Ophthalmic device

Abstract

The present application provides a new technology which is low cost, saves space and can measure the characteristics of both eyes with high precision. An ophthalmic apparatus includes an objective lens, an OCT optical system, an optical axis adjustment section, a control section, and an intraocular parameter calculation section. First and second measurement optical axes, which are arranged separately from each other, pass through the objective lens. The OCT optical system performs OCT on a left eye to be examined arranged on the first measurement optical axis or a right eye to be examined arranged on the second measurement optical axis. The optical axis adjustment section adjusts the optical axis of the OCT optical system. The control section controls the optical axis adjustment section so as to substantially coincide with either of the first and second measurement optical axes. The intraocular parameter calculation section calculates an intraocular parameter of the left or right eye to be examined based on a detection result of interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the first or 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 the 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 through which a first measurement optical axis and a second measurement optical axis arranged apart from each other pass; 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 the first measurement optical axis or a right eye to be examined arranged on the 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 the reference light via a reference light path; an optical axis adjustment section that adjusts an optical axis of the OCT optical system; a control section that controls the optical axis adjustment section so as to be approximately coincident with any one of the first measurement optical axis and the second measurement optical axis; and an intraocular parameter calculation section that calculates an intraocular parameter of the left eye to be examined on the basis of a detection result of the interference light obtained in a state where the optical axis of the OCT optical system is adjusted to be approximately coincident with the first measurement optical axis, and calculates an intraocular parameter of the right eye to be examined on the basis of a detection result of the interference light obtained in a state where the optical axis of the OCT optical system is adjusted to be approximately coincident with the second measurement optical axis.

[0014] According to the present application, it is possible to provide a new technique capable of measuring the 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 4is a schematic diagram for explaining an optical system of an ophthalmic apparatus of the first embodiment.

[0019] Figure 5 is a schematic diagram for explaining an optical system of an ophthalmic apparatus of the first embodiment.

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

[0021] Figure 7 is a schematic diagram showing a structure example of an optical system of an ophthalmic apparatus of the first embodiment.

[0022] Figure 8 is a schematic diagram showing a structure example of an optical system of an ophthalmic apparatus of the first embodiment.

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

[0024] Figure 10 is a schematic diagram for explaining an optical system of an ophthalmic apparatus of the first embodiment.

[0025] Figure 11A is a schematic diagram for explaining an optical system of an ophthalmic apparatus of the first embodiment.

[0026] Figure 11B is a schematic diagram for explaining an optical system of an ophthalmic apparatus of the first embodiment.

[0027] Figure 11C is a schematic diagram for explaining an optical system of an ophthalmic apparatus of the first embodiment.

[0028] Figure 12 is a schematic diagram showing a structure example of a processing system of an ophthalmic apparatus of the first embodiment.

[0029] Figure 13 is a schematic diagram showing a structure example of a processing system of an ophthalmic apparatus of the first embodiment.

[0030] Figure 14 is a schematic diagram showing a flow of an operation example of an ophthalmic apparatus of the first embodiment.

[0031] Figure 15 is a schematic diagram showing a flow of an operation example of an ophthalmic apparatus of the first embodiment.

[0032] Figure 16 is a schematic diagram showing a structure example of an optical system of an ophthalmic apparatus of the second embodiment.

[0033] Figure 17is a schematic diagram showing a configuration example of an optical system of an ophthalmic apparatus of a second embodiment.

[0034] Figure 18 is a schematic diagram for explaining an optical system of an ophthalmic apparatus of a second embodiment.

[0035] Figure 19 is a schematic diagram for explaining an optical system of an ophthalmic apparatus of a second embodiment.

[0036] Figure 20 is a schematic diagram showing a configuration example of an optical system of an ophthalmic apparatus of a second embodiment.

[0037] Figure 21 is a schematic diagram showing a configuration example of a processing system of an ophthalmic apparatus of a second embodiment.

[0038] Figure 22 is a schematic diagram showing a configuration example of an optical system of an ophthalmic apparatus of a third embodiment.

[0039] Figure 23 is a schematic diagram showing a configuration example of a processing system of an ophthalmic apparatus of a third embodiment.

[0040] (Explanation of Reference Numerals)

[0041] 1, 1a, 1b: ophthalmic apparatus

[0042] 2: XY alignment system

[0043] 3: corneal measurement system

[0044] 4, 4L, 4R: fixation projection system

[0045] 5: anterior eye portion observation system

[0046] 6L, 6R: reflection measurement projection system

[0047] 7: reflection measurement light receiving system

[0048] 8: OCT optical system

[0049] 9, 9a, 9b: processing section

[0050] 40, 40L, 40R: fixation unit

[0051] 41, 41L, 41R: liquid crystal panel

[0052] 42, 43, 44, 42L, 43L, 44L, 42R, 43R, 44R: relay lens

[0053] 51: objective lens

[0054] 210, 210a, 210b: control section

[0055] 211, 211a, 211b: main control section

[0056] 300, 300a: measurement optical system

[0057] 400: fixation target section

[0058] CLr, CRr: cornea

[0059] EL: left eye to be examined

[0060] ELf, ERf: fundus

[0061] ER: right eye to be examined

[0062] M1, M2: deflection surface

[0063] ML, MR: dichroic mirror

[0064] ML1, MR1: mirror

[0065] OL, OR: measurement optical axis

[0066] PR: prism DETAILED DESCRIPTION

[0067] Examples of embodiments of an 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.

[0068] The ophthalmic apparatus of the embodiments can perform predetermined examinations, measurements on both eyes 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, and calculate an intraocular parameter of each of both eyes. By sharing the objective lens among the OCT measurements of both eyes, miniaturization and cost reduction of the apparatus can be achieved.

[0069] 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.

[0070] Objective sensory measurement is a measurement method that primarily uses physical methods to obtain information about the examined eye without referring to the subject's responses. Objective sensory measurement includes measurements to obtain characteristics of the examined eye and imaging of the examined eye. Other objective sensory measurements include intraocular pressure measurement, fundus photography, etc. In several embodiments, the ophthalmic device, as an objective sensory measurement, can perform refractive power measurement (reflectance measurement) and OCT measurement. In several embodiments, the ophthalmic device, as an objective sensory measurement, can perform refractive power measurement, corneal shape measurement, and OCT measurement.

[0071] The following describes the ophthalmic device according to the embodiment performing OCT measurements on the anterior eye and fundus. Hereinafter, the method using a spectral domain type OCT will be described in particular detail in the embodiment. However, the structure of the embodiment can also be applied to ophthalmic devices using other types of OCT (e.g., swept-source type, time-domain type).

[0072] 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.

[0073] 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.

[0074] 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.

[0075] [First Implementation Method]

[0076] <Structure of an Optical System>

[0077] 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.

[0078] The ophthalmic apparatus 1 of the first embodiment includes a measurement optical system 300, dichroic mirrors ML, MR, a prism PR, a fixation projection system 4L, and a fixation projection system 4R. It can also be that the measurement optical system 300 includes the dichroic mirrors ML, MR, the prism PR, the fixation projection system 4L, and the fixation projection system 4R.

[0079] (Measurement optical system 300)

[0080] The measurement optical system 300 includes an objective lens not shown and an optical system for measurement of a left eye EL as a subject left eye and a right eye ER as a subject right eye via the objective lens. The measurement optical axes OL, OR disposed apart from each other pass through the objective lens at the time of measurement using the optical system. The left eye EL is disposed on the measurement optical axis OL. The right eye ER is disposed on the measurement optical axis OR.

[0081] As shown in FIG. 1, 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 reflection measurement projection system 6L, 6R, a reflection measurement light receiving system 7, and an OCT optical system 8. Figure 2

[0082] The corneal measurement system 3 is an optical system for measurement of information indicating the shape of a cornea CLr of the left eye EL and information indicating the shape of a cornea CRr of the right eye ER. The corneal measurement system 3 is configured to project light for corneal shape measurement to a subject eye to be measured without passing through the objective lens described above, and receive return light of the light for corneal shape measurement.

[0083] The anterior eye portion observation system 5 is configured to illuminate the anterior eye portion of the left eye EL and the anterior eye portion of the right eye ER, and receive return light of the illumination light via the objective lens.

[0084] The reflection measurement projection system 6L projects light for reflection measurement to the left eye EL via the objective lens, and projects a measurement pattern (a ring pattern) centered on the measurement optical axis OL to the fundus ELf. The reflection measurement projection system 6R projects light for reflection measurement to the right eye ER via the objective lens, and projects a measurement pattern (a ring pattern) centered on the measurement optical axis OR to the fundus ERf.

[0085] The reflection measurement light receiving system 7 is configured to receive return light from the fundus ELf and return light from the fundus ERf via the objective lens.

[0086] ​The OCT optical system 8 splits the light from the OCT light source into measurement light and reference light, projects the measurement light via the objective lens to the left eye EL disposed on the measurement optical axis OL or the right eye ER disposed on the measurement optical axis OR, and detects interference light of the return light of the measurement light from the left eye EL or the right eye ER and the reference light via the reference light path.

[0087] (dichroic mirrors ML, MR)

[0088] The dichroic mirrors ML, MR 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).

[0089] The dichroic mirror ML is disposed on the measurement optical axis OL. The dichroic mirror ML transmits the fixation light beams from the fixation projection system 4L to be guided to the left eye EL. In addition, the dichroic mirror ML reflects the light from the measurement optical system 300 toward the left eye EL while reflecting the return light from the left eye EL toward 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 beams from the fixation projection system 4R to be guided to the right eye ER. In addition, the dichroic mirror MR reflects the light from the measurement optical system 300 toward the right eye ER while reflecting the return light from the right eye ER toward the measurement optical system 300.

[0090] (prism PR)

[0091] The prism PR is disposed between the measurement optical system 300 and the dichroic mirrors ML, MR. The prism PR includes deflection surfaces M1, M2. The prism PR deflects the optical axis from the dichroic mirror ML toward the measurement optical system 300 by the deflection surface M1 and deflects the optical axis from the dichroic mirror MR toward the measurement optical system 300 by the deflection surface M2.

[0092] (fixation projection systems 4L, 4R)

[0093] The fixation projection system 4L presents a fixation target to the left eye EL by projecting the fixation light beams to the fundus EIf of the left eye EL. The fixation projection system 4L includes a fixation unit 40L, relay lenses 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 the 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 41L, the fixation position of the left eye EL can be changed. In addition, the fixation unit 40L can be moved in the optical axis direction under the control from the control section described later.

[0094] The light from the liquid crystal panel 41L passes through the relay lenses 42L, 43L, 44L, transmits through the dichroic mirror ML, and is projected to the fundus ELf. In several embodiments, the fixation unit 40L is capable of moving independently of the relay lenses 43L, 44L in the optical axis direction.

[0095] Likewise, the fixation projection system 4R presents the fixation target to the right examination eye ER by projecting the fixation light beam to the fundus ERf of the right examination eye ER. The fixation projection system 4R includes the fixation unit 40R, the relay lenses 43R, 44R. The fixation unit 40R includes the liquid crystal panel 41R, the relay lens 42R. The liquid crystal panel 41R displays a pattern representing the 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 examination eye ER can be changed. In addition, the fixation unit 40R is capable of moving in the optical axis direction under the control from the control section described later.

[0096] The light from the liquid crystal panel 41R passes through the relay lenses 42R, 43R, 44R, transmits through the dichroic mirror MR, and is projected to the fundus ERf. In several embodiments, the fixation unit 40R is capable of moving independently of the relay lenses 43R, 44R in the optical axis direction.

[0097] The fixation unit 40L is capable of moving independently of the fixation unit 40R in the optical axis direction. That is, the fixation units 40L, 40R are each capable of moving independently in the optical axis direction according to the refractive power of each of the left examination eye EL and the right examination eye ER.

[0098] The fixation position of each of the left examination eye EL and the right examination 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, and a position for acquiring an image centered on the fundus center between the macula and the optic papilla, and the like. The display position of the pattern representing the fixation target can be arbitrarily changed.

[0099] The ophthalmic apparatus 1 can perform corneal measurement, reflex 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. Further, the ophthalmic apparatus 1 can perform corneal measurement, reflex 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 some embodiments, the ophthalmic apparatus 1 performs at least one of corneal measurement and reflex measurement on 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 the left eye EL and the right eye ER by the fixation projection systems 4L and 4R, respectively. In some embodiments, the ophthalmic apparatus 1 performs at least one of corneal measurement, reflex 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 the left eye EL and the right eye ER by the fixation projection systems 4L and 4R, respectively.

[0100] Such an ophthalmic apparatus 1 includes an optical axis adjustment 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 adjustment section controls an optical member in a path of the measurement light under control from a control section described later to deflect the measurement light or to move the optical axis of the OCT optical system 8, thereby being able to adjust the optical axis of the OCT optical system 8. The control section controls the optical axis adjustment section so that the optical axis of the OCT optical system 8 substantially coincides with either of the measurement optical axes OL and OR.

[0101] Further, the ophthalmic apparatus 1 includes an interpupillary distance adjustment section that changes a distance in the X direction between the measurement optical axes OL and OR in accordance with an interpupillary distance of the subject.

[0102] Figure 3 An explanatory diagram showing an operation example of the interpupillary distance adjustment section in the ophthalmic apparatus 1 of the first embodiment is shown. In Figure 3 The same parts as Figure 1 the same reference numerals are attached to the same parts, and the explanation is appropriately omitted.

[0103] The interpupillary distance adjustment section changes the distance in the X direction between the measurement optical axes OL and OR by moving the prism PR having the deflection surfaces M1 and M2 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 prism PR is in an initial position, the distance in the X direction between the measurement optical axes OL and OR is set to the interpupillary distance PD. Here, while constantly maintaining the distance in the X direction of the left and right measurement optical axes by the objective lens of the measurement optical system 300, the prism PR is moved from the initial position along the measurement optical axis OL or the measurement optical axis OR. Thus, as shown in Figure 3As shown, the position of the optical axis deflected by the dichroic mirror ML, MR is changed, 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.

[0104] In several embodiments, the prism PR is moved in the X direction by the interpupillary distance adjustment section, and the interpupillary distance is changed. Figure 3 The interpupillary distance is changed by moving the prism PR in the X direction as shown.

[0105] In several embodiments, the optical axis adjustment section moves the prism PR 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.

[0106] In several embodiments, the prism PR is moved by a movement mechanism not shown under the control of a control section not shown. 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 prism PR is manually moved 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.

[0107] In addition, the ophthalmic apparatus 1 includes a convergence angle adjustment section that changes at least one of the orientation of the measurement optical axis OL incident on the left eye EL through the pupil and the orientation of the measurement optical axis OR incident on the right eye ER through the pupil in accordance with the convergence angle of the examined eye.

[0108] Figure 4 A drawing illustrating an example of the operation of the convergence angle adjustment section in the ophthalmic apparatus 1 of the first embodiment is shown. In the drawing, the same parts as those in Figure 4 the same parts as those in Figure 1 the same parts as those in

[0109] 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. In addition, 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.

[0110] 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.

[0111] For example, when the deflection surface of the dichroic mirror ML is oriented in the first direction and the deflection surface of the dichroic mirror MR is oriented in the second direction, the orientation of each of the measuring optical axes OL and OR is approximately parallel to the optical axis direction of the measuring optical system 300. Here, the orientation of the deflection surface of each of the dichroic mirrors ML and MR is changed to the inward side. Thus, as... Figure 4 As shown, the measuring optical axis OL, deflected by the dichroic mirror ML, becomes the measuring optical axis OL′, and the measuring optical axis OR becomes the measuring optical axis OR′, thus changing the convergence angle.

[0112] In several embodiments, the dichroic mirrors ML and MR are rotated by a moving mechanism (rotating mechanism) (not shown) under the control of a control unit described later. In this case, the convergence angle adjustment unit is functioned by the moving mechanism (and control unit) (not shown). In several embodiments, the dichroic mirrors ML and MR are rotated manually by the moving mechanism (rotating mechanism) (not shown). In this case, the convergence angle adjustment unit is functioned by the moving mechanism (not shown).

[0113] In several embodiments, the prism PR may also include a reflector having a deflection surface M1 and a reflector having a deflection surface M2.

[0114] Figure 5 Other structural examples of the ophthalmic device 1 according to the first embodiment are shown. Figure 5 In the middle, to and Figure 1 Identical parts are labeled with the same reference numerals, and descriptions are omitted where appropriate.

[0115] like Figure 5 As shown, the prism PR includes a mirror RML with a deflection surface M1 and a mirror RMR with a deflection surface M2. Figure 1 Similarly, the optical axis of the optical system 300 is measured to deflect towards the dichroic mirror ML at the deflection surface M1 and towards the dichroic mirror MR at the deflection surface M2.

[0116] The mirrors RML and RMR can also move independently. For example, the mirrors RML and RMR can move independently along the measuring optical axis. Thus, with the mirrors RML and RMR at different positions in the Z-direction, the measuring optical axes OL and OR are deflected by the dichroic mirrors ML and MR. The result is similar to... Figure 3 Compared to the case where the prism PR is moved as shown, the interpupillary distance can be adjusted with high precision by changing the intermediate position of the measuring optical axes OL and OR.

[0117] For example, the orientation of each of the mirrors RML, RMR is independently changed. Thereby, in a state where the mirrors RML, RMR deflect the measurement optical axes OL, OR at different angles from each other with the Z direction as a reference, the measurement optical axes OL, OR are deflected by the dichroic mirrors ML, MR, and thus it is not necessary to provide a mirror for changing the direction of the measurement optical axes OL, OR as in the related art. Figure 4 The converging angle can be adjusted by changing the orientations of the dichroic mirrors ML, MR as shown.

[0118] In several embodiments, the mirrors RML, RMR are rotated by a movement mechanism (rotation mechanism) not shown under the control from a control section to be described later.

[0119] In several embodiments, the ophthalmic apparatus 1 includes a height adjustment section that changes the orientation (deflection direction) of the deflection surface Ml of the prism PR or the mirror RML, the orientation of the deflection surface M2 of the prism PR or the mirror RMR, 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 and right examination eyes EL, ER is not the horizontal direction (X direction), the arrangement direction of the measurement optical axes OL, OR can be made to coincide with the arrangement direction of the left and right examination eyes EL, ER by the height adjustment section. The movement mechanism that rotates the deflection surface Ml of the prism PR or the mirror RML, the deflection surface M2 of the prism PR or the mirror RMR, 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.

[0120] In addition, the ophthalmic apparatus 1 includes an arithmetic processing section that calculates the intraocular parameters of the examination eyes 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 examination eye EL based on the detection results of the interference light obtained in a state where the optical axis of the OCT optical system 8 is adjusted to substantially coincide with the measurement optical axis OL, and calculates the intraocular parameters of the right examination eye ER based on the detection results of the interference light obtained in a state where the optical axis of the OCT optical system 8 is adjusted to substantially coincide with the measurement optical axis OR.

[0121] 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 prism PR or the mirror RML is an example of the "first deflection member" of the embodiment. The prism PR or the mirror RMR is an example of the "second deflection member" of the embodiment. The moving mechanism that rotates the dichroic mirrors ML and 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 M1 of the prism PR or the mirror RML, the deflection surface M2 of the prism PR or the mirror RMR, 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. The deflection surface M1 is an example of the "first deflection surface as the first deflection member" of the embodiment. The deflection surface M2 is an example of the "second deflection surface as the second deflection member" of the embodiment.

[0122] 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 sometimes referred to simply as the eye under examination.

[0123] Figure 6 to Figure 8 A configuration example of the measurement optical system 300 of the first embodiment will be described. Figure 6 is a configuration example of the measurement optical system 300 as viewed from the side (X direction) schematically. Figure 7 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 retro-reflective measurement projection system 6L, 6R of the measurement optical system 300. Figure 8 is a configuration example of the retro-reflective measurement projection system 6L, 6R of the measurement optical system 300. Figure 6 is a configuration example of the OCT unit 100 of the measurement optical system 300. Further, in Figure 6 , the front eye portion cameras 15LA, 15RA are illustrated as being arranged in the X direction, and the front eye portion cameras 15LB, 15RB are illustrated as being arranged in the X direction for the sake of explanation, but the configuration of the embodiment is not limited thereto. In addition, in Figure 6 , the illustration of the dichroic mirrors ML, MR illustrated in Figure 1 is omitted. In Figure 6 and Figure 8 , the same reference numerals are attached to the same parts as Figure 1 , and the explanation is appropriately omitted. In Figure 7 , the same reference numerals are attached to the same parts as Figure 6 , and the explanation is appropriately omitted.

[0124] The measurement optical system 300 includes optical systems for observing the left and right examined eyes EL and ER, optical systems for examining the left and right examined eyes EL and ER, and a dichroic mirror that wavelength-separates the optical paths of these optical systems. As the optical system for observing the left and right examined eyes EL and ER, the anterior eye portion observation system 5 is provided. As the optical system for examining the left and right examined eyes EL and 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 systems 6L and 6R and the reflection measurement light receiving system 7. Figure 2

[0125] In the first embodiment, the corneal measurement system 3, the reflection measurement light receiving system 7, and the OCT optical system 8 are shared in the examination of the left examined eye EL and the examination of the right examined eye ER, the reflection measurement projection system 6L is used for the examination of the left examined eye EL (refractive power measurement), and the reflection measurement projection system 6R is used for the examination of the right examined eye ER (refractive power measurement).

[0126] 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 systems 6L and 6R, the reflection measurement light receiving system 7, the OCT optical system 8, and the anterior eye portion cameras 15LA, 15RA, 15LB, and 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 systems 6L and 6R and 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 and 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.

[0127] (anterior eye portion observation system 5)

[0128] The anterior eye portion observation system 5 dynamically photographs the anterior eye portions of the left and right examined eyes EL and ER. 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 the anterior eye portions of the left and right examined eyes EL and ER with illumination light (for example, infrared light).

[0129] ​In several embodiments, the front eye portion illuminating light source 50 includes a pair of illuminating light sources for illuminating the front eye portions of the left and right examined eyes EL, ER from positions separated from the measurement optical axes 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 examined eye EL from a position separated from the measurement optical axis OL and a pair of illuminating light sources for illuminating the front eye portion of the right examined eye ER from a position 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 examined eye EL and one of the pair of illuminating light sources for illuminating the front eye portion of the right examined eye ER can also be shared.

[0130] As described above, the measurement optical axes OL, OR are configured to pass through the objective lens 51 (at the time of alignment completion). Light reflected by the front eye portions of the left and right examined eyes EL, ER passes through the objective lens 51, passes through the dichroic mirror 52, passes through the aperture (telecentric aperture) 53, passes through the half mirror 23, passes through the relay lenses 55 and 56, and passes through the dichroic mirror 76. The dichroic mirror 52 combines (separates) the optical paths of the reflection measurement optical system and the optical path of the front eye portion observation system 5. With regard to the dichroic mirror 52, an optical path combining surface that combines these optical paths is obliquely disposed with respect to the optical axes of the objective lens 51. 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, for example, in the horizontal direction, a front eye portion image of the left examined eye EL and a front eye portion image of the right examined eye ER based on the image signal. The front eye portion images of the left and right examined eyes EL, ER are, for example, infrared dynamic images.

[0131] (front eye portion cameras 15LA, 15RA, 15LB, 15RB)

[0132] The front eye portion cameras 15LA, 15LB image the front eye portion of the left examined eye 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, 15LB are used, for example, to perform optical system alignment with respect to the position of the left examined eye EL.

[0133] The number of front eye portion cameras that image the front eye portion of the left examined eye EL can be any number of two or more, but a configuration that enables the front eye portion to be substantially simultaneously imaged from two different directions is sufficient. In addition, one front eye portion camera can also be the imaging element 59 in the front eye portion observation system 5.

[0134] "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.

[0135] 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.

[0136] 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.

[0137] In several embodiments, instead of the anterior eye portion cameras 15LA, 15LB, a known Z alignment system of the light lever method is provided. In several embodiments, instead of the anterior eye portion cameras 15RA, 15RB, a known Z alignment system of the light lever method is provided.

[0138] (XY alignment system 2)

[0139] 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)) to the left and right subject eyes EL, ER. 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 to the left and right subject eyes EL, ER through the anterior eye portion observation system 5. The reflected light of the cornea CLr of the left subject eye EL is guided to the imaging element 59 through the anterior eye portion observation system 5. The reflected light of the cornea CRr of the right subject eye ER is guided to the imaging element 59 through the anterior eye portion observation system 5.

[0140] The front eye 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 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 section 9 causes the display section to display the front eye image including the XY bright spot image and the alignment mark for each of the left eye under examination EL and 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 section 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 section 9 controls the mechanism that moves the optical system and the mechanism that moves the Figure 1 The prism PR, the dichroic mirror ML, and the mechanism that moves the MR are shown so as to eliminate the displacement of the XY bright spot image with respect to the alignment mark.

[0141] (Corneal measurement system 3)

[0142] 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 and the shape of the cornea CRr of the right eye under examination ER (corneal shape information) to the corneas CLr, 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 measurement optical axis OL, OR 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 corneas CLr, CRr. Reflected light (corneal ring image) from the corneas CLr, CRr is detected by the imaging element 59 together with the front eye image of the left eye under examination EL and the front eye image of the right eye under examination ER. The processing section 9 performs a known operation based on the corneal ring image, thereby calculating a corneal shape parameter representing the shape of the cornea CLr and a corneal shape parameter representing the shape of the cornea CRr.

[0143] (Reflection measurement projection system 6L, 6R, reflection measurement light receiving system 7)

[0144] The reflectance measurement optical system includes reflectance measurement projection systems 6L and 6R for refractive power measurement and a reflectance measurement light receiving system 7. The reflectance measurement projection system 6L projects a refractive power measurement beam (e.g., a ring beam) (infrared light) onto the fundus ELf of the left eye (EL) being examined. The reflectance measurement projection system 6R projects a refractive power measurement beam (e.g., a ring beam) (infrared light) onto the fundus ERf of the right eye (ER) being examined. The reflectance measurement light receiving system 7 receives the reflected light from the left eye (EL) and the reflected light from the right eye (ER) being examined, both from the refractive power measurement beam.

[0145] like Figure 7 As shown, the reflectivity measurement projection system 6L is positioned in the optical path branched by the aperture prism 65L, which is located in the optical path of the reflectivity measurement receiving system 7 on the measurement optical axis OL of the objective lens 51. The reflectivity measurement projection system 6R is positioned in the optical path branched by the aperture prism 65R, which is located in the optical path of the reflectivity measurement receiving system 7 on the measurement optical axis OR of the objective lens 51. The aperture formed in the aperture prism 65L is positioned at the pupil conjugate position of the left examined eye EL. The aperture formed in the aperture prism 65R is positioned at the pupil conjugate position of the right examined eye ER. In the optical system via the reflectivity measurement receiving system 7, the imaging surface of the imaging element 59 is positioned at the fundus conjugate position.

[0146] In several embodiments, at least one of the reflectance measuring light sources 61L and 61R is an SLD (Super Luminescent Diode) light source serving as a high-brightness light source. The reflectance measuring light sources 61L and 61R are movable along their respective optical axes. The reflectance measuring light source 61L is positioned at the fundus conjugate position of the left eye (EL) being examined. The reflectance measuring light source 61R is positioned at the fundus conjugate position of the right eye (ER) being examined. In several embodiments, the functions of the reflectance measuring light sources 61L and 61R are implemented by a single light source. In several embodiments, the functions of the relay lenses 62L and 62R are implemented by a single relay lens.

[0147] The light output from the reflective light source 61L passes through the relay lens 62L and is incident on the conical surface of the conical prism 63L. The light incident on the conical surface is deflected and exits from the bottom surface of the conical prism 63L. The light exiting from the bottom surface of the conical prism 63L passes through the light-transmitting portion of the annular aperture 64L. The light passing through the light-transmitting portion of the annular aperture 64L (the annular beam) is reflected by the reflective surface around the aperture formed in the aperture prism 65L, 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 EL being examined. The rotating prism 66 is used to average the light distribution of the annular beam relative to the blood vessels and disease sites in the fundus and to reduce speckle noise caused by the light source.

[0148] The returning light of the annular light beam projected to the fundus ELf of the left eye under examination EL passes through the objective lens 51, is reflected by the dichroic mirror 52 and the dichroic mirror 67. The returning light reflected by the dichroic mirror 67 passes through the rotating prism 66, passes through the hole portion of the hole prism 65L, passes through the relay lens 71, is reflected by the mirror 72, passes through the relay lens 73 and the focusing lens 74. The light passing through the focusing lens 74 is reflected by the mirror 75, is reflected by the dichroic mirror 76, and is imaged on the imaging surface of the imaging element 59 by the imaging lens 58.

[0149] Likewise, the light output from the retroillumination light source 61R passes through the relay lens 62R, and is incident on the conical surface of the conical prism 63R. The light incident on the conical surface is deflected and emitted from the bottom surface of the conical prism 63R. The light emitted from the bottom surface of the conical prism 63R passes through the light-transmitting portion of the annular diaphragm 64R formed in a ring shape. The light (annular light beam) passing through the light-transmitting portion of the annular diaphragm 64R is reflected by the reflecting surface formed around the hole portion of the hole prism 65R, 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 to the fundus Erf of the right eye under examination ER.

[0150] The returning light of the annular light beam projected to the fundus Erf of the right eye under examination ER passes through the objective lens 51, is reflected by the dichroic mirror 52 and the dichroic mirror 67. The returning light reflected by the dichroic mirror 67 passes through the rotating prism 66, passes through the hole portion of the hole prism 65R, passes through the relay lens 71, is reflected by the mirror 72, passes through the relay lens 73 and the focusing lens 74. The light passing through the focusing lens 74 is reflected by the mirror 75, is reflected by the dichroic mirror 76, and is imaged on the imaging surface of the imaging element 59 by the imaging lens 58.

[0151] The processing section 9 performs known operations based on the output from the imaging element 59, thereby calculating the refractive power value of each of the left eye under examination EL and the right eye under examination ER. Specifically, the processing section 9 specifies the annular pattern image from the left eye under examination EL 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. In addition, the processing section 9 specifies the annular pattern image from 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 right eye under examination ER. The refractive power value includes, for example, the spherical power, the astigmatic power, and the astigmatic axis angle or the equivalent spherical power.

[0152] In several embodiments, the measurement optical system 300 includes the fixation projection system 4L, 4R.

[0153] (OCT optical system 8)

[0154] The OCT optical system 8 is an optical system for performing OCT measurement. For example, based on the results of the reflection measurement performed before the OCT measurement, the position of the focusing lens 87 is adjusted so that the end face of the optical fiber fl is conjugate with the imaging site (fundus or anterior eye) and the optical system.

[0155] The OCT optical system 8 is disposed in an optical path that 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 to be substantially coincident with either of the measurement optical axes OL, OR.

[0156] The OCT optical system 8 includes an OCT unit 100. As shown in FIG. 1, the OCT unit 100 is provided with an optical system for performing OCT measurement (OCT imaging, OCT scanning) on either of the left eye EL and the right eye ER. The optical system has the same structure as that of a conventional spectral domain type OCT apparatus. 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 that has passed through the eye under examination (OCT measurement site) and the reference light that has passed through a reference light path, and detect a spectral component of the interference light. The detection result (detection signal) is sent to the processing section 9. Figure 8

[0157] 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 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. Alternatively, near infrared light having a wavelength band that is not visible to the human eye, for example, near infrared light having a central wavelength of 1040 nm to 1060 nm or so, can be used as the low coherent light L0.

[0158] Hereinafter, the light source unit 101 outputs low coherent light L0 having a wavelength component of 840 nm.

[0159] The light source unit 101 is configured to include a light output device such as a super luminescent diode (SLD), an LED, a semiconductor optical amplifier (SOA), or the like.

[0160] 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.

[0161] ​The reference light LR guided by the optical fiber 104 reaches an optical attenuator 105. The optical attenuator 105 automatically adjusts the light quantity of the reference light LR guided by the optical fiber 104 under the control of the processing section 9 using a known technique. The reference light LR whose light quantity is adjusted by the optical attenuator 105 is guided by the optical fiber 104 to a polarization controller (polarization adjusting device) 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 to this, and any known technique can be used. The reference light LR whose polarization state is adjusted by the polarization controller 106 reaches the optical fiber coupler 109.

[0162] The measurement light LS generated by the optical fiber coupler 103 is guided to a collimator lens 90 (f1) by an optical fiber f1, becomes a parallel light flux by the collimator lens 90, and reaches the dichroic mirror 67 via the optical path length changer 89, the light scanner 88, the focusing lens 87, the relay lenses 85 and 82, and the mirror 81. Figure 6

[0163] In several embodiments, the focusing lens 87 and the light scanner 88 are housed in one unit that can move in the optical axis direction. Thereby, the optical positional relationship of the focusing lens 87 and the light scanner 88 can be maintained while moving in the optical axis direction. This configuration enables the focusing lens 87 and the light scanner 88 to be moved integrally, and thereby the optical system can be adjusted while maintaining the conjugate relationship of the light scanner 88 and the eye to be examined. In addition, in this configuration, the pupil of the eye to be examined and the magnification relationship of the light scanner 88 can be easily changed by changing the focal distance f of the focusing lens 87.

[0164] In several embodiments, the focusing lens 87 and the light scanner 88 independently move in the optical axis direction within the unit. In several embodiments, the focusing lens 87 and the light scanner 88 independently or integrally move in the optical axis direction under the control from the processing section 9. For example, the pupil of the eye to be examined is disposed at the focal position of the objective lens 51, and the deflection surface of the light scanner 88 is disposed at the focal position of the focusing lens 87 (in the case where the light scanner 88 is disposed 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 disposed at the pupil conjugate position).

[0165] ​The optical path length changer 89 changes the optical path length of the measurement light LS. By changing the optical path length of the measurement light LS, the difference between the optical path length of the reference light LR and the optical path length of the measurement light LS can be changed. For example, the optical path length changer 89 includes a retroreflector that can move 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.

[0166] The optical scanner 88 deflects the measurement light LS one-dimensionally or two-dimensionally.

[0167] In several embodiments, the optical 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 a 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 a 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 an optical 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.

[0168] In several embodiments, the optical scanner 88 includes a MEMS scanner (MEMS mirror scanner) that deflects the measurement light LS two-dimensionally. 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.

[0169] In addition, the optical scanner 88 can include, in addition to the galvanometer mirror and the MEMS scanner, a polygon mirror, a rotating mirror, a Dove prism, a double-Dove prism, a rotating prism, and the like.

[0170] The measurement light LS that has reached the dichroic mirror 67 is transmitted through the dichroic mirror 67, is reflected by the dichroic mirror 52, and is refracted by the objective lens 51. The measurement light LS that has been refracted by the objective lens 51 is deflected by the prism PR 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 is scattered (including reflection) at various depth positions of the OCT measurement site. The backscattered light of the measurement light LS of the OCT measurement site is returned on the same path as the forward path, is guided to the optical fiber coupler 103, and reaches the optical fiber coupler 109 via the optical fiber 108.

[0171] 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 thus generated is guided by the optical fiber 110 and emitted from the emission end 111. Also, the interference light LC becomes a parallel light beam by the collimator lens 112, is spectrally split by the diffraction grating (light splitter) 113, is condensed by the variable focus 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 other types of light-splitting elements such as a reflection type diffraction grating or the like can also be used.

[0172] The CCD image sensor 115 is, for example, a line sensor, and has two or more light-receiving elements (detection elements) arranged therein. The CCD image sensor 115 detects each spectral component of the spectrally split interference light LC and converts it into an electric charge. The CCD image sensor 115 accumulates the electric charge and generates a detection signal, which is sent to the processing section 9.

[0173] 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 also be appropriately employed. In addition, instead of a CCD image sensor, other types of image sensors such as a CMOS (Complementary Metal Oxide Semiconductor) image sensor or the like can also be used.

[0174] In addition, in the present embodiment, the light path length of the measurement light LS is changed by the light path length changing section 89, but the structure of the present embodiment is not limited thereto. For example, the light path length of the measurement light LS can also be changed by changing the light path length of the reference light LR by a known method. Figure 6 In the structure shown, the difference between the light path length of the measurement light LS and the light path length of the reference light LR is changed by changing the light path length of the measurement light LS by the light path length changing section 89, but the structure of the present embodiment is not limited thereto. For example, the difference between the light path length of the measurement light LS and the light path length of the reference light LR can also be changed by changing the light path length of the reference light LR by a known method.

[0175] The processing section 9 calculates the refractive power value of the left eye EL under examination from the measurement result obtained using the retroreflected measurement optical system, and moves the retroreflected measurement light source 61L in the optical axis direction to a position at which the fundus ELf and the retroreflected measurement light source 61L are conjugated with the imaging element 59 based on the calculated refractive power value. In addition, the processing section 9 calculates the refractive power value of the right eye ER under examination from the measurement result obtained using the retroreflected measurement optical system, and moves the retroreflected measurement light source 61R in the optical axis direction to a position at which the fundus ERf and the retroreflected measurement light source 61R are conjugated with the imaging element 59 based on the calculated refractive power value. In several embodiments, the processing section 9 moves the focusing lens 74 to a position corresponding to a composite refractive value (for example, an intermediate power) calculated based on the refractive value of the left eye EL under examination and the refractive value of the right eye ER under examination.

[0176] In several embodiments, the processing portion 9 moves the focusing lens 87 and the light scanner 88 in the direction of their optical axes in conjunction with the movement of the focusing lens 74. In several embodiments, the processing portion 9 moves the liquid crystal panel 41L (fixation unit 40L) in the direction of its optical axis in conjunction with the movement of the light reflection measurement light source 61L and the focusing lens 74. In several embodiments, the processing portion 9 moves the liquid crystal panel 41R (fixation unit 40R) in the direction of its optical axis in conjunction with the movement of the light reflection measurement light source 61R and the focusing lens 74.

[0177] In the described embodiments, at least one function of the focusing lens 74, 87 can also be implemented by a liquid crystal lens or a liquid lens.

[0178] The structure of the optical system of the ophthalmic apparatus 1 of the embodiments is not limited to Figure 1 to Figure 8 the structure shown.

[0179] <Configuration example of anterior eye portion camera>

[0180] Figure 9 A configuration example of the anterior eye portion cameras 15LA, 15RA, 15LB, 15RB Figure 1 is schematically shown.

[0181] As shown in Figure 9 , for example, the anterior eye portion camera 15LA is configured to take an image of the left eye to be examined EL from a direction that forms a positive angle in the Y direction with respect to the measurement optical axis OL, and the anterior eye portion camera 15LB is configured to take an image of the left eye to be examined EL from a direction that forms a negative angle in the Y direction with respect to the measurement optical axis OL. It is also possible to configure the anterior eye portion camera 15LA to take an image of the left eye to be examined EL from a direction that forms a positive angle in the X direction with respect to the measurement optical axis OL, and the anterior eye portion camera 15LB to take an image of the left eye to be examined EL from a direction that forms a negative angle in the X direction with respect to the measurement optical axis OL.

[0182] Likewise, for example, the anterior eye portion camera 15RA is configured to take an image of the right eye to be examined ER from a direction that forms a positive angle in the Y direction with respect to the measurement optical axis OR, and the anterior eye portion camera 15RB is configured to take an image of the right eye to be examined ER from a direction that forms a negative angle in the Y direction with respect to the measurement optical axis OR. It is also possible to configure the anterior eye portion camera 15RA to take an image of the right eye to be examined ER from a direction that forms a positive angle in the X direction with respect to the measurement optical axis OR, and the anterior eye portion camera 15RB to take an image of the right eye to be examined ER from a direction that forms a negative angle in the X direction with respect to the measurement optical axis OR.

[0183] It is also possible to implement part of the functions of the anterior eye portion cameras 15LA, 15RA, 15LB, 15RB by one anterior eye portion camera.

[0184] Figure 10 A configuration example in which the functions of the anterior eye portion cameras 15LA, 15RA, 15LB, 15RB are implemented by the anterior eye portion camera 15LR Figure 1Configuration example in the case of the function of the front eye cameras 15LB, 15RB of the first embodiment.

[0185] The front eye camera 15LR captures the front eye portions of the left and right examination eyes EL, ER. As shown in FIG. 1, for example, the front eye camera 15LA is configured to capture the left examination eye EL from a direction that forms a positive angle of the Y direction with respect to the measurement optical axis OL, and the front eye camera 15LR is configured to capture the left examination eye EL from a direction that forms a negative angle of the Y direction with respect to the measurement optical axis OL. It is also possible to configure the front eye camera 15LA to capture the left examination eye EL from a direction that forms a positive angle of the X direction with respect to the measurement optical axis OL, and the front eye camera 15LR to capture the left examination eye EL from a direction that forms a negative angle of the X direction with respect to the measurement optical axis OL. Figure 10 Similarly, for example, the front eye camera 15RA is configured to capture the right examination eye ER from a direction that forms a positive angle of the Y direction with respect to the measurement optical axis OR, and the front eye camera 15LR is configured to capture the right examination eye ER from a direction that forms a negative angle of the Y direction with respect to the measurement optical axis OR. It is also possible to configure the front eye camera 15LR to capture the right examination eye ER from a direction that forms a positive angle of the X direction with respect to the measurement optical axis OR, and the front eye camera 15RA to capture the right examination eye ER from a direction that forms a negative angle of the X direction with respect to the measurement optical axis OR.

[0186] The ophthalmic apparatus 1 of the embodiment can at least share the objective lens in the reflection measurement optical system and the OCT optical system 8, and can perform both the reflection measurement (refractive power measurement) using the reflection measurement optical system and the OCT measurement using the OCT optical system 8. The reflection measurement can be performed on both the left and right examination eyes simultaneously. The OCT measurement can be performed on either one of the left and right examination eyes sequentially. In several embodiments, before the OCT measurement is performed on one of the left and right examination eyes EL, ER, the OCT optical system 8 is controlled based on the axial length and the refractive power of the other one of the left and right examination eyes EL, ER, whereby the optical path length of the reference light path is adjusted. Thereby, before the OCT measurement is performed on one examination eye, the measurement environment estimated from the measurement environment of the other examination eye can be set, and thus the time required for the OCT measurement can be shortened.

[0187] The ophthalmic apparatus 1 of the first embodiment can adjust the optical axis (the axis of the optical path of the measurement light) of the OCT optical system 8.

[0188] <Adjustment example of the optical axis of the OCT optical system 8>

[0189]

[0190] An explanatory diagram showing a first adjustment example of the optical axis of the OCT optical system 8 of the first embodiment. In the first adjustment example, the optical axis of the OCT optical system 8 is adjusted based on the axial length of the left examination eye EL. Figure 11A Figure 11A Figure 1 ​​Identical parts are labeled with the same reference numerals, and descriptions are omitted where appropriate.

[0191] The measurement optical system 300 includes deflection components DF1 and DF2. Deflection component DF1 deflects the optical axis of the OCT optical system 8 to deflect component DF2, and deflection component DF2 deflects the optical axis deflected by deflection component DF1 to prism PR. For example, by moving deflection component DF1 in the optical axis direction, the optical axis of the OCT optical system 8 can be adjusted so that it approximately coincides with the other optical axis from one of the measurement optical axes OL and OR. For example, at the position of deflection component DF1', the optical axis of the OCT optical system 8 can be approximately coincident with the measurement optical axis OL, and at the position of deflection component DF1, the optical axis of the OCT optical system 8 can be approximately coincident with the measurement optical axis OR.

[0192] For example, the ophthalmic device 1 moves the deflection component DF1 according to the interpupillary distance of the subject, thereby enabling the optical axis of the OCT optical system 8 to approximately coincide with either of the measurement optical axes OL or OR.

[0193] exist Figure 6 In the example of deflection component DF1, a reflector 81 is included. In the example of deflection component DF2, a dichroic mirror 52 is included.

[0194] Figure 11B An explanatory diagram showing a second adjustment example of the optical axis of the OCT optical system 8 according to the first embodiment. Figure 11B In the middle, to and Figure 1 Identical parts are labeled with the same reference numerals, and descriptions are omitted where appropriate.

[0195] 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.

[0196] 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.

[0197] Figure 11C An explanatory diagram showing a third adjustment example of the optical axis of the OCT optical system 8 according to the first embodiment. Figure 11C In the middle, to and Figure 1 Identical parts are labeled with the same reference numerals, and descriptions are omitted where appropriate.

[0198] The measuring optical system 300 (ophthalmic device 1) includes a prism PR (or...) under the control of a control unit described later. Figure 5 The illustrated moving mechanism moves the mirrors (RML, RMR) in the X direction. This moving mechanism can also move the prism PR in a direction intersecting the Z direction. For example, by moving the prism PR in the X direction, the optical axis of the OCT optical system 8 can be adjusted so that one of the measurement optical axes OL and OR approximately coincides with the other. For example, at the position of the prism PR′, the optical axis of the OCT optical system 8 can approximately coincide with the measurement optical axis OL, and at the position of the prism PR, the optical axis of the OCT optical system 8 can approximately coincide with the measurement optical axis OR.

[0199] For example, the ophthalmic device 1 can move the prism PR in the X direction according to the interpupillary distance of the subject, so that the optical axis of the OCT optical system 8 is approximately coincident with either the measurement optical axis OL or OR.

[0200] Furthermore, as a fourth 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 using optical components in the path of the measured light. Examples of optical components include... Figure 6 The reflector 81, dichroic mirror 52, and other reflectors not shown are included. For example, the direction of deflection of the optical axis 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.

[0201] <Structure of the Processing System>

[0202] Explain the structure of the processing system of ophthalmic device 1.

[0203] Figure 12 and Figure 13 An example of the functional structure of the processing system of ophthalmic device 1 is shown. Figure 12 An example of a functional block diagram of the processing system of ophthalmic device 1 is shown. Figure 13 Show Figure 12 An example of a functional block diagram of the OCT optical system 8. Figure 12 and Figure 13 In the middle, to and Figure 1 or Figure 6 Identical parts are labeled with the same reference numerals, and descriptions are omitted where appropriate.

[0204] The processing unit 9 controls various parts of the ophthalmic device 1. Furthermore, the processing unit 9 is capable of performing various arithmetic operations. The functions of the processing unit 9 are implemented through processing circuitry. The processing unit 9 includes one or more processors. The functions of the processors are implemented, for example, through circuitry of a CPU (Central Processing Unit), GPU (Graphics Processing Unit), ASIC (Application Specific Integrated Circuit), or programmable logic device (e.g., SPLD (Simple Programmable Logic Device), CPLD (Complex Programmable Logic Device), FPGA (Field Programmable Gate Array)). The processing unit 9 implements the functions of the embodiment, for example, by reading and executing a program stored in a storage circuit or storage device.

[0205] In several embodiments, the processing unit 9 includes a single processor that implements the functions of the embodiments. In several embodiments, the processing unit 9 includes multiple processors that each implement one or more functions of the embodiments.

[0206] The processing unit 9 includes a control unit 210 and a computing unit 220. Additionally, the ophthalmic device 1 includes a moving mechanism 200, 310, 320, a display unit 270, an operation unit 280, and a communication unit 290.

[0207] The moving mechanism 200 is used to move a head housing an optical system, including anterior eye cameras 15LA, 15LB, 15RA, 15RB, an XY alignment system 2, a corneal measurement system 3, anterior eye observation system 5, reflectance measurement projection systems 6L, 6R, a reflectance measurement light receiving system 7, and an OCT optical system 8, in the X, Y, and Z directions. For example, the moving mechanism 200 includes an actuator that generates a driving force for moving the head and a transmission mechanism that transmits this driving force. The actuator may be, for example, a pulse motor. The transmission mechanism may be, for example, a gear assembly or a rack and pinion. The control unit 210 (main control unit 211) controls the moving mechanism 200 by sending control signals to the actuator.

[0208] like Figure 3 As shown, the moving mechanism 310 moves the prism PR. For example, the moving mechanism 310 has the same structure as the moving mechanism 200. The control unit 210 (main control unit 211) controls the moving mechanism 310 by sending control signals to the actuator.

[0209] As shown in FIG. 20, the moving mechanism 320 independently rotates the dichroic mirrors ML, MR around the rotation axes. For example, the moving mechanism 320 is provided with an actuator that generates a driving force for rotating the dichroic mirrors ML, MR 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

[0210] Further, an illustration is omitted, but 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 11A to Figure 11C

[0211] (Control section 210)

[0212] 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.

[0213] 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, synchronous control of the front eye portion cameras 15LA, 15LB, synchronous control of the front eye portion cameras 15RA, 15RB, and synchronous control of the front eye portion cameras 15LA, 15LB, 15RA, 15RB.

[0214] ​​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.).

[0215] 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.

[0216] 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 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.

[0217] 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.

[0218] 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.

[0219] 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.

[0220] Further, for example, the moving mechanism that moves the liquid crystal panel 41L, 41R (or the fixation unit 40L, 40R) in the optical axis direction is provided in the fixation projection system 4L, 4R. The moving mechanism is provided with the actuator that generates the driving force for moving the moving mechanism and the 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 actuator. 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.

[0221] The control of the anterior eye portion observation system 5 includes the control of the anterior eye portion illumination light source 50, the control of a lens moving mechanism that moves the relay lens 56, the control of the imaging element 59, and the like. The control of the anterior eye portion illumination light source 50 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 anterior eye portion illumination light source 50 are switched 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 the exposure adjustment, the gain adjustment, the 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 a process of image formation and the like based on the received signal.

[0222] The control of the retroillumination measurement projection system 6L, 6R includes the control of the retroillumination light source 61L, 61R, the control of the rotating prism 66, and the like. The control of the retroillumination light source 61L, 61R includes the lighting, the extinguishing, the light amount adjustment, and the like of the light source. Thereby, the lighting and the non-lighting of the retroillumination light source 61L, 61R are switched or the light amount is changed. For example, the retroillumination measurement projection system 6L includes a moving mechanism that moves the retroillumination light source 61L in the optical axis direction, and the retroillumination measurement projection system 6R includes a moving mechanism that moves the retroillumination light source 61R in the optical axis direction. These moving mechanisms are 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 mechanisms by transmitting a control signal to the actuators, and moves the retroillumination light sources 61L, 61R independently in the optical axis direction, respectively. In several embodiments, the retroillumination light sources 61L, 61R are moved integrally. The control of the rotating prism 66 includes the 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.

[0223] The control of the reflection photometry 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 reflection photometry light receiving system 7 includes a movement mechanism that moves the focusing lens 74 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 a control signal to the execution mechanism, and moves the focusing lens 74 in the optical axis direction. The main control section 211 can move the reflection photometry light source 61L and the focusing lens 74 in the optical axis direction, respectively, for example, in accordance with the refractive power of the left eye to be examined EL, so that the reflection photometry light source 61L and the fundus ELf are optically conjugate with the imaging element 59. In addition, the main control section 211 can move the reflection photometry light source 61R and the focusing lens 74 in the optical axis direction, respectively, for example, in accordance with the refractive power of the right eye to be examined ER, so that the reflection photometry light source 61R and the fundus ERf are optically conjugate with the imaging element 59.

[0224] The control of the OCT optical system 8 includes control of the light source unit 101, control of the optical attenuator 105, control of the polarization wave controller 106, control of the variable magnification optical system 114, control of the CCD image sensor 115, control of the focusing lens 87, control of the optical scanner 88, control of the optical path length changer 89, and the like.

[0225] The control of the light source unit 101 includes lighting, extinguishing, light amount adjustment, aperture adjustment, and the like of the light source. The control of the optical attenuator 105 includes adjustment of the light amount of the reference light LR and the like. The control of the polarization wave controller 106 includes adjustment of the polarization wave state of the reference light LR and the like. The control of the variable magnification optical system 114 includes control of the optical magnification and the like. The control of the CCD image sensor 115 includes exposure adjustment, gain adjustment, detection rate adjustment, and the like of the CCD image sensor 115. The main control section 211 receives a signal detected by the CCD image sensor 115, and causes the arithmetic processing section 220 to perform processing of image formation and the like based on the received signal.

[0226] The control of the focusing lens 87 includes 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 a control signal to the execution mechanism, and moves the focusing lens 87 in the optical axis direction.

[0227] In several embodiments, the ophthalmic device 1 is provided with a holding member for holding the focusing lenses 74 and 87 and a drive unit for driving the holding member. The main control unit 211 controls the movement of the focusing lenses 74 and 87 by controlling the drive unit. For example, the main control unit 211 may move the focusing lens 87 only based on the intensity of the interference signal after moving the focusing lens 74 in conjunction with the movement of the focusing lens 87.

[0228] The control of the optical scanner 88 includes setting the scanning mode for scanning the measurement area using a predetermined scanning pattern, controlling the scanning range, and controlling the scanning speed. The angle range of the deflection surface that causes the measuring light LS to deflect can be controlled by controlling the scanning range (scan start position and scan end position). The rate at which the angle of the deflection surface changes can be controlled by controlling the scanning speed. The main control unit 211 controls at least one of the scanning mode, scanning range, and scanning speed by outputting control signals to the optical scanner 88.

[0229] The control of the optical path length changing unit 89 includes the control of the optical path length of the measured optical LS. The main control unit 211 outputs a control signal to the optical path length changing unit 89, causing the optical path length changing unit 89 to change the optical path length of the measured optical LS.

[0230] In addition, the main control unit 211 performs the processing of writing data to the storage unit 212 and the processing of reading data from the storage unit 212.

[0231] (Storage Department 212)

[0232] Storage unit 212 stores various types of data. Data stored in storage unit 212 includes, for example, measurement results of objective visual acuity tests (OCT measurement results), image data of OCT images, image data of anterior eye images, results of subjective examinations, and information about the examined eye. Information about the examined eye includes patient ID, name, and other information related to the subject, as well as left / right eye identification information and other information related to the examined eye. Additionally, storage unit 212 stores various programs and data used to operate the ophthalmic device.

[0233] (Computational Processing Unit 220)

[0234] The arithmetic processing unit 220 includes a processor that performs various arithmetic operations. A computer program for performing these various arithmetic operations is pre-stored in a storage unit (e.g., storage unit 212) not shown. The processor operates according to this computer program, thereby realizing the functions of each unit for performing the various arithmetic operations.

[0235] like Figure 12 As shown, the arithmetic processing unit 220 includes an ocular refractive power calculation unit 221, an image forming unit 222, and a data processing unit 223.

[0236] The ocular refractive power calculating section 221 calculates the refractive power value of each of the left eye EL and the right eye ER based on the results of the reflection measurement performed simultaneously on both eyes. The image forming section 222 forms an OCT image based on the detection results 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 the measurement results obtained using the optical system provided in the ophthalmic apparatus 1 (detection results of the interference light LC, etc.), the OCT image formed by the image forming section 222.

[0237] (Ocular refractive power calculating section 221)

[0238] The ocular refractive power calculating section 221 analyzes the annular image (pattern image) obtained by the return light of the annular light beam (annular measurement pattern) projected to the fundus ELf by the reflection measurement projection system 6L received by the imaging element 59, and calculates the refractive power value of the left eye EL. In addition, the ocular refractive power calculating section 221 analyzes the annular image (pattern image) obtained by the return light of the annular light beam projected to the fundus ERf by the reflection measurement projection system 6R received by the imaging element 59, and calculates the refractive power value of the right eye 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 luminance distribution in the image depicting the annular image, obtains the luminance distribution along a plurality of scanning directions extending radially from the center of gravity position, and specifies the annular image from the luminance 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 the reference pattern.

[0239] In addition, the ocular refractive power calculating section 221 calculates the corneal refractive power, the corneal astigmatism power, and the corneal astigmatism axis angle of each of the left eye EL and the right eye ER based on the corneal ring image of each of the left eye EL and the right eye ER acquired by the anterior eye portion observation system 5. For example, with respect to each corneal ring 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 ring image, and calculates the parameters based on the corneal curvature radii.

[0240] (Image forming section 222)

[0241] The image forming section 222 forms image data of an 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 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 filtering process, an FFT (Fast Fourier Transform) process, 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 path of each measurement light LS in the eye to be examined).

[0242] 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 averaging).

[0243] (Data processing section 223)

[0244] The data processing section 223 performs various data processing (image processing), analysis processing on the tomographic image 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 image. In addition, the data processing section 223 performs various image processing, analysis processing on the image (an anterior eye portion image, and the like) obtained using the anterior eye portion observation system 5.

[0245] The data processing section 223 can form volume 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 the image is displayed based on the volume data, the data processing section 223 performs rendering processing on the volume data to form a simulated three-dimensional image when viewed from a specified line-of-sight direction.

[0246] 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 position of a pixel is defined by a three-dimensional coordinate system. The image data of the three-dimensional image includes image data formed by voxels arranged in three dimensions. This image data is referred to as volume data or voxel data, and the like. In a case where the image is displayed based on the volume data, the data processing section 223 performs rendering processing (stereoscopic rendering, MIP (Maximum Intensity Projection), and the like) on the volume 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.

[0247] In addition, as image data of a 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 positional relationships of the scan lines. That is, the stack data is image data obtained by expressing (that is, embedding in a three-dimensional space) a plurality of tomographic images defined by originally separate two-dimensional coordinate systems by one three-dimensional coordinate system.

[0248] The data processing portion 223 can form a B-mode image (longitudinal sectional image, axial direction sectional image) in an arbitrary cross section, a C-mode image (transverse sectional image, horizontal sectional image) in an arbitrary cross section, 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 specified cross section from a three-dimensional data set. A projection image is formed by projecting a three-dimensional data set in a predetermined direction (Z direction, depth direction, axial direction). A shadow image is formed by projecting a part of a three-dimensional data set (for example, a part of data corresponding to a specified 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.

[0249] The data processing portion 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 based on 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 site of the eye to be examined.

[0250] In several embodiments, the data processing portion 223 compares time-series B-scan images obtained by B-scanning substantially the same site, transforms pixel values of a signal intensity change portion to pixel values corresponding to a change amount, thereby constructing an emphasis image in which the change portion is emphasized. Further, the data processing portion 223 extracts information of a predetermined thickness amount in a desired site from a plurality of constructed emphasis images, constructs an en-face image, thereby forming an OCTA image.

[0251] Images (for example, three-dimensional images, B-mode images, C-mode images, projection images, shadow images, OCTA images) generated by the data processing portion 223 are also included in the OCT images.

[0252] Further, the data processing section 223 analyzes the two captured images acquired substantially simultaneously by the two front eye cameras as described above, respectively, and specifies feature positions corresponding to feature portions of the front eye. The data processing section 223 calculates three-dimensional positions of the feature portions (i.e., three-dimensional positions of the subject eye) by applying a known triangulation method to the positions of the two front eye cameras and the feature positions corresponding to the feature portions in the two captured images as specified. The calculated three-dimensional positions can be used for position alignment of the optical system with respect to the subject eye.

[0253] Further, the ophthalmic apparatus 1 can measure an intraocular parameter by performing an OCT scan on the left subject eye EL or the right subject eye ER. Examples of the intraocular parameter include an axial length, a thickness of a predetermined layer region, a distance between predetermined portions, and the like.

[0254] In the first embodiment, the data processing section 223 is provided as an axial length calculation section that calculates an axial length. In this case, the data processing section 223 can calculate a distance between a position corresponding to the vertex of the cornea and a position corresponding to the Retinal Pigment Epithelium (hereinafter, RPE) layer as the axial length based on the detection result of the interference light LC obtained by performing the OCT scan. For example, the data processing section 223 specifies the position of the vertex of the cornea and the position of the RPE layer by specifying positions of maxima of intensities of interference signals corresponding to the detection result of the interference light LC, and calculates a distance between the two positions as the axial length. For example, the data processing section 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 vertex of the cornea and the position of the RPE layer based on a plurality of layer regions as specified, and calculates a distance between the two positions as the axial length.

[0255] (Display section 270, operation section 280)

[0256] The display section 270 displays information under the control of the control section 210 as a user interface section.

[0257] The operation section 280 is used for operating the ophthalmic apparatus as a user interface section. The operation section 280 includes various hardware keys (joysticks, buttons, switches, and the like) provided to the ophthalmic apparatus. Further, the operation section 280 can include various software keys (buttons, icons, menus, and the like) displayed on a touch panel-type display screen.

[0258] At least a part of the display section 270 and the operation section 280 can be integrally configured. As a typical example, a touch panel-type display screen is included.

[0259] (Communication section 290)

[0260] 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.

[0261] The components and mechanisms that adjust the optical axis of the OCT optical system 8 in any one of the first to fourth 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 6L and the catoptric measurement light receiving system 7 are examples of the "refractive power measurement optical system" of the embodiment. The catoptric measurement projection system 6L is an example of the "first projection system" of the embodiment. The catoptric measurement projection system 6R is an example of the "second projection system" of the embodiment. The catoptric measurement light receiving system 7 is an example of the "light receiving system" of the embodiment.

[0262] <WORKING EXAMPLE>

[0263] A working example of the ophthalmic device 1 of the first embodiment will be described.

[0264] Figure 14 And Figure 15 An example of the operation of the ophthalmic device 1 is shown. Figure 14 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 15 A flowchart showing a processing example of Step S2 of Figure 14 is shown. The computer program for implementing the processing shown in Figure 14 and Figure 15 is stored in the storage section 212. The main control section 211 operates in accordance with the computer program, and executes the processing of Figure 14and Figure 15 the processing shown.

[0265] Here, it is assumed that the examination in either of the near vision or the distance vision is determined in advance before the flow shown below is started. Figure 14

[0266] (S1: Adjustment of convergence angle)

[0267] 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, and adjusts the convergence angle.

[0268] As shown in Figure 4 , the dichroic mirrors ML, MR change the deflection direction of the optical axis deflected by the prism PR.

[0269] (S2: Alignment)

[0270] Next, the main control section 211 performs alignment. Step S2 is described in detail later.

[0271] In step S2, the alignment of the positions of the optical system 300 with respect to the left and right examination eyes EL, ER is performed.

[0272] (S3: Acquisition of binocular anterior eye portion image)

[0273] Next, the main control section 211 controls the anterior eye portion observation system 5 to acquire the binocular anterior eye portion image.

[0274] Specifically, the main control section 211 controls the corneal measurement system 3 and turns on the corneal ring light source 32 to project the ring-shaped light beam to the cornea CLr of the left examination eye EL and the cornea CRr of the right examination eye 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 portions of the left and right examination eyes EL, ER. Thereafter, the main control section 211 acquires the binocular anterior eye portion image in which the anterior eye portion of the left examination eye EL on which the corneal ring image is superimposed and the anterior eye portion of the right examination eye ER on which the corneal ring image is superimposed are depicted, by receiving the light-receiving results of the return light of the illumination light in the imaging surface of the imaging element 59.

[0275] In several embodiments, the ring-shaped light beam is transmitted to the left and right examination eyes EL, ER in sequence, and the anterior eye portion image of the left examination eye EL on which the corneal ring image is superimposed and the anterior eye portion image of the right examination eye ER on which the corneal ring image is superimposed are acquired in sequence. The binocular anterior eye portion image is acquired by synthesizing the anterior eye portion image of the left examination eye EL and the anterior eye portion image of the right examination eye ER acquired in sequence.

[0276] (S4: Corneal shape analysis) ​

[0277] Next, the main control section 211 analyzes the front eye portion images of both eyes acquired in step S3 by controlling the eye refractive power calculating section 221. As described above, the eye refractive power calculating 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 refractive 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.

[0278] (S5: Preliminary measurement)

[0279] Next, the main control section 211 performs a preliminary measurement for reflection measurement of both eyes. In the preliminary measurement, the focusing state in the reflection measurement optical system is changed in accordance with the refractive power of each of the left and right examination eyes EL and ER. In the reflection measurement (the present measurement), the refractive power of each of the left and right examination eyes EL and ER is measured while the clouding of the left and right examination eyes EL and ER is promoted with the focusing state changed by the preliminary measurement as a reference.

[0280] For example, the reflection measurement light sources 61L, 61R, the focusing lenses 74, 87 are respectively moved in the optical axis direction and disposed at positions corresponding to the refractive power of the examination eyes. The main control section 211 turns on the reflection measurement light sources 61L, 61R and causes the rotating prism 66 to start rotating. Next, the main control section 211 projects the annular measurement pattern light beams to the left and right examination eyes EL and ER, respectively. The annular image based on the return light of the measurement pattern light beams from the left and right examination eyes EL and ER is imaged on the imaging surface of the imaging element 59.

[0281] The main control section 211 determines whether the annular image based on the return light from the fundus ELf, ERf 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 (image) of a predetermined height (ring diameter) or more, and thereby determine whether the annular image can be acquired.

[0282] When it is determined that the annular image can be acquired, the eye refractive power calculating 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 preliminary spherical degree S and the preliminary astigmatism degree C with respect to each of the left and right examination eyes EL and ER.

[0283] The main control section 211 moves the retro-reflective measurement light sources 61L, 61R, the focusing lens 74, and the liquid crystal panels 41L, 41R to the position of the equivalent spherical power (S+C / 2) based on the calculated temporary spherical power S and the temporary astigmatism C.

[0284] The main control section 211 again causes the annular measurement pattern light beams to be projected to each of the left and right eyes under examination EL, ER. The annular images based on the return light of the measurement pattern light beams from the fundus ELf, ERf detected by the photographing element 59 are imaged on the photographing surface of the photographing element 59. The main control section 211 determines whether or not the annular images based on the return light of the measurement pattern light beams from the fundus ELf, ERf detected by the photographing element 59 can be acquired.

[0285] When it is determined that the annular images are acquired, the ocular power calculation section 221 analyzes the annular images based on the return light of the projected measurement pattern light beams by a known method to calculate the temporary spherical power S and the temporary astigmatism C with respect to each of the left and right eyes under examination EL, ER.

[0286] The main control section 211 controls the ocular power calculation section 221 to calculate the intermediate power position of the left and right eyes under examination EL, ER. For example, the intermediate power position can be the position of the intermediate power ((ESR+ESL) / 2) corresponding to the equivalent spherical power ESL of the left eye under examination EL and the equivalent spherical power ESR of the right eye under examination ER.

[0287] The main control section 211 moves the retro-reflective measurement light sources 61L, 61R, the focusing lens 74, and the liquid crystal panels 41L, 41R to the intermediate power position with respect to each of the left and right eyes under examination EL, ER. The moved position is the position corresponding to the temporary far point.

[0288] In several embodiments, the main control section 211 does not calculate the intermediate power position, and moves the retro-reflective measurement light sources 61L, 61R, the focusing lens 74, and the liquid crystal panels 41L, 41R to the position of the equivalent spherical power with respect to each of the left and right eyes under examination EL, ER.

[0289] Further, in the step S5, in a case where the results of the temporary measurement on the both eyes do not converge due to anisometropia or the like, the temporary measurement can be performed on each of the single eyes. In this case, the intermediate power position of the left and right eyes under examination EL, ER can be calculated from the equivalent spherical powers obtained by the temporary measurement on each of the single eyes as described above while blocking the light path of the fixation projection system on the side other than the measurement object by a shutter or the like.

[0290] (S6: Promoting clouding of both eyes)

[0291] Next, the main control section 211 moves each of the liquid crystal panels 41L, 41R further toward the cloud position from the position found in the temporary measurement in step S5 while promoting the cloud of the both eyes.

[0292] (S7: Refractive power measurement)

[0293] Next, the main control section 211 simultaneously performs the reflection measurement on the both eyes.

[0294] Specifically, the main control section 211 lights up the reflection measurement light sources 61L, 61R in a case where the reflection measurement light sources 61L, 61R are 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 found 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.

[0295] The main control section 211 acquires the annular images by controlling the reflection measurement projection systems 6L, 6R and the reflection measurement light receiving systems 7 similarly to the temporary measurement in step S5. That is, the reflection measurement optical system projects the measurement pattern light beams for the left eye under examination EL and the right eye under examination ER and acquires the respective annular images of the both eyes 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. With respect to each of the both eyes, the main control section 211 causes the ocular 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 annular 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.

[0296] That is, the reflection measurement optical system projects the measurement pattern light beams along the measurement optical axis OL to the left eye under examination EL and along the measurement optical axis OR to the right eye under examination ER via the objective lens 51 and receives the return light of the measurement pattern light beams from the left eye under examination EL and the return light of the measurement pattern light beams from the right eye under examination ER. The ocular 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 beams from the left eye under examination EL and 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 beams from the right eye under examination ER.

[0297] In several embodiments, the acquisition of the anterior eye segment image in step S3 and the corneal shape analysis in step S4 are simultaneously performed in step S7.

[0298] (S8: Adjustment of the optical axis of the OCT optical system so as to coincide with the measurement optical axis of the single eye)

[0299] Next, the main control section 211 adjusts the optical axis of the OCT optical system 8 so as to coincide with the measurement optical axis of the monocular. The main control section 211 can adjust the optical axis of the OCT optical system 8 so as to coincide with the measurement optical axis of the monocular as shown in any one of Figure 3 , Figure 4 , Figure 11A to Figure 11C adjust the optical axis of the OCT optical system 8 so as to coincide with the measurement optical axis of the monocular.

[0300] For example, the main control section 211 moves the optical axis of the OCT optical system 8 in the Y direction as shown in Figure 11B For example, the main control section 211 moves the optical axis of the OCT optical system 8 in the X direction as shown in Figure 11A For example, the main control section 211 moves the optical axis of the OCT optical system 8 in the X direction as shown in

[0301] In several embodiments, the alignment in step S2 is performed before the OCT measurement in step S9.

[0302] (S9: OCT measurement)

[0303] Next, the main control section 211 performs the OCT measurement by controlling the OCT optical system 8.

[0304] For example, the main control section 211 prompts the subject eye of the measurement target with a fixation target for the OCT measurement, controls the OCT optical system 8 to perform the OCT provisional measurement, and acquires an adjustment tomographic image 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 on the basis of the light L0 emitted from the light source unit 101, and scans a predetermined site (e.g., the fundus) of the subject eye 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 a tomographic image (OCT image) of the subject eye on the basis of the obtained interference signal.

[0305] 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 site (e.g., the sclera) in the obtained tomographic image, and sets a position separated by a predetermined distance in the depth direction from the position of the specified predetermined site 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 coincides with that of the reference light LR.

[0306] 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 focus lens 87 by a predetermined distance.

[0307] 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 relating 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 it is determined that the focus state of the measurement light LS is appropriate.

[0308] In several embodiments, the main control section 211 monitors the intensity of the interference signal (interference intensity, interference sensitivity) acquired successively while acquiring the interference signal by the repeated OCT measurement as described above. Also, the focus lens 87 is moved while this monitoring process is performed, and thus the position of the focus lens 87 at which the interference intensity is the maximum is searched. Based on such focus adjustment, the focus lens 87 can be guided to the position at which the interference intensity is optimized.

[0309] In addition, the data processing section 223 analyzes the detection result of the interference light obtained by the OCT measurement, and determines the polarization wave state of at least one of the measurement light LS and the reference light LR.

[0310] For example, the main control section 211 controls the polarization wave controller 106 in accordance with a predetermined algorithm while performing the repeated OCT measurement. In several embodiments, the main control section 211 controls the optical attenuator 105, and changes the attenuation amount of the reference light LR. The data processing section 223 analyzes the detection result of the interference light LC acquired repeatedly by the OCT measurement, calculates a predetermined evaluation value relating to the quality of the OCT image, and determines whether the calculated evaluation value is below a threshold value. The threshold value is set in advance. The polarization 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 adjustment continues until it is determined that the polarization wave state of the measurement light LS is appropriate.

[0311] In several embodiments, the main control section 211 can monitor the interference intensity also in the polarization adjustment.

[0312] When the position adjustment in the depth direction, the focus adjustment, and the polarization adjustment are completed, the main control section 211 causes the optical scanner 88 to scan a predetermined portion of the fundus of the eye to be examined of the subject 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.

[0313] The main control section 211 controls the data processing section 223 to calculate the distance between the position corresponding to the corneal vertex and the position corresponding to the RPE layer as the axial length based on 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). The main control section 221 controls the data processing section 223 to calculate the distance between the position corresponding to the corneal vertex and the position corresponding to the RPE layer as the axial length based on the detection signal or tomographic image obtained by scanning the cornea and the detection signal or tomographic image obtained by scanning the fundus. For example, a method of calculating such an axial length is disclosed in Japanese Patent Application Publication No. 2020-044027.

[0314] In several embodiments, in a case where OCT measurement is performed on each monocular eye, before OCT measurement is performed on one of the left and right examined eyes EL and 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 and right examined eyes EL and ER. That is, in a case where the optical path length of the reference light path, which is one of the measurement environments of the OCT measurement, can be associated with the axial length and the refractive power of the examined eye and the optical path length of the reference light path is substantially 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 examined eye that is initially performed is specified based on the axial length and the refractive power of the examined eye that is next performed, and the optical path length of the reference light path at the time of the OCT measurement of the examined eye is adjusted to the specified optical path length. Thereby, the time required for the OCT measurement of both eyes can be greatly shortened.

[0315] (S10: Measurement of both eyes completed?)

[0316] Next, the main control section 211 determines whether the measurement of both eyes is completed. When it is determined that the measurement of both eyes is completed (S10: YES), the operation of the ophthalmic apparatus 1 ends (END). When it is determined that the measurement of both eyes is not completed (S10: NO), the operation of the ophthalmic apparatus 1 shifts to step S8.

[0317] In several embodiments, after the process of steps S1 to S10 is performed on one of the far vision time and the near vision time, the process of steps S1 to S10 is performed on the other of the far vision time and the near vision time, whereby the examination is performed in both the far vision time and the near vision time. In several embodiments, after the refractive power measurement of steps S1 to S7 is performed on one of the far vision time and the near vision time, the refractive power measurement of steps S1 to S7 is performed on the other of the far vision time and the near vision time.

[0318] As shown in FIG. 8, the process of steps S1 to S10 is performed on the left and right examined eyes EL and ER in the far vision time (S11). Figure 15 As shown in FIG. 8, the process of steps S1 to S10 is performed on the left and right examined eyes EL and ER in the far vision time (S11). Figure 14the step S2.

[0319] (S21: Specifying pupil positions of both eyes)

[0320] First, the main control section 211 specifies the feature positions of both eyes based on the captured images obtained by controlling the front eye camera 15LA, 15RA, 15LB, 15RB. In the present embodiment, the pupil positions are specified as the feature positions.

[0321] Specifically, the main control section 211 controls the front eye cameras 15LA, 15LB to capture the left eye EL substantially simultaneously from different directions, and acquires two captured images (front eye images). Similarly, the main control section 211 controls the front eye cameras 15RA, 15RB to capture the right eye ER substantially simultaneously from different directions, and acquires two captured images. In several embodiments, the two captured images of the left eye EL and the two captured images of the right eye ER are captured substantially simultaneously.

[0322] The specification process of the pupil position of the left eye EL is the same as that of the pupil position of the right eye ER. Hereinafter, the specification process of the pupil position of the left eye EL will be mainly described.

[0323] 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 cameras 15LA, 15LB, and specify the pupil position (pupil center position or pupil barycentric position) of the left eye EL.

[0324] 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, and thus 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 substantially circular and has low luminance.

[0325] Next, the data processing section 223 specifies the center position of the specified pupil region. As described above, the pupil is substantially circular, and thus the outline of the pupil region can be specified, and the center position of the outline (approximate circle or approximate ellipse) can be specified as the pupil center position. Alternatively, the barycentric position of the pupil region can be calculated, and the barycentric position can be specified as the pupil barycentric position.

[0326] The data processing portion 223 can successively specify the pupil positions with respect to the captured images successively obtained by the front eye portion cameras 15LA, 15LB. Alternatively, the data processing portion 223 can specify the pupil positions with respect to the captured images successively obtained by the front eye portion cameras 15LA, 15LB at every arbitrary number of frames of one or more.

[0327] Next, the data processing portion 223 specifies the three-dimensional position of the feature position as the three-dimensional position of the subject eye, based on the positions of the front eye portion cameras 15LA, 15LB and the specified pupil positions, as a three-dimensional position calculation portion. For example, as disclosed in Japanese Patent Application Publication No. 2013-248376, the data processing portion 223 calculates the three-dimensional position of the subject eye by applying a known triangulation method to the positions (known) of the two front eye portion cameras 15LA, 15LB and the pupil positions in the two captured images.

[0328] The pupil position of the right subject eye ER can also be specified by the same processing as described above.

[0329] (S22: Movement of measurement optical axes)

[0330] The main control portion 211 controls the movement of the measurement optical system 300, the movement of the prism PR, and the presentation of the fixation targets by the fixation projection systems 4L, 4R, based on the pupil positions of the both eyes specified in step S21. Figure 3 The adjustment of the interpupillary distance of the prism PR and the positions of the fixation targets presented by the fixation projection systems 4L, 4R are shown.

[0331] Specifically, the interpupillary distance is specified based on the pupil positions of the both eyes specified in step S21. For example, the main control portion 211 adjusts at least one of the movement mechanism 200, the movement 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 known respective measurement optical axes OL, OR. The main control portion 211 can change the relative positions of the measurement optical system 300 with respect to the left and right subject eyes EL, ER by controlling the movement mechanism 200. The main control portion 211 can change the distance between the measurement optical axes OL, OR by moving the prism PR by controlling the movement mechanism 310. The main control portion 211 can change the fixation positions (fixation target presentation positions) of the left and right subject eyes EL, ER by controlling the fixation projection systems 4L, 4R.

[0332] As a result, the positions in the X and Y directions of the left subject eye EL and the positions in the X and Y directions of the measurement optical axis OL are adjusted to substantially coincide, and the distance in the Z direction becomes a predetermined working distance.

[0333] In several embodiments, the main control section 211 determines whether the arrangement directions of the left and right examination eyes EL and ER are parallel to the X direction (i.e., whether the heights of the two eyes are offset) based on the pupil positions of the two 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 two eyes specified in step S21, whereby it is possible to change at least one of the deflection directions of the prisms PR (deflection surfaces Ml, M2) and the deflection directions of the dichroic mirrors ML, MR.

[0334] In several embodiments, when it is determined that the arrangement directions of the left and right examination eyes EL and 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.

[0335] (S23: Acquire anterior eye portion images of two eyes)

[0336] Next, the main control section 211 acquires anterior eye portion images of the two eyes that depict XY bright spot images based on reflected light from the light of the XY alignment light source 21 by again controlling the anterior eye portion cameras 15LA, 15RA, 15LB, 15RB after the XY alignment light source 21 is lit.

[0337] (S24: Detect XY bright spot images?)

[0338] 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 two eyes acquired in step S23.

[0339] For example, the data processing section 223 detects whether the two anterior eye portion images of the left examination eye EL and the two anterior eye portion images of the right examination eye ER each depict XY bright spot images based on pixel values. When it is detected by the data processing section 223 that all of the four anterior eye portion images depict 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 anterior eye portion images does not depict an XY bright spot image (S24: No), the operation of the ophthalmic apparatus 1 shifts to step S22.

[0340] (S25: Specify positions of XY bright spot images of two eyes)

[0341] When the XY bright spot images of the both eyes are detected in the anterior eye portion images of the both eyes in step S24 (S24: YES), the main control portion 211 controls the data processing portion 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.

[0342] (S26: Movement of measurement optical axis)

[0343] The main control portion 211 controls the movement of the measurement optical system 300, the adjustment of the interpupillary distance of the prism PR, and the presentation of the fixation target position by the fixation projection systems 4L, 4R, on the basis of 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 prism PR and the presentation of the fixation target position by the fixation projection systems 4L, 4R are shown.

[0344] In step S26, the adjustment of the measurement optical axis is performed in the same manner as in step S22.

[0345] (S27: Acquisition of anterior eye portion images of both eyes)

[0346] Next, the main control portion 211 controls the anterior eye portion cameras 15LA, 15RA, 15LB, 15RB to acquire the anterior eye portion images of the both eyes.

[0347] (S28: Specification of positions of XY bright spot images of both eyes)

[0348] Next, the main control portion 211 controls the data processing portion 223 in the same manner as in step S25 to specify the positions of the XY bright spot images of the both eyes on the basis of the anterior eye portion images of the both eyes acquired in step S27.

[0349] (S29: Alignment complete?)

[0350] Next, the main control portion 211 determines whether each of the positions of the XY bright spot images of the both eyes specified in step S28 is within a predetermined alignment completion range.

[0351] 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 14 the process 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 ophthalmologic apparatus 1 shifts to step S26.

[0352] As described above, in the ophthalmologic apparatus 1 according to the present embodiment, the positions of the XY bright spot images of the both eyes are specified on the basis of the anterior eye portion images of the both eyes acquired in step S27. Figure 14In step S2, the main control section 211 changes the relative positions of the OCT optical system 8 with respect to the left and right eyes EL and ER based on the two or more images obtained by the two or more front eye sections, and simultaneously changes 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 eye EL and the measurement optical axis OR coincides with the visual axis of the right eye ER.

[0353] As described above, according to the first embodiment, the optical axis of the OCT optical system 8 that performs OCT measurement via the objective lens through which the measurement optical axes OL and OR pass, which are arranged separately from each other, is adjusted to substantially coincide with either of the measurement optical axes OL and OR, and thus OCT measurement can be performed on both eyes in turn in a state in which both eyes are open. Thus, 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 an ophthalmic apparatus that can perform OCT measurement on both eyes can be achieved. In addition, since the refractive power is measured by the objective lens through which the measurement optical axes OL and OR pass, refractive power measurement can also be performed on both eyes simultaneously in a state in which both eyes are open.

[0354] [Second Embodiment]

[0355] In the first embodiment, a case in which 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 both eyes.

[0356] 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.

[0357] Figure 16 and Figure 17 An example of the structure of the optical system of the ophthalmic apparatus of the second embodiment is shown. Figure 16 With Figure 1 Similarly, the structure of the optical system of the ophthalmic apparatus of the second embodiment when viewed from above is schematically shown. Figure 17 is a block diagram showing Figure 16 an example of the structure of the measurement optical system 300a of

[0358] 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 and 4R.

[0359] The mirror ML1 deflects the measurement optical axis OL deflected by the deflecting surface Ml of the prism PR toward the left of the examined eye EL. The mirror MR1 deflects the measurement optical axis OR deflected by the deflecting surface M2 of the prism PR toward the right of the examined eye ER.

[0360] As Figure 17 shown, 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 systems 6L, 6R, the reflection measurement light receiving system 7, and the OCT optical system 8.

[0361] As with the ophthalmic apparatus 1, the ophthalmic apparatus la also includes an optical axis adjustment section, an interpupillary distance adjustment section, and a convergence angle adjustment section.

[0362] Figure 18 An explanatory diagram showing an operation example of the interpupillary distance adjustment section in the ophthalmic apparatus la of the second embodiment. In Figure 18 , the same reference numerals are attached to the same parts as Figure 3 or Figure 16 , and the explanation is appropriately omitted.

[0363] 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 prism PR having the deflecting surfaces Ml, M2 along the measurement optical axis OL or the measurement optical axis OR (Z direction, optical axis of the measurement optical system 300a). Thereby, as Figure 18 shown, the positions of the optical axes deflected by the mirrors ML1, MR1 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.

[0364] In several embodiments, the interpupillary distance is changed by moving the prism PR in the X direction shown. Figure 18

[0365] In several embodiments, the prism PR is moved by a not-shown moving mechanism under the control from a control section described later. In this case, the function of the interpupillary distance adjustment section is realized by the control section and the not-shown moving mechanism. In several embodiments, the prism PR is manually moved by the not-shown moving mechanism. In this case, the function of the interpupillary distance adjustment section is realized by the not-shown moving mechanism.

[0366] Figure 19 An explanatory diagram showing an operation example of the convergence angle adjustment section in the ophthalmic apparatus la of the second embodiment. In Figure 19 , the same reference numerals are attached to the same parts as Figure 4 or Figure 16 ​Identical parts are labeled with the same reference numerals, and descriptions are omitted where appropriate.

[0367] The convergence angle adjustment unit, similar to the first embodiment, changes the orientation of at least one of the optical axes OL and OR by changing at least one of the orientations of the reflector ML1 and the reflector MR1.

[0368] For example, the deflecting surface of mirror ML1 is configured to rotate about a rotation axis extending along the Y-axis. Similarly, the deflecting surface of mirror MR1 is configured to rotate about a rotation axis extending along the Y-axis. Thus, as... Figure 19 As shown, the measuring optical axis OL, which is deflected by the reflector ML1, becomes the measuring optical axis OL′, and the measuring optical axis OR becomes the measuring optical axis OR′, thus changing the convergence angle.

[0369] In several embodiments, reflectors ML1 and MR1 are rotated via a moving mechanism (rotation mechanism) (not shown) under the control of a control unit described later. In this case, the function of the convergence angle adjustment unit is achieved by the control unit and the moving mechanism (not shown). In several embodiments, reflectors ML1 and MR1 are manually rotated via a moving mechanism (rotation mechanism) (not shown). In this case, the function of the convergence angle adjustment unit is achieved by the moving mechanism (not shown).

[0370] Figure 20 An example of the structure of the measuring optical system 300a according to the second embodiment is shown. Figure 20 and Figure 6 Similarly, a schematic example of the structure of the measuring optical system 300a is shown when viewed from the side (X direction). Figure 20 In the middle, to and Figure 6 or Figure 16 Identical parts are labeled with the same reference numerals, and descriptions are omitted where appropriate.

[0371] The difference between the structure of the measuring optical system 300a and the measuring optical system 300 is that a dichroic mirror 83, a reflector 84, and a fixed projection system 4 are arranged between the relay lens 82 and the relay lens 85, so that the optical path of the fixed projection system 4 and the optical path of the OCT optical system 8 are coaxially coupled through the dichroic mirror 83.

[0372] The dichroic mirror 83 allows light with wavelengths in the visible region to pass through, while reflecting light with wavelengths in the near-infrared (or infrared) region. A fixed-view projection system 4 is positioned in the transmission direction of the dichroic mirror 83, and an OCT optical system 8 is positioned in the reflection direction of the dichroic mirror 83. Specifically, the dichroic mirror 83 is positioned between the relay lens 82 and the fixed-view projection system 4, and a reflector 84 is positioned between the dichroic mirror 83 and the OCT optical system 8.

[0373] The fixation projection system 4 projects a fixation light beam to the fundus ELf of the left eye EL or the fundus ERf of the right eye ER, and presents a fixation target to the left eye EL or the right eye ER. The fixation projection system 4 includes a fixation unit 40 and relay lenses 43 and 44. The fixation unit 40 includes a liquid crystal panel 41 and a relay lens 42. The liquid crystal panel 41 displays a pattern representing a fixation target under the control of 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 of the control section.

[0374] The light from the liquid crystal panel 41 passes through the relay lenses 42, 43, and 44, and the dichroic mirror 83, and is projected to the eye along the same path as the measurement light LS from the OCT optical system 8.

[0375] In several embodiments, the fixation unit 40 can be independently moved in the optical axis direction with the relay lenses 43 and 44.

[0376] 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 11A 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 11B or the third adjustment example of Figure 11C In addition, in the fourth adjustment example in which the deflection direction of the optical axis of the OCT optical system 8 is changed by the optical member in the path of the measurement light, as examples of the optical member, the mirror 81, the dichroic mirror 52, the dichroic mirror 83, the mirror 84, and a mirror not shown can be used. Figure 20

[0377] The fixation projection system 4 is an example of the "fixation optical system" of the embodiments. The dichroic mirror 83 is an example of the "light path coupling member" of the embodiments. The deflection surface M1 of the prism PR is an example of the "first deflection member" of the embodiments. The mirror ML1 is an example of the "first reflection member" of the embodiments. The deflection surface M2 of the prism PR is an example of the "second deflection member" of the embodiments. The mirror MR1 is an example of the "second reflection member" of the embodiments. The convergence angle adjustment section is an example of the "first adjustment section" of the embodiments. The moving mechanism that rotates the deflection surface M1 of the prism PR or the mirror RML, the deflection surface M2 of the prism PR or the mirror RMR, 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 embodiments. ​

[0378] Figure 21 A functional configuration example of the processing system of the ophthalmic apparatus 1a of the second embodiment is shown. Figure 21 An example of a functional block diagram of the processing system of the ophthalmic apparatus 1a is shown. In Figure 21 The same components as Figure 12 or Figure 20 the same reference numerals are attached to the same parts, and the explanation is omitted as appropriate.

[0379] The structure of the processing system of the ophthalmic apparatus 1a is different from that of the ophthalmic apparatus 1 shown 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. Figure 12

[0380] The structure of the processing section 9a is different from that of the processing section 9 shown in that the control section 210a is provided instead of the control section 210. The control section 210a includes a main control section 211a and a 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. Figure 12

[0381] The operation of the ophthalmic apparatus 1a of the second embodiment is substantially the same as that of the ophthalmic apparatus 1 of the first embodiment shown in Figure 14 and Figure 15 except for the control of the fixation projection system 4.

[0382] In the second embodiment, the same fixation target is presented to both eyes in the reflection measurement, the corneal measurement, and the OCT measurement. That is, the reflection measurement and the corneal measurement can be performed simultaneously for both eyes in a state in which the same fixation target is presented to both eyes in a state in which both eyes are open. In addition, the OCT measurement can be performed sequentially for each eye in a state in which the same fixation target is presented to both eyes in a state in which both eyes are open.

[0383] Specifically, instead of the control by the main control section 211 to present the fixation target independently to the left and right examination eyes EL, ER by the fixation projection systems 4L, 4R, the main control section 211a controls the fixation projection system 4 so that the same fixation target is presented to the left and right examination eyes EL, ER.

[0384] For example, in the case where the examination is performed in a state in which the fixation target is seen far away in step S7 of Figure 14 Figure 14 ​​​The temporary spherical power S and the temporary astigmatism C (or the equivalent spherical power) of the left eye EL and the temporary spherical power S and the temporary astigmatism C (or the equivalent spherical power) of the right eye ER, which correspond to the temporary spherical power S and the temporary astigmatism C (or the equivalent spherical power) of the more negative side (the near side), are determined in step S5.

[0385] For example, in the case where the examination is performed in the state of near vision in step S7, the main control section 211a presents the fixation target to both eyes from the same position as in the case where the examination is performed in the state of far vision. 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 position where the examinee is monovision in the case where the examination is performed in the state of far vision. Figure 14 Figure 14 The temporary spherical power S and the temporary astigmatism C (or the equivalent spherical power) of the left eye EL and the temporary spherical power S and the temporary astigmatism C (or the equivalent spherical power) of the right eye ER, which correspond to the temporary spherical power S and the temporary astigmatism C (or the equivalent spherical power) of the more negative side (the near side), are determined in step S5. At this time, the main control section 211a can adjust the convergence angle as needed by controlling the mirrors ML1, MR1.

[0386] Further, the main control section 211a can determine whether the arrangement directions of the left eye EL and the right eye ER are parallel to the X direction (i.e., whether the heights of both eyes are shifted) on the basis of the pupil positions of both eyes specified in step S21, as in step S22. Figure 15 The main control section 211a can change the deflection directions of the mirrors ML1, MR1, the orientations of the reflecting surfaces of the prisms PR or the deflection surface M1, and the orientations of the reflecting surfaces of the prisms PR or the deflection surface M2 on the basis of the pupil positions of both eyes specified in step S21, as a second adjustment section, thereby adjusting the arrangement directions of the measurement optical axes OL, OR.

[0387] In several embodiments, in the structure of the second embodiment, a binocular single vision field or a trial lens can also be provided in front of both eyes.

[0388] As described above, according to the second embodiment, as in the first embodiment, an ophthalmic apparatus which is low in cost and saves space and can measure the characteristics of both eyes with high precision can be provided. In particular, the miniaturization and the low cost of the optical system of the ophthalmic apparatus which can perform OCT measurement on both eyes can be achieved. In addition, the refractive power measurement is performed via the objective lenses through which the measurement optical axes OL, OR pass, and thus the refractive power measurement can also be performed simultaneously in the open state of both eyes.

[0389] [Third Embodiment] ​

[0390] In the first embodiment, the case where the fixation projection systems 4L, 4R are provided in the transmission direction 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 arranged in the transmission direction of the dichroic mirrors ML, MR.

[0391] 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.

[0392] Figure 22 An example of the structure of the optical system of the ophthalmic apparatus of the third embodiment is shown. Figure 22 With Figure 1 Likewise, the structure of the optical system of the ophthalmic apparatus of the third embodiment is schematically shown when viewed from above.

[0393] 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 a fixation target prompting section 400 is provided instead of the fixation projection systems 4L, 4R.

[0394] The fixation target prompting section 400 includes a fixation target chart. For example, the fixation target chart is arranged between the light source for illumination and the eye under examination, 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. As examples of the fixation target, a landscape, a point target, and the like are included.

[0395] The control section illuminates the fixation target chart with light from the light source for illumination when performing the reflection measurement. The light that has transmitted the fixation target chart transmits the dichroic mirrors ML, MR as fixation light, and is projected to the left eye under examination EL and the right eye under examination ER.

[0396] The deflection surface M1 of the prism PR is an example of the "first deflection member" of the embodiment. The dichroic mirror ML is an example of the "first optical path coupling member" of the embodiment. The deflection surface M2 of the prism PR is an example of the "second deflection member" of the embodiment. The dichroic mirror MR is an example of the "second optical path coupling member" of the embodiment.

[0397] Figure 23 An example of the functional structure of the processing system of the ophthalmic apparatus 1b of the third embodiment is shown. Figure 23 An example of the functional block diagram of the processing system of the ophthalmic apparatus 1b is shown. In Figure 23 the same parts are attached with the same reference numerals, and the description is appropriately omitted. Figure 12 or Figure 22 the same parts are attached with the same reference numerals, and the description is appropriately omitted.

[0398] The structure of the processing system of the ophthalmic apparatus 1b differs from that of the ophthalmic apparatus 1 of the first embodiment in that the fixation target prompting section 400 is provided instead of the fixation projection systems 4L, 4R. Figure 12The structure of the processing system of the ophthalmic apparatus 1 shown differs in that the fixation projection systems 4L, 4R are omitted, and a processing section 9b is provided instead of the processing section 9.

[0399] The structure of the processing section 9b is the same as that of the processing section 9 except that the control section 210 is omitted. Figure 12 The structure of the processing section 9 shown differs in that a control section 210b is provided instead of the control section 210. The control section 210b includes a main control section 211b and a storage section 212b. The main control section 211b is able to 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 that the processing of the control of the fixation projection systems 4L, 4R is not executed.

[0400] The operation of the ophthalmic apparatus 1b of the third embodiment is the same as that of the ophthalmic apparatus 1 of the first embodiment except that the control of the fixation projection systems 4L, 4R is omitted. Figure 14 and Figure 15 The operation of the ophthalmic apparatus 1 of the first embodiment shown is substantially the same.

[0401] In the third embodiment, the same fixation target is presented to both eyes in the reflection measurement, the corneal measurement, and the OCT measurement. That is, the reflection measurement and the corneal measurement can be performed simultaneously on both eyes in a state in which the same fixation target is presented to both eyes in an open-eye state. In addition, the OCT measurement can be performed sequentially on each eye in a state in which the same fixation target is presented to both eyes in an open-eye state.

[0402] In the several embodiments, the target presentation section 400 presents the target by the operation of the examiner. In the several embodiments, the target presentation section 400 presents the target under the control from the main control section 211b. In this case, the main control section 211b controls the target presentation section 400 similarly to the control of the fixation projection system 4 of the second embodiment.

[0403] In the 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 both eyes.

[0404] 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 is able to measure the characteristics of both eyes with high precision can be provided. In particular, miniaturization and cost reduction of the optical system of an ophthalmic apparatus that is able to perform the OCT measurement on both eyes can be achieved. In addition, the refractive power measurement is performed via the objective lenses through which the optical axes OL, OR pass, so that the refractive power measurement can also be performed simultaneously in an open-eye state.

[0405] [Effects]

[0406] An ophthalmic apparatus of an embodiment is explained.

[0407] The ophthalmic apparatus (1, la, lb) of the first aspect of the embodiment includes an objective lens (51), an OCT optical system (8), an optical axis adjustment section (adjustment Figure 11A to Figure 11C The optical axis of the OCT optical system 8 illustrated in any one of the aspects is adjusted by the components and mechanisms, the control section (210, 210a, 210b, the main control section 211, 211a, 211b), and the intraocular parameter calculation section (data processing section 223). The first measurement optical axis (measurement optical axis OL) and the second measurement optical axis (measurement optical axis OR) that are arranged separately from each other pass through the objective lens. 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) arranged on the first measurement optical axis or a right eye (ER) arranged on the second measurement optical axis 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 the reference light path. The optical axis adjustment section adjusts the optical axis of the OCT optical system. The control section controls the optical axis adjustment section so as to be substantially coincident with any one of the first measurement optical axis and the second measurement optical axis. 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 in which the optical axis of the OCT optical system is adjusted to be substantially coincident 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 in which the optical axis of the OCT optical system is adjusted to be substantially coincident with the second measurement optical axis.

[0408] According to this aspect, the optical axis of the OCT optical system that performs OCT measurement via the objective lens through which the first measurement optical axis and the second measurement optical axis that are arranged separately from each other pass is adjusted to be substantially coincident with any one of the first measurement optical axis and the second measurement optical axis. Thus, it is possible to sequentially perform OCT measurement on both eyes in a state in which both eyes are open. Accordingly, it is possible to provide an ophthalmic apparatus that is low in cost, saves space, and is capable of measuring the characteristics of both eyes with high accuracy.

[0409] In the second aspect of the embodiment, in the first aspect, before performing OCT measurement using measurement light on one of the left eye and the right eye, the control section controls the OCT optical system so as 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 and the right eye.

[0410] According to this aspect, it is possible to set a measurement environment estimated from the measurement environment of one of the eyes before performing OCT measurement on the other eye, and thus it is possible to shorten the time required for OCT measurement.

[0411] The third aspect of the embodiment includes, in the first aspect or the second aspect: a first fixation optical system (fixation projection system 4L) that projects a first fixation light beam; a first deflection member (prism PR or mirror RML) that deflects an optical path of the measurement light; a first optical path coupling member (dichroic mirror ML) that optically couples the optical path of the measurement light deflected by the first deflection member and the optical path of the first fixation light beam; a second fixation optical system (fixation projection system 4R) that projects a second fixation light beam; a second deflection member (prism PR or mirror RMR) that deflects the optical path of the measurement light; and a second optical path coupling member (dichroic mirror MR) that optically couples the optical path of the measurement light deflected by the second deflection member and the optical path of the second fixation light beam.

[0412] According to this aspect, it is possible to perform OCT measurement in a binocular open state while independently presenting fixation targets to the left and right eyes, respectively, with a simple structure.

[0413] The fourth aspect of the embodiment includes, in the first aspect or the second aspect: a fixation optical system (4) that projects a fixation light beam; an optical path coupling member (dichroic mirror 83) that optically couples the optical path of the fixation light beam and the optical path of the measurement light and guides the fixation light beam to the objective lens; a first deflection member (deflection surface M1 of prism PR) that deflects the optical path of the measurement light; a first reflection member (mirror ML1) that deflects the optical path of the measurement light deflected by the first deflection member toward the left eye; a second deflection member (deflection surface M2 of prism PR) that deflects the optical path of the measurement light; and a second reflection member (mirror MR1) that deflects the optical path of the measurement light deflected by the second deflection member toward the right eye.

[0414] According to this aspect, it is possible to perform OCT measurement in a binocular open state while presenting the same fixation target to both eyes using a fixation projection system common to both eyes.

[0415] The fifth aspect of the embodiment includes, in the first aspect or the second aspect: a first deflection member (deflection surface M1 of prism PR) that deflects the optical path of the measurement light; a first optical path coupling member (dichroic mirror ML) that deflects the optical path of the measurement light deflected by the first deflection member toward the left eye while making the first fixation light beam from the transmission direction transmit and be guided to the left eye; a second deflection member (deflection surface M2 of prism PR) that deflects the optical path of the measurement light; and a second optical path coupling member (dichroic mirror MR) that deflects the optical path of the measurement light deflected by the second deflection member toward the right eye while making the second fixation light beam from the transmission direction transmit and be guided to the right eye.

[0416] According to this aspect, it is possible to perform OCT measurement in a binocular open state while presenting the same fixation target to both eyes by arranging a fixation projection system common to both eyes outside the device.

[0417] The sixth aspect of the embodiment includes, in the third aspect or the fifth aspect, a first adjustment section (a convergence angle adjustment section, a moving mechanism that rotates the dichroic mirror ML, MR), which changes the orientation of the optical path coupling surface of the first optical path coupling member and the orientation of the optical path coupling surface of the second optical path coupling member, thereby changing the orientation of the first measurement optical axis and the orientation of the second measurement optical axis.

[0418] According to this aspect, the OCT measurement can be performed with the convergence angle adjusted and with the eyes open in a simple configuration.

[0419] The seventh aspect of the embodiment includes, in the third aspect, the fifth aspect, or the sixth aspect, a second adjustment section (a height adjustment section, a moving mechanism that rotates the deflection surface M1 of the prism PR or the mirror RML, the deflection surface M2 of the prism PR or the mirror RMR, the deflection surface of the dichroic mirror ML, and the deflection surface of the dichroic mirror MR), which adjusts the arrangement direction of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the first deflection member, the deflection direction of the second deflection member, the orientation of the optical path coupling surface of the first optical path coupling member, and the orientation of the optical path coupling surface of the second optical path coupling member.

[0420] According to this aspect, 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 and right eyes in a simple configuration 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 and right eyes.

[0421] The eighth aspect of the embodiment includes, in the fourth aspect, a first adjustment section (a convergence angle adjustment section, a moving mechanism that rotates the mirror ML1, MR1), which changes the orientation of the reflection surface of the first reflection member and the orientation of the reflection surface of the second reflection member, thereby changing the orientation of the first measurement optical axis and the orientation of the second measurement optical axis.

[0422] According to this aspect, the OCT measurement can be performed with the convergence angle adjusted and with the eyes open in a simple configuration.

[0423] The ninth aspect of the embodiment includes, in the fourth aspect or the eighth aspect, a second adjustment section (a height adjustment section, a moving mechanism that rotates the deflection surface M1 of the prism PR or the mirror RML, the deflection surface M2 of the prism PR or the mirror RMR, the deflection surface of the mirror ML1, and the deflection surface of the mirror MR1), which adjusts the arrangement direction of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the first deflection member, the deflection direction of the second deflection member, the orientation of the reflection surface of the first reflection member, and the orientation of the reflection surface of the second reflection member.

[0424] According to this aspect, 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 to be examined and the right eye to be examined, the arrangement directions of the first measurement optical axis and the second measurement optical axis can be made to coincide with the arrangement directions of the left eye to be examined and the right eye to be examined with a simple structure.

[0425] 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, movement mechanism 310) that changes the distance between the first measurement optical axis and the second measurement optical axis by moving the first deflection member and the second deflection member along the first measurement optical axis or the second measurement optical axis.

[0426] According to this aspect, the first measurement optical axis and the second measurement optical axis can be matched to the interpupillary distance of the subject with a simple structure.

[0427] The eleventh aspect of the embodiment includes, in any one of the third aspect to the tenth aspect, a prism (PR) that has a first deflection surface (deflection surface M1) as the first deflection member and a second deflection surface (deflection surface M2) as the second deflection member.

[0428] According to this aspect, the first measurement optical axis and the second measurement optical axis can be made to respectively enter the left eye to be examined and the right eye to be examined with a simple structure, and OCT measurement can be performed on both eyes in a state where both eyes are open.

[0429] In the twelfth aspect of the embodiment, in any one of the third aspect to the eleventh aspect, the optical axis adjustment section adjusts the optical axis of the OCT optical system by moving the first deflection member and the second deflection member along the first measurement optical axis or the second measurement optical axis.

[0430] According to this aspect, the optical axis of the OCT optical system can be made to substantially coincide with the first measurement optical axis or the second measurement optical axis with a simple structure and control.

[0431] The thirteenth aspect of the embodiment includes, in any one of the first aspect to the twelfth aspect, two or more photographing sections (anterior eye portion cameras 15LA, 15LB, 15RA, 15RB) that photograph the anterior eye portions of the left eye to be examined and the right eye to be examined from different directions from each other, and a movement mechanism (200) that three-dimensionally moves at least the OCT optical system. The control section changes the relative positions of the OCT optical system with respect to the left eye to be examined and the right eye to be examined while changing the directions of the first measurement optical axis and the second measurement optical axis and the distance between the first measurement optical axis and the second measurement optical axis 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 two or more images obtained by the two or more photographing sections.

[0432] According to this aspect, the position alignment of the ophthalmic apparatus capable of performing OCT measurement of both eyes in a state where both eyes are open can be performed with a simple structure in a wide dynamic range.

[0433] In a fourteenth aspect of the embodiments, in the thirteenth aspect, the two or more photographing sections include: a first photographing section (an anterior eye portion camera 15LA) that photographs an anterior eye portion of the left eye to be examined; a second photographing section (an anterior eye portion camera 15LR) that photographs the anterior eye portion of the left eye to be examined and an anterior eye portion of the right eye to be examined; and a third photographing section (an anterior eye portion camera 15RA) that photographs the anterior eye portion of the right eye to be examined.

[0434] According to this aspect, the number of anterior eye portion cameras can be reduced, and the OCT measurement of both eyes in a state where both eyes are open can be performed at a lower cost.

[0435] In a fifteenth aspect of the embodiments, in any one of the first aspect to the fourteenth aspect, the OCT optical system includes an optical member (a mirror 81, a dichroic mirror 52, a dichroic mirror 83, a mirror 84, and a mirror not shown) that deflects an optical axis of the OCT optical system. The optical axis adjustment section adjusts the optical axis of the OCT optical system by changing a deflection direction of the optical axis deflected by the optical member based on an interpupillary distance of the examinee.

[0436] According to this aspect, the optical axis of the OCT optical system can be made to substantially coincide with the first measurement optical axis or the second measurement optical axis with a simple structure and control.

[0437] In a sixteenth aspect of the embodiments, in any one of the first aspect to the fifteenth aspect, the optical axis adjustment section adjusts the optical axis of the OCT optical system by moving a position of the optical axis of the OCT optical system based on an interpupillary distance of the examinee.

[0438] According to this aspect, the optical axis of the OCT optical system can be made to substantially coincide with the first measurement optical axis or the second measurement optical axis with a simple structure and control.

[0439] A seventeenth aspect of the embodiments includes, in any one of the first aspect to the sixteenth aspect, a refractive power measurement optical system (a retinal measurement projection system 6L, 6R and a retinal measurement light receiving system 7) and an eye refractive power calculation section (221). The refractive power measurement optical system projects the first measurement pattern light along the first measurement optical axis to the left eye to be examined and the second measurement pattern light 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 from the left eye to be examined and return light of the second measurement pattern light from the right eye to be examined. The eye refractive power calculation section calculates the refractive power of the left eye to be examined based on a light receiving result of the return light of the first measurement pattern light, and calculates the refractive power of the right eye to be examined based on a light receiving result of the return light of the second measurement pattern light.

[0440] According to this manner, the diopter measurement can be performed on both eyes simultaneously in the state where both eyes are open.

[0441] In the eighteenth aspect of the embodiment, in the seventeenth aspect, the diopter measurement optical system projects the first measurement pattern light flux and the second measurement pattern light flux so that a position corresponding to an intermediate power between the diopter of the left eye to be examined and the diopter of the right eye to be examined becomes a focal position.

[0442] According to this manner, the diopter measurement can be performed on both eyes simultaneously even in the case where the diopters of both eyes are different.

[0443] In the nineteenth aspect of the embodiment, in the seventeenth aspect or the eighteenth aspect, the diopter measurement optical system includes: a first projection system (retro-illumination measurement projection system 6L) that projects the first measurement pattern light flux to the left eye to be examined; a second projection system (retro-illumination measurement projection system 6R) that projects the second measurement pattern light flux to the right eye to be examined; and a light receiving system (retro-illumination measurement light receiving system) that receives the return light of the first measurement pattern light flux and the return light of the second measurement pattern light flux.

[0444] According to this manner, the diopter measurement can be performed on both eyes with high accuracy while suppressing the size of the diopter measurement optical system to be as small as possible.

[0445] <Others>

[0446] The above-described embodiment is merely one example for implementing the present application. Any modification, omission, addition, and the like can be made by a person who implements the present application within the scope of the present application.

[0447] 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 anterior eye segment.

[0448] In addition, in the above-described embodiment, the prism PR bends the optical axis in the XZ plane, but the structure of the embodiment is not limited thereto. For example, the prism PR can also be configured to bend the optical axis in the Y direction (upward direction or 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 through which a first measurement optical axis and a second measurement optical axis arranged apart from each other pass; 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 the first measurement optical axis or a right eye to be examined arranged on the second measurement optical axis via the objective lens, 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 the reference light via a reference light path; an optical axis adjustment section that adjusts an optical axis of the OCT optical system; a control section that controls the optical axis adjustment section so as to cause either of the first measurement optical axis and the second measurement optical axis to substantially coincide; 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 in which the optical axis of the OCT optical system is adjusted 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 in which the optical axis of the OCT optical system is adjusted to substantially coincide with the second measurement optical axis, the control section controlling 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 to be examined and the right eye to be examined before performing OCT measurement using the measurement light on one of the left eye to be examined and the right eye to be examined.

2. The ophthalmic apparatus according to claim 1, characterized in that the ophthalmic apparatus comprises: a first fixation optical system that projects a first fixation light beam; a first deflection section that deflects a light path of the measurement light; a first light path coupling section that optically couples the light path of the measurement light deflected by the first deflection section and a light path of the first fixation light beam; a second fixation optical system that projects a second fixation light beam; a second deflection section that deflects a light path of the measurement light; and a second light path coupling section that optically couples the light path of the measurement light deflected by the second deflection section and a light path of the second fixation light beam.

3. The ophthalmic apparatus according to claim 1, characterized in that the ophthalmic apparatus comprises: a fixation optical system that projects a fixation light beam; a light path coupling section that optically couples a light path of the fixation light beam and a light path of the measurement light, and guides the fixation light beam to the objective lens; a first deflection section that deflects a light path of the measurement light; a first reflection section that deflects the light path of the measurement light deflected by the first deflection section toward the left eye to be examined; a second deflection section that deflects a light path of the measurement light; and a second reflection section that deflects the light path of the measurement light deflected by the second deflection section toward the right eye to be examined.

4. The ophthalmic apparatus according to claim 1, characterized in that the ophthalmic apparatus comprises: a first deflection section that deflects a light path of the measurement light; a first light path coupling section that deflects the light path of the measurement light deflected by the first deflection section toward the left eye to be examined, while causing a first fixation light beam from a transmissive direction to be transmitted and guided to the left eye to be examined. a second deflection member that deflects an optical path of the measurement light; and a second optical path coupling member that deflects the optical path of the measurement light deflected by the second deflection 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 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 directions of the first deflection member and the second deflection 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.

7. 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.

8. The ophthalmic apparatus according to claim 3, 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 directions of the first deflection member and the second deflection member, the orientations of the reflecting surfaces of the first reflecting member, and the orientations of the reflecting surfaces of the second reflecting member.

9. 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 first deflection member and the second deflection member along the first measurement optical axis or the second measurement optical axis.

10. The ophthalmic apparatus according to claim 2, wherein the ophthalmic apparatus includes: a prism that has a first deflection surface as the first deflection member and a second deflection surface as the second deflection member.

11. The ophthalmic apparatus according to claim 2, wherein the optical axis adjustment section adjusts the optical axis of the OCT optical system by moving the first deflection member and the second deflection member along the first measurement optical axis or the second measurement optical axis.

12. 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 eye under examination and the right eye under examination 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 under test based on two or more images obtained by the two or more imaging sections, 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 under test and the second measurement optical axis coincides with the visual axis of the right eye under test.

13. The ophthalmic apparatus according to claim 12, wherein the two or more imaging sections include: a first imaging section that images the anterior eye portion of the left eye under test; a second imaging section that images the anterior eye portion of the left eye under test and the anterior eye portion of the right eye under test; and a third imaging section that images the anterior eye portion of the right eye under test.

14. The ophthalmic apparatus according to claim 1, wherein the OCT optical system includes an optical member that deflects an optical axis of the OCT optical system, the optical axis adjustment section adjusts the optical axis of the OCT optical system by changing a deflection direction of the optical axis deflected by the optical member based on the interpupillary distance of the subject.

15. The ophthalmic apparatus according to claim 1, wherein the optical axis adjustment section adjusts the optical axis of the OCT optical system by moving a position of the optical axis of the OCT optical system based on the interpupillary distance of the subject.

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 under test via the objective lens, while projecting a second measurement pattern light beam along the second measurement optical axis to the right eye under test, and receives return light of the first measurement pattern light beam from the left eye under test and return light of the second measurement pattern light beam from the right eye under test; and an eye refractive power calculation section that calculates a refractive power of the left eye under test based on a light reception result of the return light of the first measurement pattern light beam, and calculates a refractive power of the right eye under test based on a light reception 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 power between the refractive power of the left eye under test and the refractive power of the right eye under test becomes a focal position.

18. The ophthalmic apparatus according to claim 16, wherein the refractive power measurement optical system includes: a first projection system that projects the first measurement pattern light beam to the left eye under test; a second projection system that projects the second measurement pattern light beam to the right eye under test; and a light reception system that receives return light of the first measurement pattern light beam and return light of the second measurement pattern light beam.

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