here, after the reflection measurement on the left eye under examination EL, the reflection measurement on the right eye under examination ER is performed.

[0287] Specifically, the main control section 211 turns on the reflection measurement light source 61 in a case where the reflection measurement light source 61 is turned off. In addition, the main control section 211 starts the rotation of the rotating prism 66 in a case where the rotation of the rotating prism 66 is stopped. In a case where the measurement is performed in a state of looking at a distance, the fixation target is a position equivalent to the far point obtained in step S5 as described above. In a case where the measurement is performed in a state of looking at a near distance, the fixation target is a fixed position determined in advance.

[0288] The main control section 211 acquires the ring image by controlling the reflection measurement projection system 6 and the reflection measurement light receiving system 7 as in the temporary measurement in step S5. That is, the reflection measurement optical system projects the measurement pattern light beam for the left eye under examination, acquires the ring image so that a position corresponding to the intermediate degree of the refractive power of the left eye under examination EL and the refractive power of the right eye under examination ER becomes the focal position. The main control section 211 causes the eye refractive power calculation section 221 to calculate the spherical degree, the astigmatic degree, and the astigmatic axis angle on the basis of the analysis result of the ring image and the movement amount of the focusing lens 74. The calculated spherical degree, astigmatic degree, and astigmatic axis angle are saved to the storage section 212.

[0289] Next, the reflection measurement is performed with respect to the right eye under examination ER as well. At this time, the optical axis of the reflection measurement optical system is switched by the optical axis switching member SW as described above.

[0290] That is, the reflection measurement optical system projects the measurement pattern light beam to the left eye under examination EL along the measurement optical axis OL via the objective lens 51, and projects the measurement pattern light beam to the right eye under examination ER along the measurement optical axis OR, receives the return light of the measurement pattern light beam from the left eye under examination EL and the return light of the measurement pattern light beam from the right eye under examination ER. The eye refractive power calculation section 221 calculates the refractive power of the left eye under examination EL on the basis of the light receiving result of the return light of the measurement pattern light beam from the left eye under examination EL, and calculates the refractive power of the right eye under examination ER on the basis of the light receiving result of the return light of the measurement pattern light beam from the right eye under examination ER.

[0291] In several embodiments, the acquisition of the anterior eye portion image in step S3 and the corneal shape analysis in step S4 are simultaneously performed in step S7. In several embodiments, the alignment in step S2 is performed before the transition to step S8.

[0292] (S8: OCT measurement for each monocular eye)

[0293] Next, the main control section 211 performs the OCT measurement for each monocular eye by controlling the OCT optical system 8.

[0294] Here, after the OCT measurement of the left eye EL, the OCT measurement of the right eye ER is performed.

[0295] For example, the main control section 211 prompts the left eye EL for the fixation target for the OCT measurement, controls the OCT optical system 8 to perform the OCT provisional measurement, and acquires the adjustment tomogram for adjusting the reference position of the measurement range in the depth direction. Specifically, the main control section 211 controls the optical scanner 88 to deflect the measurement light LS generated from the light source unit 101, and scans a predetermined portion (for example, the fundus) of the left eye EL with the deflected measurement light LS. The detection result of the interference light LC obtained by the scanning of the measurement light LS is sent to the image forming section 222. The image forming section 222 forms the tomogram (OCT image) of the left eye EL from the obtained interference signal.

[0296] Next, the main control section 211 adjusts the reference position of the measurement range in the depth direction (Z direction). For example, the main control section 211 causes the data processing section 223 to specify a predetermined portion (for example, the sclera) in the obtained tomogram, and sets a position separated by a predetermined distance from the position of the specified predetermined portion in the depth direction as the reference position of the measurement range. Alternatively, a predetermined position determined in advance can be set as the reference position of the measurement range so that the optical path length of the measurement light LS and the reference light LR substantially coincide.

[0297] Next, the main control section 211 performs the focus adjustment control and the polarization wave adjustment control. For example, the main control section 211 controls the OCT unit 100 to perform the OCT measurement after moving the focusing lens 87 by a predetermined distance.

[0298] The main control section 211 causes the data processing section 223 to determine the focus state of the measurement light LS based on the detection result of the interference light obtained by the OCT measurement. For example, the data processing section 223 calculates a predetermined evaluation value related to the quality of the OCT image, and determines whether the calculated evaluation value is below a threshold value. In several embodiments, the focus adjustment continues until the calculated evaluation value becomes below the threshold value. That is, when the evaluation value is below the threshold value, it is determined that the focus state of the measurement light LS is appropriate, and the focus adjustment continues until the focus state of the measurement light LS is determined to be appropriate.

[0299] In several embodiments, the main control section 211 acquires the interference signal while performing the repeated OCT measurement as described above, and monitors the intensity (interference intensity, interference sensitivity) of the interference signal acquired sequentially. Also, the focusing lens 87 is moved while this monitoring process is performed, and thus the position of the focusing lens 87 at which the interference intensity is the maximum is searched. Based on such focus adjustment, the focusing lens 87 can be guided to the position at which the interference intensity is optimized.

[0300] Further, the data processing section 223 analyzes the detection results of the interference light measured by the OCT, and determines the polarization wave state of at least one of the measurement light LS and the reference light LR.

[0301] For example, the main control section 211 performs repeated OCT measurement while controlling the polarization wave controller 106 in accordance with a predetermined algorithm. In several embodiments, the main control section 211 controls the optical attenuator 105 to change the attenuation amount of the reference light LR. The data processing section 223 calculates a predetermined evaluation value related to the quality of the OCT image by analyzing the detection results of the interference light LC repeatedly acquired by the OCT measurement, and determines whether the calculated evaluation value is below a threshold value. The threshold value is set in advance. The polarization wave adjustment continues until the calculated evaluation value becomes below the threshold value. That is, when the evaluation value is below the threshold value, it is determined that the polarization wave state of the measurement light LS is appropriate, and the polarization wave adjustment continues until it is determined that the polarization wave state of the measurement light LS is appropriate.

[0302] In several embodiments, the main control section 211 can also monitor the interference intensity in the polarization wave adjustment.

[0303] When the position adjustment in the depth direction, the focus adjustment, and the polarization wave adjustment are completed, the main control section 211 controls the optical scanner 88 to scan a predetermined portion of the fundus of the left eye EL using the measurement light LS. For example, the detection signal obtained by the scanning of the measurement light LS is sent to the image forming section 222. The image forming section 222 forms a tomographic image of the fundus based on the obtained detection signal.

[0304] Next, with respect to the right eye ER, OCT measurement is similarly performed. At this time, as described above, the optical axis of the OCT optical system 8 is switched by the optical axis switching member SW.

[0305] In several embodiments, before OCT measurement is performed on one of the left eye EL and the right eye ER using the measurement light LS, the main control section 211 controls the OCT optical system 8 to adjust the optical path length of the reference light path based on the axial length and the refractive power of the other of the left eye EL and the right eye ER. That is, in view of the fact that the optical path length of the reference light path, which is one of the measurement environments of the OCT measurement, is often associated with the axial length and the refractive power of the eye and the optical path length of the reference light path is approximately the same in the left and right eyes, the optical path length of the reference light path at the time of the OCT measurement of the eye for which the measurement is first performed is specified based on the axial length and the refractive power of the eye for which the measurement is next performed, and the optical path length of the reference light path at the time of the OCT measurement of the eye is adjusted to the specified optical path length. Thereby, the time required for the OCT measurement of both eyes can be greatly reduced.

[0306] As for each of the left eye under examination EL and the right eye under examination ER, the main control section 211 controls the data processing section 223 to calculate, as the axial length, the distance between the position corresponding to the corneal vertex and the position corresponding to the RPE layer, on the basis of the obtained detection signal or tomographic image. The data processing section 223 can calculate an intraocular parameter other than the axial length. For example, the main control section 211 controls the OCT optical system 8 to sequentially or simultaneously scan the fundus and the cornea (anterior eye portion). The main control section 211 controls the data processing section 223 to calculate, as the axial length, the distance between the position corresponding to the corneal vertex and the position corresponding to the RPE layer, on the basis of the detection signal obtained by scanning the cornea or the detection signal or tomographic image obtained by scanning the tomographic image and the fundus. For example, a method of calculating such an axial length is disclosed in Japanese Patent Application Publication No. 2020-044027.

[0307] The operation of the ophthalmic apparatus 1 ends (END).

[0308] In several embodiments, after the process of one of the distant viewing time and the near viewing time is executed steps S1 to S8, the process of the other of the distant viewing time and the near viewing time is executed steps S1 to S8, whereby the examination is performed in the state of both the distant viewing time and the near viewing time.

[0309] The step S2 is executed as shown in Figure 13 . Figure 12

[0310] (S21: Specifying the pupil position of both eyes)

[0311] First, the main control section 211 specifies the feature position of both eyes on the basis of the captured images obtained by controlling the anterior eye portion cameras 15LA, 15RA, 15LB, 15RB. In the present embodiment, the pupil position is specified as the feature position.

[0312] Specifically, the main control section 211 controls the anterior eye portion cameras 15LA, 15LB to substantially simultaneously capture the left eye under examination EL from different directions, and acquires two captured images (anterior eye portion images). Similarly, the main control section 211 controls the anterior eye portion cameras 15RA, 15RB to substantially simultaneously capture the right eye under examination ER from different directions, and acquires two captured images. In several embodiments, the two captured images of the left eye under examination EL and the two captured images of the right eye under examination ER are substantially simultaneously captured.

[0313] The specifying process of the pupil position of the left eye under examination EL is the same as the specifying process of the pupil position of the right eye under examination ER. Hereinafter, the specifying process of the pupil position of the left eye under examination EL will mainly be described.

[0314] ​The main control section 211 controls the data processing section 223 functioning as a feature position specifying section to analyze the two captured images obtained by the front eye section cameras 15LA, 15LB and specify the pupil position (pupil center position or pupil barycentric position) of the left eye under examination EL.

[0315] In this case, with respect to each captured image, the data processing section 223 specifies an image region (pupil region) corresponding to the pupil based on the distribution of pixel values (luminance values, etc.). Normally, the pupil is depicted with lower luminance than other parts, so the pupil region can be specified by searching for an image region with low luminance. At this time, the pupil region can also be specified taking into account the shape of the pupil. That is, it can be configured to specify the pupil region by searching for an image region that is roughly circular and has low luminance.

[0316] Next, the data processing section 223 specifies the center position of the specified pupil region. As described above, the pupil is roughly circular, so the outline of the pupil region can be specified, the center position of this outline (approximate circle or approximate ellipse) can be specified, and this can be set as the pupil center position. Alternatively, the barycentric position of the pupil region can be found, and this barycentric position can be specified as the pupil barycentric position.

[0317] The data processing section 223 can successively specify the pupil position for the captured images successively obtained by the front eye section cameras 15LA, 15LB. Alternatively, the data processing section 223 can specify the pupil position for the captured images successively obtained by the front eye section cameras 15LA, 15LB at intervals of more than one arbitrary number of frames.

[0318] Next, the data processing section 223, as a three-dimensional position calculation section, specifies the three-dimensional position of the feature position as the three-dimensional position of the eye under examination based on the positions of the front eye section cameras 15LA, 15LB and the specified pupil positions. For example, as disclosed in Japanese Patent Application Publication No. 2013-248376, the data processing section 223 calculates the three-dimensional position of the eye under examination by applying a well-known triangulation method to the positions (known) of the two front eye section cameras 15LA, 15LB and the pupil positions in the two captured images.

[0319] The pupil position of the right eye under examination ER can also be specified by the same processing as described above.

[0320] (S22: Movement of measurement optical axis)

[0321] The main control section 211 controls the movement of the measurement optical system 300, the adjustment of the interpupillary distance of the optical axis switching member SW, and the position of the fixation target presented by the fixation projection system 4L, 4R based on the pupil positions of both eyes specified in step S21.

[0322] Specifically, the interpupillary distance is specified based on the pupil positions of the both eyes specified in step S21. For example, the main control section 211 adjusts at least one of the moving mechanism 200, the moving mechanism 310, and the fixation projection systems 4L, 4R so that the pupil positions of the both eyes specified in step S21 are closest to (substantially coincide with) the respective known measurement optical axes OL, OR. The main control section 211 can change the relative positions of the measurement optical system 300 with respect to the left and right examination eyes EL, ER by controlling the moving mechanism 200. The main control section 211 can change the distance between the measurement optical axes OL, OR by controlling the moving mechanism 310, the optical axis switching member SW. The main control section 211 can change the fixation positions (fixation target presentation positions) of each of the left and right examination eyes EL, ER by controlling the fixation projection systems 4L, 4R.

[0323] As a result, the positions in the X and Y directions of the left examination eye EL are adjusted to substantially coincide with the positions in the X and Y directions of the measurement optical axis OL, and the distance in the Z direction becomes the predetermined working distance.

[0324] In several embodiments, the main control section 211 determines whether the arrangement directions of the left and right examination eyes EL, ER are parallel to the X direction (i.e., whether the heights of the both eyes are shifted) based on the pupil positions of the both eyes specified in step S21. In this case, the main control section 211 controls the moving mechanisms 310, 320 based on the pupil positions of the both eyes specified in step S21, whereby it can change at least one of the deflection direction of the optical axis switching member SW and the deflection directions of the dichroic mirrors ML, MR.

[0325] In several embodiments, when it is determined that the arrangement directions of the left and right examination eyes EL, ER are not parallel to the X direction, the main control section 211 can control the display section 270 to prompt the examinee to tilt the face. The main control section 211 can also prompt the examinee to tilt the face by voice output.

[0326] (S23: Acquire anterior eye portion images of both eyes)

[0327] Next, the main control section 211 controls the anterior eye portion cameras 15LA, 15RA, 15LB, 15RB again after the XY alignment light source 21 is lit, and acquires anterior eye portion images of the both eyes that depict XY bright spot images based on reflected light from the light from the XY alignment light source 21.

[0328] (S24: Detect XY bright spot images?)

[0329] Next, the main control section 211 controls the data processing section 223 to detect XY bright spot images from the anterior eye portion images of the both eyes acquired in step S23.

[0330] For example, the data processing section 223 detects whether the two front eye images of the left eye under examination EL and the two front eye images of the right eye under examination ER depict the XY bright spot images based on the pixel values, respectively. When it is detected by the data processing section 223 that all of the four front eye images depict the XY bright spot images (S24: YES), the operation of the ophthalmic apparatus 1 shifts to step S25. When it is detected by the data processing section 223 that at least one of the four front eye images does not depict the XY bright spot image (S24: NO), the operation of the ophthalmic apparatus 1 shifts to step S22.

[0331] (S25: Specify the positions of the XY bright spot images of the both eyes)

[0332] When the XY bright spot images are detected in the front eye images of the both eyes in step S24 (S24: YES), the main control section 211 controls the data processing section 223 to specify the positions of the XY bright spot images of the both eyes detected in step S24. In step S25, the positions of the XY bright spot images of the both eyes are specified by the same specifying process as in step S21. That is, instead of the pupil positions of the both eyes specified in step S21, the positions of the XY bright spot images of the both eyes specified in step S25 are specified.

[0333] (S26: Move the measurement optical axis)

[0334] The main control section 211 controls the movement of the measurement optical system 300, the adjustment of the interpupillary distance of the optical axis switching member SW, and the presentation of the fixation target position by the fixation projection systems 4L, 4R based on the positions of the XY bright spot images of the both eyes specified in step S25. Figure 3 The adjustment of the interpupillary distance of the optical axis switching member SW and the presentation of the fixation target position by the fixation projection systems 4L, 4R are shown.

[0335] In step S26, the adjustment of the measurement optical axis is performed as in step S22.

[0336] (S27: Acquire front eye images of the both eyes)

[0337] Next, the main control section 211 controls the front eye cameras 15LA, 15RA, 15LB, 15RB to acquire the front eye images of the both eyes.

[0338] (S28: Specify the positions of the XY bright spot images of the both eyes)

[0339] Next, the main control section 211 controls the data processing section 223 to specify the positions of the XY bright spot images of the both eyes based on the front eye images of the both eyes acquired in step S27 as in step S25.

[0340] (S29: Alignment complete?)

[0341] Next, the main control section 211 determines whether each of the positions of the XY bright spot images of the both eyes designated in step S28 is within a predetermined alignment completion range.

[0342] When it is determined that each of the positions of the XY bright spot images of the both eyes is within the predetermined alignment completion range (S29: YES), Figure 12 The processing of step S2 ends (END). When at least one of the positions of the XY bright spot images of the both eyes is not within the predetermined alignment completion range (S29: NO), the operation of the ophthalmic apparatus 1 shifts to step S26.

[0343] As described above, in the ophthalmic apparatus 1 of the first embodiment, Figure 12 In step S2 of the ophthalmic apparatus 1, the main control section 211 changes the relative positions of the OCT optical system 8 with respect to the left and right examination eyes EL and ER based on the two or more images obtained by the two or more front eye section cameras, while changing the orientations of the measurement optical axes OL and OR and the distance between the measurement optical axes OL and OR, so that the measurement optical axis OL coincides with the visual axis of the left examination eye EL and the measurement optical axis OR coincides with the visual axis of the right examination eye ER.

[0344] As described above, according to the first embodiment, the optical axis switching member SW is used to switch so that the optical axis of the measurement optical system 300 (specifically, the optical axis of the OCT optical system 8, the optical axis of the retroreflected measurement optical system coupled optically coaxially with the optical axis of the OCT optical system 8) substantially coincides with any one of the measurement optical axes OL and OR arranged apart from each other, and thus the OCT measurement can be sequentially performed on the both eyes in the open eyes state. Thereby, an ophthalmic apparatus which is low in cost and saves space and can measure the characteristics of the both eyes with high precision can be provided. In particular, the miniaturization and low cost of the optical system of the ophthalmic apparatus which can perform the OCT measurement on the both eyes can be achieved.

[0345] [Second Embodiment]

[0346] In the first embodiment, the case where the fixation projection systems 4L and 4R are provided in the transmission directions of the dichroic mirrors ML and MR is described, but the structure of the ophthalmic apparatus of the embodiment is not limited thereto. For example, the measurement optical system can also be provided with fixation projection systems common to the both eyes.

[0347] Hereinafter, the ophthalmic apparatus of the second embodiment will be described focusing on the distinguishing features from the ophthalmic apparatus 1 of the first embodiment.

[0348] Figure 14 and Figure 15 An example of the structure of the optical system of the ophthalmic apparatus of the second embodiment is shown. Figure 14 With Figure 1The structure of the optical system of the ophthalmic apparatus of the second embodiment is also schematically shown as viewed from above. Figure 15 is a block diagram showing a structure example of the measurement optical system 300a. Figure 14

[0349] The structure of the optical system of the ophthalmic apparatus 1a of the second embodiment differs from that of the optical system of the ophthalmic apparatus 1 of the first embodiment in that a mirror ML1 is provided instead of the dichroic mirror ML, a mirror MR1 is provided instead of the dichroic mirror MR, and a measurement optical system 300a is provided instead of the measurement optical system 300 and the fixation projection systems 4L, 4R.

[0350] The mirror ML1 deflects the measurement optical axis OL deflected by the optical axis switching member SW toward the left examined eye EL. The mirror MR1 deflects the measurement optical axis OR deflected by the optical axis switching member SW toward the right examined eye ER.

[0351] As shown in Figure 15 , the measurement optical system 300a includes the corneal measurement system 3, the fixation projection system 4, the anterior eye portion observation system 5, the reflection measurement projection system 6, the reflection measurement light receiving system 7, and the OCT optical system 8.

[0352] As with the ophthalmic apparatus 1, the ophthalmic apparatus 1a also includes an optical axis adjustment section, an interpupillary distance adjustment section, and a convergence angle adjustment section.

[0353] Figure 16 An explanatory diagram showing an operation example of the interpupillary distance adjustment section in the ophthalmic apparatus 1a of the second embodiment is shown. In Figure 16 , the same reference numerals are attached to the same parts as Figure 3 or Figure 14 , and the explanation is appropriately omitted.

[0354] The interpupillary distance adjustment section, as with the first embodiment, changes the distance in the X direction between the measurement optical axes OL, OR by moving the optical axis switching member SW having the measurement optical axis OL or the measurement optical axis OR (Z direction, optical axis of the measurement optical system 300a) along the measurement optical axis OL or the measurement optical axis OR. As a result, as shown in Figure 16 , the positions of the optical axes deflected by the mirrors ML1, MR1 change, the measurement optical axis OL becomes a measurement optical axis OL', and the measurement optical axis OR becomes a measurement optical axis OR'. As a result, the distance in the X direction between the measurement optical axes OL', OR' becomes an interpupillary distance PD', and the interpupillary distance is changed.

[0355] In the several embodiments, the interpupillary distance is changed by moving the optical axis switching member SW in the X direction as shown. Figure 16

[0356] ​​In several embodiments, the optical axis switching member SW is moved by a movement mechanism not shown under control from a control section to be described later. In this case, the function of the interpupillary distance adjustment section is realized by the control section and the movement mechanism not shown. In several embodiments, the optical axis switching member SW is moved manually by a movement mechanism not shown. In this case, the function of the interpupillary distance adjustment section is realized by the movement mechanism not shown.

[0357] Figure 17 An explanatory diagram showing an operation example of the convergence angle adjustment section in the ophthalmic apparatus 1a of the second embodiment is shown. In Figure 17 the same parts as Figure 4 or Figure 14 the same parts are attached with the same reference numerals, and the explanation is appropriately omitted.

[0358] The convergence angle adjustment section changes the orientation of at least one of the measurement optical axes OL, OR by changing at least one of the orientation of the mirror ML1 and the orientation of the mirror MR1, as in the first embodiment.

[0359] For example, the deflection surface of the mirror ML1 is configured to be able to rotate around a rotation axis extending in the Y-axis direction. For example, the deflection surface of the mirror MR1 is configured to be able to rotate around a rotation axis extending in the Y-axis direction. Thereby, as shown in Figure 17 the measurement optical axis OL deflected by the mirror ML1 becomes the measurement optical axis OL', the measurement optical axis OR becomes the measurement optical axis OR', and the convergence angle is changed.

[0360] In several embodiments, the mirrors ML1, MR1 are rotated by a movement mechanism (rotation mechanism) not shown under control from a control section to be described later. In this case, the function of the convergence angle adjustment section is realized by the control section and the movement mechanism not shown. In several embodiments, the mirrors ML1, MR1 are rotated manually by a movement mechanism (rotation mechanism) not shown. In this case, the function of the convergence angle adjustment section is realized by the movement mechanism not shown.

[0361] Figure 18 An example of the structure of the measurement optical system 300a of the second embodiment is shown. Figure 18 the same as Figure 5 is shown schematically from the side (X direction) looking at the measurement optical system 300a. In Figure 18 the same parts as Figure 5 or Figure 14 the same parts are attached with the same reference numerals, and the explanation is appropriately omitted.

[0362] The structure of the measurement optical system 300a differs from that of the measurement optical system 300 in that the dichroic mirror 83, the mirror 84, and the fixation projection system 4 are provided between the relay lens 82 and the relay lens 85, and the optical path of the fixation projection system 4 is coaxially coupled with the optical path of the OCT optical system 8 through the dichroic mirror 83.

[0363] The dichroic mirror 83 transmits light having a wavelength component of the visible region and reflects light having a wavelength component of the near-infrared region (or the infrared region). The fixation projection system 4 is disposed in the transmission direction of the dichroic mirror 83, and the OCT optical system 8 is disposed in the reflection direction of the dichroic mirror 83. Specifically, the dichroic mirror 83 is disposed between the relay lens 82 and the fixation projection system 4, and the mirror 84 is disposed between the dichroic mirror 83 and the OCT optical system 8.

[0364] The fixation projection system 4 projects a fixation light beam onto the fundus EIf of the left eye EL or the fundus Erf of the right eye ER on the measurement optical axis which is optically coaxially coupled with the optical axis of the objective lens 51 (the measurement optical system 300a), and presents a fixation target to the left eye EL or the right eye ER. The fixation projection system 4 includes the fixation unit 40 and the relay lenses 43 and 44. The fixation unit 40 includes the liquid crystal panel 41 and the relay lens 42. The liquid crystal panel 41 displays a pattern representing a fixation target under the control from the control section. The fixation position of the left eye EL or the right eye ER can be changed by changing the display position of the pattern in the screen of the liquid crystal panel 41. In addition, the fixation unit 40 can be moved in the optical axis direction under the control from the control section.

[0365] Light from the liquid crystal panel 41 passes through the relay lenses 42, 43, and 44, transmits the dichroic mirror 83, and is projected onto the eye to be examined in the same path as the measurement light LS from the OCT optical system 8.

[0366] In several embodiments, the fixation unit 40 can be independently moved in the optical axis direction with the relay lenses 43 and 44.

[0367] In addition, in the second embodiment as well as in the first embodiment, the optical axis of the OCT optical system 8 can be adjusted. For example, as the deflection member DF1, the mirror 84 is used and as the deflection member DF2, the dichroic mirror 83 is used, and the optical axis of the OCT optical system 8 can be adjusted as shown in the first adjustment example of Figure 9A In addition, in the second embodiment, the optical axis of the OCT optical system 8 can be adjusted as shown in the second adjustment example of Figure 9B In addition, in the third adjustment example in which the deflection direction of the optical axis of the OCT optical system 8 is changed by an optical member in the path of the measurement light, as an example of the optical member, the dichroic mirror 83 can be used. Figure 18mirror 81, the dichroic mirror 52, the dichroic mirror 83, the mirror 84, and a mirror not shown.

[0368] The fixation projection system 4 is an example of the "fixation optical system" of the embodiment. The dichroic mirror 83 is an example of the "optical path coupling member" of the embodiment. The mirror ML1 is an example of the "first reflecting member" of the embodiment. The mirror MR1 is an example of the "second reflecting member" of the embodiment. The converging angle adjustment section is an example of the "first adjustment section" of the embodiment. The moving mechanism that rotates the deflection surface of the optical axis switching member SW, the deflection surface of the mirror ML1, and the deflection surface of the mirror MR1 is an example of the "second adjustment section" of the embodiment.

[0369] Figure 19 An example of the functional configuration of the processing system of the ophthalmic apparatus 1a of the second embodiment is shown. Figure 19 An example of the functional block diagram of the processing system of the ophthalmic apparatus 1a is shown. In Figure 19 the same parts are attached with the same reference numerals, and the explanation is omitted as appropriate. Figure 10 or Figure 18 the same parts are attached with the same reference numerals, and the explanation is omitted as appropriate.

[0370] The structure of the processing system of the ophthalmic apparatus 1a is different from the structure of the processing system of the ophthalmic apparatus 1 shown Figure 10 in that the fixation projection system 4 is provided instead of the fixation projection systems 4L, 4R, and the processing section 9a is provided instead of the processing section 9.

[0371] The structure of the processing section 9a is different from the structure of the processing section 9 shown Figure 10 in that the control section 210a is provided instead of the control section 210. The control section 210a includes the main control section 211a and the storage section 212a. The main control section 211a can perform the same control as the main control section 211 except that the control of the fixation projection system 4 is performed instead of the control of the fixation projection systems 4L, 4R. The storage section 212a stores the same programs as the storage section 212 except that the processing of the control of the fixation projection systems 4L, 4R is not executed.

[0372] The operation of the ophthalmic apparatus 1a of the second embodiment is substantially the same as the operation of the ophthalmic apparatus 1 of the first embodiment shown Figure 12 and Figure 13 except that the control of the fixation projection system 4 is performed.

[0373] In the second embodiment, in a state in which the same fixation target is presented to both eyes in the open-eye state, the OCT measurement and the reflex measurement can be sequentially performed for each eye.

[0374] Specifically, instead of the control of the presentation of the fixation target to the left eye EL and the right eye ER independently by the main control section 211 through the fixation projection systems 4L, 4R, the main control section 211a controls the fixation projection system 4 so as to present the same fixation target to the left eye EL and the right eye ER.

[0375] For example, in the case where the examination is performed in the state of looking far in step S7 of Figure 12 the main control section 211a presents the fixation target to both eyes from the positions corresponding to the temporary spherical power S and the temporary astigmatism power C (or the equivalent spherical power) of the more positive side (far looking side) among the temporary spherical power S and the temporary astigmatism power C (or the equivalent spherical power) of the left eye EL and the temporary spherical power S and the temporary astigmatism power C (or the equivalent spherical power) of the right eye ER calculated in step S5 of Figure 12

[0376] For example, in the case where the examination is performed in the state of looking near in step S7 of Figure 12 the main control section 211a presents the fixation target to both eyes from the same positions as in the case where the examination is performed in the state of looking far. In several embodiments, in the case where the examinee is monovision, the main control section 211a presents the fixation target to both eyes from the positions corresponding to the temporary spherical power S and the temporary astigmatism power C (or the equivalent spherical power) of the more negative side (near looking side) among the temporary spherical power S and the temporary astigmatism power C (or the equivalent spherical power) of the left eye EL and the temporary spherical power S and the temporary astigmatism power C (or the equivalent spherical power) of the right eye ER calculated in step S5 of Figure 12

[0377] Further, similarly to step S22 of Figure 13 the main control section 211a can determine whether the arrangement direction of the left eye EL and the right eye ER is parallel to the X direction (i.e., whether the height of both eyes is shifted) based on the pupil positions of both eyes specified in step S21. In this case, the main control section 211a as the second adjustment section can change the deflection direction of the mirror ML1, the deflection direction of the mirror MR1, the orientation of the deflection surface of the optical axis switching member SW based on the pupil positions of both eyes specified in step S21, thereby adjusting the arrangement direction of the measurement optical axis OL and the measurement optical axis OR.

[0378] ​​In several embodiments, the main control section 211a can cause the optical axis switching member SW to switch the optical axis at high speed, thereby performing the reflection measurement in a state where both eyes are looking at the fixation target. At this time, the main control section 211a acquires a plurality of annular images of the return light based on the measurement pattern light beams of the left and right eyes when the optical axis is switched, and calculates the refractive power value by analyzing an image in which the acquired annular images are superimposed.

[0379] In several embodiments, in the structure of the second embodiment, a binocular single vision or a trial lens can be disposed in front of the eyes of the both eyes.

[0380] As described above, according to the second embodiment, as with the first embodiment, an ophthalmic apparatus that is low in cost and saves space and can measure the characteristics of both eyes with high precision can be provided. In particular, miniaturization and cost reduction of the optical system of the ophthalmic apparatus that can perform OCT measurement of both eyes can be achieved.

[0381] [Third Embodiment]

[0382] In the first embodiment, a case where the fixation projection systems 4L, 4R are disposed in the transmission directions of the dichroic mirrors ML, MR is described, but the structure of the ophthalmic apparatus of the embodiment is not limited thereto. For example, a fixation target prompting section common to both eyes can be disposed in the transmission directions of the dichroic mirrors ML, MR.

[0383] Hereinafter, the ophthalmic apparatus of the third embodiment will be described focusing on the distinguishing features from the ophthalmic apparatus 1 of the first embodiment.

[0384] Figure 20 An example of the structure of the optical system of the ophthalmic apparatus of the third embodiment is shown. Figure 20 As with Figure 1 An example of the structure of the optical system of the ophthalmic apparatus of the third embodiment is shown.

[0385] The structure of the optical system of the ophthalmic apparatus 1b of the third embodiment differs from that of the ophthalmic apparatus 1 of the first embodiment in that the fixation target prompting section 400 is disposed instead of the fixation projection systems 4L, 4R.

[0386] The fixation target prompting section 400 includes a fixation target chart. For example, the fixation target chart is disposed between the light source for illumination and the eye to be examined, and is a transmission type fixation target chart indicating a fixation target. In several embodiments, the fixation target chart is a film on which the transmission of the fixation target is printed. Examples of the fixation target include a landscape, a point target, and the like.

[0387] The control section illuminates the light source for illumination when the light reflex test is performed, and the chart is illuminated by light from the light source for illumination. Light that has passed through the chart passes through the dichroic mirrors ML, MR as the fixation light, and is projected to the left and right eyes EL, ER.

[0388] The dichroic mirror ML is an example of the "first optical path coupling member" of the embodiment. The dichroic mirror MR is an example of the "second optical path coupling member" of the embodiment.

[0389] Figure 21 An example of the functional configuration of the processing system of the ophthalmic apparatus 1b of the third embodiment is shown. Figure 21 An example of the functional block diagram of the processing system of the ophthalmic apparatus 1b is shown. In Figure 21 The same reference numerals are attached to the same parts as those of Figure 10 or Figure 20 and appropriate description is omitted.

[0390] The structure of the processing system of the ophthalmic apparatus 1b is different from that of the processing system of the ophthalmic apparatus 1 shown in Figure 12 the difference being that the fixation projection systems 4L, 4R are omitted, and the processing section 9b is provided instead of the processing section 9.

[0391] The structure of the processing section 9b is different from that of the processing section 9 shown in Figure 10 the difference being that the control section 210b is provided instead of the control section 210. The control section 210b includes the main control section 211b and the storage section 212b. The main control section 211b can perform the same control as the main control section 211 except that the control of the fixation projection systems 4L, 4R by the main control section 211 is omitted. The storage section 212b stores the same programs as the storage section 212 except for the processing of performing control of the fixation projection systems 4L, 4R.

[0392] The operation of the ophthalmic apparatus 1b of the third embodiment is substantially the same as that of the ophthalmic apparatus 1 of the first embodiment shown in Figure 12 and Figure 13 except that the control of the fixation projection systems 4L, 4R is omitted.

[0393] In the third embodiment, the same fixation chart is presented to both eyes during the light reflex test, the corneal test, and the OCT measurement. That is, the light reflex test can be performed on each eye in turn in a state in which the same fixation chart is presented to both eyes in a state in which both eyes are open. In addition, the OCT measurement can be performed on each eye in turn in a state in which the same fixation chart is presented to both eyes in a state in which both eyes are open.

[0394] In several embodiments, the fixation target presentation section 400 performs fixation target presentation by the operation of an examiner. In several embodiments, the fixation target presentation section 400 performs fixation target presentation under the control from the main control section 211b. In this case, the main control section 211b controls the fixation target presentation section 400 similarly to the control of the fixation target presentation system 4 of the second embodiment.

[0395] In several embodiments, in the structure of the third embodiment, a binocular single vision field or a trial lens can also be provided in front of the eyes of the binocular eyes.

[0396] As described above, according to the third embodiment, similarly to the first embodiment, an ophthalmic apparatus that is low in cost and saves space and that can measure the characteristics of binocular eyes with high precision can be provided. In particular, miniaturization and cost reduction of the optical system of an ophthalmic apparatus that can perform OCT measurement on binocular eyes can be achieved.

[0397] [Effects]

[0398] An ophthalmic apparatus of an embodiment is described.

[0399] An ophthalmic apparatus (1, 1a, 1b) of the first mode of the embodiment includes an objective lens (51), an OCT optical system (8), an optical axis switching member (SW), a control section (210, 210a, 210b, main control section 211, 211a, 211b), and an intraocular parameter calculation section (data processing section 223). The OCT optical system divides light (L0) from a light source (light source unit 101) into measurement light (LS) and reference light (LR), and projects the measurement light to a left eye (EL) disposed on a first measurement optical axis (measurement optical axis OL) or a right eye (ER) disposed on a second measurement optical axis (measurement optical axis OR) via the objective lens, and detects interference light (LC) of the return light of the measurement light from the left eye or the right eye and the reference light via a reference light path. The optical axis switching member switches the optical axis of the OCT optical system to substantially coincide with either one of the first measurement optical axis and the second measurement optical axis. The control section controls the optical axis switching member. The intraocular parameter calculation section calculates an intraocular parameter (for example, an axial length) of the left eye based on the detection result of the interference light obtained in a state where the optical axis of the OCT optical system is switched to substantially coincide with the first measurement optical axis, and calculates an intraocular parameter (for example, an axial length) of the right eye based on the detection result of the interference light obtained in a state where the optical axis of the OCT optical system is switched to substantially coincide with the second measurement optical axis.

[0400] According to this mode, using a single OCT optical system, OCT measurement can be performed on binocular eyes in an open-eye state. Thus, an ophthalmic apparatus that is low in cost and saves space and that can measure the characteristics of binocular eyes with high precision can be provided.

[0401] In the second aspect of the embodiment, in the first aspect, before the OCT measurement using the measurement light is performed on one of the left and right eyes under examination, the control section controls the OCT optical system to adjust the optical path length of the reference light path based on the axial length and the refractive power of the other of the left and right eyes under examination.

[0402] According to this aspect, it is possible to set the measurement environment estimated from the measurement environment of the other eye under examination before the OCT measurement is performed on one eye under examination, and thus it is possible to shorten the time required for the OCT measurement.

[0403] In the third aspect of the embodiment, in the first or second aspect, the optical axis switching member deflects the optical path of the measurement light. The ophthalmic apparatus of this aspect further includes a first fixation optical system (fixation projection system 4L) that projects a first fixation beam to the left eye under examination, a first optical path coupling member (dichroic mirror ML) that optically couples the optical path of the measurement light deflected by the optical axis switching member and the optical path of the first fixation beam, a second fixation optical system (fixation projection system 4R) that projects a second fixation beam to the right eye under examination, and a second optical path coupling member (dichroic mirror MR) that optically couples the optical path of the measurement light deflected by the optical axis switching member and the optical path of the second fixation beam.

[0404] According to this aspect, it is possible to perform the OCT measurement in the open-eye state while independently presenting fixation targets to the left and right eyes under examination using a simple structure.

[0405] In the fourth aspect of the embodiment, in the first or second aspect, the optical axis switching member deflects the optical path of the measurement light. The ophthalmic apparatus of this aspect further includes a fixation optical system (4) that projects a fixation beam to either of the left and right eyes under examination, an optical path coupling member (dichroic mirror 83) that optically couples the optical path of the fixation beam and the optical path of the measurement light and guides the fixation beam to the objective lens, a first reflection member (mirror ML1) that deflects the optical path of the measurement light deflected by the optical axis switching member toward the left eye under examination, and a second reflection member (mirror MR1) that deflects the optical path of the measurement light deflected by the optical axis switching member toward the right eye under examination.

[0406] According to this aspect, it is possible to perform the OCT measurement in the open-eye state while presenting the same fixation target to both eyes using a fixation projection system common to both eyes.

[0407] In a fifth aspect of the embodiments, in the first aspect or the second aspect, the optical axis switching member deflects the optical path of the measurement light. The ophthalmic apparatus of the present aspect further includes: a first optical path coupling member (dichroic mirror ML) that deflects the optical path of the measurement light deflected by the optical axis switching member toward the left eye under test while transmitting the first fixation light beam from the transmission direction to the left eye under test; and a second optical path coupling member (dichroic mirror MR) that deflects the optical path of the measurement light deflected by the optical axis switching member toward the right eye under test while transmitting the second fixation light beam from the transmission direction to the right eye under test.

[0408] According to this aspect, it is possible to perform OCT measurement with both eyes open while configuring a fixation projection system common to both eyes outside the apparatus and presenting the same fixation target to both eyes.

[0409] A sixth aspect of the embodiments includes, in the third aspect or the fifth aspect: a first adjustment section (convergence angle adjustment section, moving mechanism that rotates the dichroic mirrors ML, MR) that changes the orientations of the first measurement optical axis and the second measurement optical axis by changing the orientations of the optical path coupling surfaces of the first optical path coupling member and the second optical path coupling member.

[0410] According to this aspect, it is possible to perform OCT measurement with both eyes open while adjusting the convergence angle with a simple structure.

[0411] A seventh aspect of the embodiments includes, in the third aspect, the fifth aspect, or the sixth aspect: a second adjustment section (height adjustment section, moving mechanism that rotates the deflection surfaces of the optical axis switching member SW, the dichroic mirror ML, and the dichroic mirror MR) that adjusts the arrangement directions of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the optical axis switching member, the orientations of the optical path coupling surfaces of the first optical path coupling member, and the orientations of the optical path coupling surfaces of the second optical path coupling member.

[0412] According to this aspect, it is possible to align the arrangement directions of the first measurement optical axis and the second measurement optical axis with the arrangement directions of the left eye under test and the right eye under test with a simple structure in a case where the arrangement directions of the first measurement optical axis and the second measurement optical axis are not parallel to the arrangement directions of the left eye under test and the right eye under test.

[0413] An eighth aspect of the embodiments includes, in the fourth aspect: a first adjustment section (convergence angle adjustment section, moving mechanism that rotates the mirrors ML1, MR1) that changes the orientations of the first measurement optical axis and the second measurement optical axis by changing the orientations of the reflection surfaces of the first reflection member and the second reflection member.

[0414] According to this aspect, it is possible to perform OCT measurement with both eyes open while adjusting the convergence angle with a simple structure.

[0415] The ninth aspect of the embodiment includes, in the fourth aspect or the eighth aspect, a second adjustment section (height adjustment section, moving mechanism that rotates the deflection surface of the optical axis switching member SW, the deflection surface of the mirror ML1, and the deflection surface of the mirror MR1), which changes the arrangement direction of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the optical axis switching member, the orientation of the reflection surface of the first reflection member, and the orientation of the reflection surface of the second reflection member.

[0416] According to this aspect, in a case where the arrangement direction of the first measurement optical axis and the second measurement optical axis is not parallel to the arrangement direction of the left eye and the right eye, the arrangement direction of the first measurement optical axis and the second measurement optical axis can be made to coincide with the arrangement direction of the left eye and the right eye with a simple structure.

[0417] The tenth aspect of the embodiment includes, in any one of the third aspect to the ninth aspect, a third adjustment section (interpupillary distance adjustment section, moving mechanism 310), which changes the distance between the first measurement optical axis and the second measurement optical axis by moving the optical axis switching member along the first measurement optical axis or the second measurement optical axis.

[0418] According to this aspect, the first measurement optical axis and the second measurement optical axis can be made to match the interpupillary distance of the subject with a simple structure.

[0419] The eleventh aspect of the embodiment includes, in any one of the first aspect to the tenth aspect, two or more photographing sections (anterior eye portion cameras 15LA, 15LB, 15RA, 15RB) that photograph the anterior eye portion of the left eye and the anterior eye portion of the right eye from different directions from each other, and a moving mechanism (200) that moves the OCT optical system three-dimensionally. The control section changes the relative positions of the OCT optical system with respect to the left eye and the right eye while changing the orientation of the first measurement optical axis and the orientation of the second measurement optical axis and the distance between the first measurement optical axis and the second measurement optical axis, based on two or more images obtained by the two or more photographing sections, so that the first measurement optical axis coincides with the visual axis of the left eye and the second measurement optical axis coincides with the visual axis of the right eye.

[0420] According to this aspect, the position alignment of the ophthalmic apparatus that can perform OCT measurement of both eyes in a state where both eyes are open in a large dynamic range can be performed with a simple structure.

[0421] In the twelfth aspect of the embodiment, in the eleventh aspect, the two or more photographing sections include a first photographing section (anterior eye portion camera 15LA) that photographs the anterior eye portion of the left eye, a second photographing section (anterior eye portion camera 15LR) that photographs the anterior eye portion of the left eye and the anterior eye portion of the right eye, and a third photographing section (anterior eye portion camera 15RA) that photographs the anterior eye portion of the right eye.

[0422] According to this manner, it is possible to reduce the number of front eye cameras and perform OCT measurement of both eyes in a state where both eyes are open at a lower cost.

[0423] The thirteenth aspect of the embodiment includes the refractive power measurement optical system (the retinoscopy projection system 6 and the retinoscopy light receiving system 7) and the eye refractive power calculation section (221) in any one of the first aspect to the twelfth aspect. The refractive power measurement optical system projects the first measurement pattern light along the first measurement optical axis to the left eye under examination via the objective lens, projects the second measurement pattern light along the second measurement optical axis to the right eye under examination, and receives the return light of the first measurement pattern light from the left eye under examination and the return light of the second measurement pattern light from the right eye under examination. The eye refractive power calculation section calculates the refractive power of the left eye under examination based on the light receiving result of the return light of the first measurement pattern light, and calculates the refractive power of the right eye under examination based on the light receiving result of the return light of the second measurement pattern light.

[0424] According to this manner, it is possible to perform refractive power measurement of both eyes in a state where both eyes are open.

[0425] In the fourteenth aspect of the embodiment, in the thirteenth aspect, the refractive power measurement optical system projects the first measurement pattern light and the second measurement pattern light so that a position corresponding to an intermediate degree number of the refractive power of the left eye under examination and the refractive power of the right eye under examination becomes a focal position.

[0426] According to this manner, it is possible to perform refractive power measurement of both eyes at the same time even in a case where the refractive powers of both eyes are different.

[0427] <Others>

[0428] The above-described embodiment is merely one example for implementing the present application. A person who implements the present application can implement any modification, omission, addition, and the like within the scope of the gist of the present application.

[0429] In addition, in the above-described embodiment, the case where the ophthalmic apparatus performs OCT on the fundus is described, but the structure of the ophthalmic apparatus of the embodiment is not limited thereto. For example, the present application can be applied to an ophthalmic apparatus that performs OCT on the fundus and the front eye portion.

[0430] In addition, in the above-described embodiment, the optical axis switching member SW makes the optical axis turn back in the XZ plane, but the structure of the embodiment is not limited thereto. For example, the optical axis switching member SW can also be configured to make the optical axis turn back in the Y direction (the upward direction or the downward direction with respect to the examinee). In this case, the interpupillary distance adjustment section can adjust the interpupillary distance by moving or rotating the dichroic mirrors ML and MR.

Claims

1. An ophthalmic apparatus comprising: an objective lens; an OCT optical system that splits light from a light source into measurement light and reference light, and projects the measurement light to a left eye under examination arranged on a first measurement optical axis or a right eye under examination arranged on a second measurement optical axis via the objective lens, detects interference light of the measurement light from the left eye under examination or the right eye under examination and the reference light via a reference light path; an optical axis switching member that switches an optical axis of the OCT optical system to substantially coincide with either one of the first measurement optical axis and the second measurement optical axis; a control section that controls the optical axis switching member; and an intraocular parameter calculation section that calculates an intraocular parameter of the left eye under examination based on a detection result of the interference light obtained in a state where the optical axis of the OCT optical system is switched to substantially coincide with the first measurement optical axis, and calculates an intraocular parameter of the right eye under examination based on a detection result of the interference light obtained in a state where the optical axis of the OCT optical system is switched to substantially coincide with the second measurement optical axis, the control section controls the OCT optical system so as to adjust a light path length of the reference light path based on an axial length and a refractive power of the other of the left eye under examination and the right eye under examination before performing OCT measurement using the measurement light on one of the left eye under examination and the right eye under examination.

2. The ophthalmic apparatus according to claim 1, wherein the optical axis switching member deflects a light path of the measurement light, the ophthalmic apparatus comprises: a first fixation optical system that projects a first fixation beam to the left eye under examination; a first light path coupling member that optically couples the light path of the measurement light deflected by the optical axis switching member and a light path of the first fixation beam; a second fixation optical system that projects a second fixation beam to the right eye under examination; and a second light path coupling member that optically couples the light path of the measurement light deflected by the optical axis switching member and a light path of the second fixation beam.

3. The ophthalmic apparatus according to claim 1, wherein the optical axis switching member deflects a light path of the measurement light, the ophthalmic apparatus comprises: a fixation optical system that projects a fixation beam to either one of the left eye under examination and the right eye under examination; a light path coupling member that optically couples a light path of the fixation beam and a light path of the measurement light, and guides the fixation beam to the objective lens; a first reflection member that deflects the light path of the measurement light deflected by the optical axis switching member toward the left eye under examination; and a second reflection member that deflects the light path of the measurement light deflected by the optical axis switching member toward the right eye under examination.

4. The ophthalmic apparatus according to claim 1, wherein the optical axis switching member deflects a light path of the measurement light, the ophthalmic apparatus comprises: a first light path coupling member that deflects the light path of the measurement light deflected by the optical axis switching member toward the left eye under examination, while passing a first fixation beam from a passing direction to guide to the left eye under examination; and ​ ​ The second optical path coupling member deflects the optical path of the measurement light deflected by the optical axis switching member toward the right eye under examination while allowing the second fixation light beam from the transmission direction to be transmitted to the right eye under examination.

5. The ophthalmic apparatus according to claim 2, wherein the ophthalmic apparatus includes: a first adjustment section that changes the orientations of the first measurement optical axis and the second measurement optical axis by changing the orientations of the optical path coupling surfaces of the first optical path coupling member and the second optical path coupling member.

6. The ophthalmic apparatus according to claim 4, wherein the ophthalmic apparatus includes: a first adjustment section that changes the orientations of the first measurement optical axis and the second measurement optical axis by changing the orientations of the optical path coupling surfaces of the first optical path coupling member and the second optical path coupling member.

7. The ophthalmic apparatus according to claim 2, wherein the ophthalmic apparatus includes: a second adjustment section that adjusts the arrangement directions of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the optical axis switching member, the orientations of the optical path coupling surfaces of the first optical path coupling member, and the orientations of the optical path coupling surfaces of the second optical path coupling member.

8. The ophthalmic apparatus according to claim 4, wherein the ophthalmic apparatus includes: a second adjustment section that adjusts the arrangement directions of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the optical axis switching member, the orientations of the optical path coupling surfaces of the first optical path coupling member, and the orientations of the optical path coupling surfaces of the second optical path coupling member.

9. The ophthalmic apparatus according to claim 3, wherein the ophthalmic apparatus includes: a first adjustment section that changes the orientations of the first measurement optical axis and the second measurement optical axis by changing the orientations of the reflecting surfaces of the first reflecting member and the second reflecting member.

10. The ophthalmic apparatus according to claim 3, wherein the ophthalmic apparatus includes: a second adjustment section that changes the arrangement directions of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the optical axis switching member, the orientations of the reflecting surfaces of the first reflecting member, and the orientations of the reflecting surfaces of the second reflecting member.

11. The ophthalmic apparatus according to claim 2, wherein the ophthalmic apparatus includes: a third adjustment section that changes the distance between the first measurement optical axis and the second measurement optical axis by moving the optical axis switching member along the first measurement optical axis or the second measurement optical axis.

12. The ophthalmic apparatus according to claim 3, wherein the ophthalmic apparatus includes: a third adjustment section that changes the distance between the first measurement optical axis and the second measurement optical axis by moving the optical axis switching member along the first measurement optical axis or the second measurement optical axis.

13. The ophthalmic apparatus according to claim 4, wherein the ophthalmic apparatus includes: The third adjustment section changes the distance between the first measurement optical axis and the second measurement optical axis by moving the optical axis switching member along the first measurement optical axis or the second measurement optical axis.

14. The ophthalmic apparatus according to claim 1, wherein the ophthalmic apparatus includes: two or more photographing sections that photograph the anterior eye portions of the left and right eyes to be examined from different directions from each other; and a moving mechanism that moves the OCT optical system three-dimensionally, the control section changes the relative positions of the OCT optical system with respect to the left and right eyes to be examined while changing the orientations of the first and second measurement optical axes and the distance between the first and second measurement optical axes so that the first measurement optical axis coincides with the visual axis of the left eye to be examined and the second measurement optical axis coincides with the visual axis of the right eye to be examined, on the basis of the two or more images obtained by the two or more photographing sections.

15. The ophthalmic apparatus according to claim 14, wherein the two or more photographing sections include: a first photographing section that photographs the anterior eye portion of the left eye to be examined; a second photographing section that photographs the anterior eye portions of the left and right eyes to be examined; and a third photographing section that photographs the anterior eye portion of the right eye to be examined.

16. The ophthalmic apparatus according to claim 1, wherein the ophthalmic apparatus includes: a refractive power measurement optical system that projects a first measurement pattern light beam along the first measurement optical axis to the left eye to be examined and a second measurement pattern light beam along the second measurement optical axis to the right eye to be examined via the objective lens, and receives return light of the first measurement pattern light beam from the left eye to be examined and return light of the second measurement pattern light beam from the right eye to be examined; and an eye refractive power calculation section that calculates the refractive power of the left eye to be examined on the basis of a light-receiving result of the return light of the first measurement pattern light beam, and calculates the refractive power of the right eye to be examined on the basis of a light-receiving result of the return light of the second measurement pattern light beam.

17. The ophthalmic apparatus according to claim 16, wherein the refractive power measurement optical system projects the first and second measurement pattern light beams so that a position corresponding to an intermediate degree number of the refractive power of the left eye to be examined and the refractive power of the right eye to be examined becomes a focal position.

Images