Ophthalmologic apparatus

Abstract

To accurately measure characteristics of both eyes at a lower cost in a saved space.SOLUTION: An ophthalmologic apparatus includes: a measurement optical system, an optical axis changeover member, a control section, and an intraocular parameter calculation section. The measurement optical system includes an objective lens and an OCT optical system. The OCT optical system performs: projecting measurement light to a left subject eye placed on a first measurement optical axis or a right subject eye placed on a second measurement optical axis via the objective lens; and detecting interference light between return light of the measurement light from the left subject eye or the right subject eye by way of the objective lens and reference light by way of a reference light path. The optical axis changeover member changes over the optical axis of the OCT optical system to be nearly coincident with the first measurement optical axis or the second measurement optical axis. The control section controls the optical axis changeover member. The intraocular parameter calculation section calculates an intraocular parameter of the left subject eye or the right subject eye based on a detection result of the interference light which is obtained in a state where the optical axis of the OCT optical system is changed over to be nearly coincident with the first measurement optical axis or the second measurement optical axis.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The present invention relates to an ophthalmic apparatus. [Background technology]

[0002] Ophthalmic devices capable of performing multiple tests and measurements on a subject's eye are known. Tests and measurements on a subject's eye include subjective tests and objective measurements. Subjective tests obtain results based on responses from the subject. Objective measurements obtain information about the subject's eye primarily using physical methods without reference to responses from the subject.

[0003] For example, Patent Document 1 discloses an ophthalmic apparatus capable of subjective examination and objective measurement. This ophthalmic apparatus can perform objective measurements such as refractive power measurement, corneal shape measurement, and imaging and measurement using optical coherence tomography. This ophthalmic apparatus is equipped with an optical system common to both the left and right eyes, and can use this optical system to perform subjective examination and objective measurement on one of the left and right eyes.

[0004] Furthermore, for example, Patent Document 2 discloses an ophthalmic device that can perform refractive power measurement for one of the left and right eyes using a single optical system while presenting fixation targets independently to each of the left and right eyes.

[0005] In response to this, for example, Patent Document 3 discloses an ophthalmic device that has two optical systems independently installed for the left and right eyes, and that can simultaneously perform refractive power measurement and corneal shape measurement for the left and right eyes using the two optical systems.

[0006] Furthermore, for example, Patent Document 4 discloses an ophthalmic apparatus that can simultaneously acquire Hartmann images of the left and right eyes and simultaneously measure the wavefront aberrations of the left and right eyes. [Prior art documents] [Patent documents]

[0007] [Patent Document 1] Japanese Patent Application Laid-Open No. 2016-187461 [Patent Document 2] Japanese Patent Application Publication No. 06-304139 [Patent Document 3] Japanese Patent Application Publication No. 2019-062939 [Patent Document 4] U.S. Patent No. 8,506,079 Summary of the Invention [Problem to be solved by the invention]

[0008] However, the configurations disclosed in Patent Documents 1 and 2 measure each eye separately, and are unable to measure the characteristics of both eyes with both eyes open. In contrast, the configuration disclosed in Patent Document 3 is capable of measuring both eyes simultaneously with both eyes open, but this results in an increase in the size and cost of the device. Furthermore, the configuration disclosed in Patent Document 4 may result in an increase in the size of the device when performing measurements other than wavefront aberration measurement, or may result in an inability to perform measurements other than wavefront aberration measurement in an optimal state, resulting in a decrease in measurement accuracy.

[0009] The present invention has been made in view of the above circumstances, and one of its objectives is to provide a new technology that is low-cost, space-saving, and capable of measuring the characteristics of both eyes with high accuracy. [Means for solving the problem]

[0010] One aspect of the embodiment is an ophthalmologic apparatus including: a measurement optical system including an objective lens; an OCT optical system that splits light from a light source into measurement light and reference light, projects the measurement light via the objective lens onto a left eye to be examined that is positioned on a first measurement optical axis or a right eye to be examined that is positioned on a second measurement optical axis, and detects interference light between return light of the measurement light from the left eye to be examined or the right eye to be examined that has passed through the objective lens and the reference light that has passed through a reference optical path; an optical axis switching member that switches the optical axis of the measurement optical system to approximately coincide with either the first measurement optical axis or the second measurement optical axis; a control unit that controls the optical axis switching member; and an intraocular parameter calculation unit that calculates intraocular parameters of the left eye to be examined based on detection results of the interference light obtained when the optical axis of the measurement optical system is switched to approximately coincide with the first measurement optical axis, and calculates intraocular parameters of the right eye to be examined based on detection results of the interference light obtained when the optical axis of the measurement optical system is switched to approximately coincide with the second measurement optical axis. [Effects of the Invention]

[0011] According to the present invention, it is possible to provide a new technology that is low-cost, space-saving, and capable of measuring the characteristics of both eyes with high accuracy. [Brief explanation of the drawings]

[0012] [Figure 1] 1 is a schematic diagram illustrating an example of the configuration of an optical system of an ophthalmic apparatus according to a first embodiment. [Figure 2] 1 is a schematic diagram illustrating an example of the configuration of an optical system of an ophthalmic apparatus according to a first embodiment. [Figure 3] 1 is a schematic diagram for explaining an optical system of an ophthalmologic apparatus according to a first embodiment. [Figure 4] 1 is a schematic diagram for explaining an optical system of an ophthalmologic apparatus according to a first embodiment. [Figure 5] 1 is a schematic diagram illustrating an example of the configuration of an optical system of an ophthalmic apparatus according to a first embodiment. [Figure 6] 1 is a schematic diagram illustrating an example of the configuration of an optical system of an ophthalmic apparatus according to a first embodiment. [Figure 7]1 is a schematic diagram for explaining an optical system of an ophthalmologic apparatus according to a first embodiment. [Figure 8] 1 is a schematic diagram for explaining an optical system of an ophthalmologic apparatus according to a first embodiment. [Figure 9A] 1 is a schematic diagram for explaining an optical system of an ophthalmologic apparatus according to a first embodiment. [Figure 9B] 1 is a schematic diagram for explaining an optical system of an ophthalmologic apparatus according to a first embodiment. [Figure 10] 2 is a schematic diagram illustrating an example of the configuration of a processing system of the ophthalmologic apparatus according to the first embodiment. FIG. [Figure 11] 2 is a schematic diagram illustrating an example of the configuration of a processing system of the ophthalmologic apparatus according to the first embodiment. FIG. [Figure 12] FIG. 2 is a schematic diagram showing a flow of an example of operation of the ophthalmologic apparatus according to the first embodiment. [Figure 13] FIG. 2 is a schematic diagram showing a flow of an example of operation of the ophthalmologic apparatus according to the first embodiment. [Figure 14] FIG. 10 is a schematic diagram illustrating an example of the configuration of an optical system of an ophthalmic apparatus according to a second embodiment. [Figure 15] FIG. 10 is a schematic diagram illustrating an example of the configuration of an optical system of an ophthalmic apparatus according to a second embodiment. [Figure 16] FIG. 10 is a schematic diagram for explaining an optical system of an ophthalmologic apparatus according to a second embodiment. [Figure 17] FIG. 10 is a schematic diagram for explaining an optical system of an ophthalmologic apparatus according to a second embodiment. [Figure 18] FIG. 10 is a schematic diagram illustrating an example of the configuration of an optical system of an ophthalmic apparatus according to a second embodiment. [Figure 19] FIG. 10 is a schematic diagram illustrating an example of the configuration of a processing system of an ophthalmologic apparatus according to a second embodiment. [Figure 20] FIG. 10 is a schematic diagram showing an example of the configuration of an optical system of an ophthalmic apparatus according to a third embodiment. [Figure 21] FIG. 11 is a schematic diagram illustrating an example of the configuration of a processing system of an ophthalmologic apparatus according to a third embodiment. DETAILED DESCRIPTION OF THE INVENTION

[0013] An example of an embodiment of an ophthalmic device according to the present invention will be described in detail with reference to the drawings. Note that the contents of documents cited in this specification and any publicly known techniques can be incorporated into the following embodiments.

[0014] The ophthalmic apparatus according to the embodiment is capable of sequentially performing predetermined examinations and measurements on both eyes with both eyes open while sharing an objective lens among multiple optical systems for performing multiple measurements of different measurement types. In particular, the ophthalmic apparatus according to the embodiment is capable of sequentially performing OCT measurements on both eyes using a single OCT optical system and calculating intraocular parameters for each of the eyes. Sharing the OCT optical system and objective lens for OCT measurements on both eyes allows for a smaller device and lower costs.

[0015] In some embodiments, the ophthalmic apparatus further includes at least one of an objective measurement optical system for performing objective measurements other than OCT measurement and a subjective test optical system for performing subjective tests. In such an ophthalmic apparatus, the objective lens can be shared among multiple optical systems corresponding to the types of tests and measurements, thereby making the apparatus smaller and less expensive.

[0016] Objective measurement is a measurement technique that acquires information about the subject's eye primarily using physical techniques without reference to responses from the subject. Objective measurement includes measurement for acquiring characteristics of the subject's eye and photography for acquiring images of the subject's eye. Other objective measurements include intraocular pressure measurement, fundus photography, etc. In some embodiments, the ophthalmic device is capable of performing refractive power measurement (REF measurement) and OCT measurement as objective measurements. In some embodiments, the ophthalmic device is capable of performing refractive power measurement, corneal topography measurement, and OCT measurement as objective measurements.

[0017] The following describes a case where an ophthalmic apparatus according to an embodiment performs OCT measurement on the anterior segment of the eye or the fundus. In the following embodiments, a case where a spectral domain type OCT technique is used will be described in particular detail. However, the configuration according to the embodiment can also be applied to an ophthalmic apparatus that uses other types of OCT (for example, swept source type, time domain type).

[0018] Subjective tests are measurement techniques that obtain information from the subject's responses. Subjective tests include subjective refraction measurements such as distance tests, near tests, contrast tests, and glare tests, as well as visual field tests.

[0019] Hereinafter, the fundus conjugate position is a position that is approximately optically conjugate with the fundus of the subject's eye after alignment is complete, and refers to a position that is optically conjugate with the fundus of the subject's eye or a position near the fundus. Similarly, the pupil conjugate position is a position that is approximately optically conjugate with the pupil of the subject's eye after alignment is complete, and refers to a position that is optically conjugate with the pupil of the subject's eye or a position near the pupil.

[0020] In the following embodiments, the horizontal direction (left-right direction) perpendicular to the optical axis of the optical system is defined as the X direction, the vertical direction (up-down direction) perpendicular to the optical axis of the optical system is defined as the Y direction, and the optical axis direction of the optical system (front-back direction) is defined as the Z direction.

[0021] [First embodiment] <Optical system configuration> 1 and 2 show an example of the configuration of the optical system of the ophthalmic apparatus according to the first embodiment. Fig. 1 is a schematic diagram of the configuration of the optical system of the ophthalmic apparatus according to the first embodiment as viewed from above. Fig. 2 is a block diagram of an example of the configuration of the measurement optical system 300 of Fig. 1.

[0022] The ophthalmologic apparatus 1 according to the first embodiment includes a measurement optical system 300, dichroic mirrors ML and MR, an optical axis switching member SW, a fixation projection system 4L, and a fixation projection system 4R. The measurement optical system 300 may include dichroic mirrors ML and MR, an optical axis switching member SW, a fixation projection system 4L, and a fixation projection system 4R.

[0023] (Measurement optical system 300) The measurement optical system 300 includes an objective lens (not shown) and an optical system for measuring the left eye EL, which is the left eye of the subject, and the right eye ER, which is the right eye, via the objective lens. When performing measurement using the above optical system, one of measurement optical axes OL and OR, which are spaced apart from each other, passes through the objective lens. The measurement optical axis adjusted to approximately coincide with the optical axis of the measurement optical system 300 (the optical axis of the OCT optical system 8). The left eye EL is positioned on the measurement optical axis OL. The right eye ER is positioned on the measurement optical axis OR.

[0024] As shown in FIG. 2, the measurement optical system 300 includes, in addition to the objective lens, a keratometry system 3, an anterior segment observation system 5, a reflex measurement projection system 6, a reflex measurement light receiving system 7, and an OCT optical system 8.

[0025] The keratometry system 3 is an optical system for measuring information representing the shape of the cornea CLr of the left eye EL and information representing the shape of the cornea CRr of the right eye ER. The keratometry system 3 is configured to project light for corneal shape measurement onto the eye to be measured without passing through the objective lens and to receive return light of the light for corneal shape measurement.

[0026] The anterior eye observation system 5 is configured to illuminate either the anterior eye of the left eye EL or the anterior eye of the right eye ER, and to receive the return light of the illumination light via an objective lens.

[0027] The reflex measurement projection system 6 projects light for reflex measurement onto either the left test eye EL or the right test eye ER via an objective lens, and projects a measurement pattern (ring pattern) centered on the measurement optical axis OL or the measurement optical axis OR onto the fundus ELf or the fundus ERf.

[0028] The refraction measurement light receiving system 7 is configured to receive the return light from the fundus ELf or ERf via an objective lens.

[0029] The OCT optical system 8 splits the light from the OCT light source into measurement light and reference light, projects the measurement light via an objective lens onto either the left test eye EL positioned on the measurement optical axis OL or the right test eye ER positioned on the measurement optical axis OR, and detects the interference light between the return light of the measurement light from the left test eye EL or the right test eye ER and the reference light that has passed through the reference optical path.

[0030] (Dichroic mirror ML, MR) Each of the dichroic mirrors ML and MR transmits light having wavelength components in the visible region and reflects light having wavelength components in the near-infrared region (or infrared region). Here, the fixation light beams projected by the fixation projection systems 4L and 4R have wavelength components in the visible region, and the light projected by the measurement optical system 300 has wavelength components in the near-infrared region (or infrared region).

[0031] The dichroic mirror ML is disposed on the measurement optical axis OL. The dichroic mirror ML transmits the fixation light beam from the fixation projection system 4L and guides it to the left test eye EL. The dichroic mirror ML also reflects light from the measurement optical system 300 toward the left test eye EL and reflects returning light from the left test 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 beam from the fixation projection system 4R and guides it to the right test eye ER. The dichroic mirror MR also reflects light from the measurement optical system 300 toward the right test eye ER and reflects returning light from the right test eye ER toward the measurement optical system 300.

[0032] (Optical axis switching member SW) The optical axis switching member SW is disposed between the measurement optical system 300 and the dichroic mirrors ML and MR. The optical axis switching member SW is configured to guide the optical axis of the measurement optical system 300 (i.e., light from or to the measurement optical system 300) to either the dichroic mirror ML or MR.

[0033] In some embodiments, the optical axis switching member SW deflects the optical axis of the measurement optical system 300. For example, the optical axis switching member SW has one or more deflection surfaces that can change the deflection direction of the optical axis. In this case, the optical axis switching member SW guides the optical axis of the measurement optical system 300 to the dichroic mirror ML when the deflection surface is oriented in a first deflection direction, and guides the optical axis of the measurement optical system 300 to the dichroic mirror MR when the deflection surface is oriented in a second deflection direction. For example, the optical axis switching member SW has two or more deflection surfaces whose normal directions are different from each other and is configured to be rotatable around a rotation axis extending in the Y-axis direction. In FIG. 1 , the optical axis switching member SW has two deflection surfaces formed on both sides and includes a switching mirror that is rotatable around a rotation axis extending in the Y-axis direction. By rotating such an optical axis switching member SW around the rotation axis, the deflection direction of the optical axis of the measurement optical system 300 can be switched.

[0034] In some embodiments, the optical axis switching member SW is configured to be insertable into and removable from the optical axis of the measurement optical system 300. For example, when the optical axis switching member SW is positioned on the optical axis of the measurement optical system 300, it guides the optical axis to one of the dichroic mirrors ML and MR, and when it is retracted from the optical axis of the measurement optical system 300, it guides the optical axis to the other of the dichroic mirrors ML and MR.

[0035] In some embodiments, the optical axis switching member SW has a deflection surface that deflects the optical axis of the measurement optical system 300 and is configured to be movable along the optical axis. For example, when the optical axis switching member SW is disposed at a first deflection position on the optical axis of the measurement optical system 300, it deflects the optical axis and guides it to one of the dichroic mirrors ML and MR, and when it is disposed at a second deflection position on the optical axis of the measurement optical system 300, it deflects the optical axis and guides it to the other of the dichroic mirrors ML and MR.

[0036] In some embodiments, the optical axis switching member SW quickly switches the optical axis of the measurement optical system 300 so that it alternately substantially coincides with the measurement optical axis OL and the measurement optical axis OR. That is, the optical axis switching member SW may quickly switch the optical axis of the measurement optical system 300 so that light from the measurement optical system 300 is projected onto both eyes substantially simultaneously. For example, the optical axis switching member SW can switch the optical axis of the measurement optical system 300 to at least one of the eyes after providing a time period between projecting light from the measurement optical system 300 onto one of the eyes and receiving the returned light.

[0037] For the sake of convenience, the optical axis switching member SW is hereinafter referred to as having two deflection surfaces formed on both sides, and by rotating around the rotation axis to change the orientation of the deflection surfaces, it is possible to guide the optical axis of the measurement optical system 300 to either the dichroic mirror ML or MR.

[0038] (Fixation projection system 4L, 4R) The fixation projection system 4L projects a fixation light beam onto the fundus ELf of the left eye EL to present a fixation target to the left eye EL. The fixation projection system 4L includes a fixation unit 40L and relay lenses 43L and 44L. The fixation unit 40L includes a liquid crystal panel 41L and a relay lens 42L. The liquid crystal panel 41L displays a pattern representing the fixation target under the control of a control unit described below. The fixation position of the left eye EL can be changed by changing the display position of the pattern on the screen of the liquid crystal panel 41L. Furthermore, the fixation unit 40L can be moved in the optical axis direction under the control of a control unit described below.

[0039] Light from the liquid crystal panel 41L passes through relay lenses 42L, 43L, and 44L, transmits through a dichroic mirror ML, and is projected onto the fundus ELf. In some embodiments, the fixation unit 40L can move in the optical axis direction independently of the relay lenses 43L and 44L.

[0040] Similarly, the fixation projection system 4R projects a fixation light beam onto the fundus ERf of the right eye ER, thereby presenting a fixation target to the right eye ER. The fixation projection system 4R includes a fixation unit 40R and relay lenses 43R and 44R. The fixation unit 40R includes a liquid crystal panel 41R and a relay lens 42R. The liquid crystal panel 41R displays a pattern representing the fixation target under the control of a control unit (described later). The fixation position of the right eye ER can be changed by changing the display position of the pattern on the screen of the liquid crystal panel 41R. Furthermore, the fixation unit 40R can be moved in the optical axis direction under the control of a control unit (described later).

[0041] Light from the liquid crystal panel 41R passes through relay lenses 42R, 43R, and 44R, passes through a dichroic mirror MR, and is projected onto the fundus ERf. In some embodiments, the fixation unit 40R can move in the optical axis direction independently of the relay lenses 43R and 44R.

[0042] The fixation unit 40L can move in the optical axis direction independently of the fixation unit 40R. That is, the fixation units 40L and 40R can move in the optical axis direction independently according to the refractive powers of the left and right eyes EL and ER.

[0043] The fixation positions of the left eye EL and the right eye ER include a position for acquiring an image centered on the macula of the fundus, a position for acquiring an image centered on the optic disc, a position for acquiring an image centered on the center of the fundus between the macula and the optic disc, etc. The display position of the pattern representing the fixation target can be changed as desired.

[0044] The ophthalmic apparatus 1 can perform keratometry, REF measurement, and OCT measurement on the left subject eye EL using the measurement optical system 300, with a fixation target being presented to the left subject eye EL using the fixation projection system 4L. Furthermore, the ophthalmic apparatus 1 can perform keratometry, REF measurement, and OCT measurement on the right subject eye ER using the measurement optical system 300, with a fixation target being presented to the right subject eye ER using the fixation projection system 4R. In some embodiments, the ophthalmic apparatus 1 sequentially performs at least one of keratometry, REF measurement, and OCT measurement on each of the left subject eye EL and the right subject eye ER using the measurement optical system 300, with a fixation target being presented to each of the left subject eye EL and the right subject eye ER using the fixation projection systems 4L and 4R.

[0045] Such an ophthalmic apparatus 1 includes an optical axis adjustment unit that adjusts the optical axis (axis of the optical path of the measurement light) of the OCT optical system 8. Under the control of a control unit (described later), the optical axis adjustment unit controls optical members in the path of the measurement light to deflect the measurement light or move the optical axis of the OCT optical system 8, thereby adjusting the optical axis of the OCT optical system 8. The control unit controls the optical axis adjustment unit so that the optical axis of the OCT optical system 8 approximately coincides with either the measurement optical axis OL or OR.

[0046] The ophthalmologic apparatus 1 also includes an interpupillary distance adjustment unit that changes the distance in the X direction between the measurement optical axes OL and OR in accordance with the interpupillary distance of the subject.

[0047] 3 is an explanatory diagram showing an example of the operation of the interpupillary distance adjusting unit in the ophthalmologic apparatus 1 according to the first embodiment. In Fig. 3, the same parts as in Fig. 1 are given the same reference numerals, and the description thereof will be omitted as appropriate.

[0048] The interpupillary distance adjustment unit changes the distance in the X direction between the measurement optical axes OL and OR by moving the optical axis switching member SW along the measurement optical axis OL or the measurement optical axis OR (Z direction, the optical axis of the measurement optical system 300). For example, when the optical axis switching member SW is in its initial position, the distance in the X direction between the measurement optical axes OL and OR is the interpupillary distance PD. Here, while maintaining the deflection surface of the optical axis switching member SW constant, the optical axis switching member SW is moved from its initial position along the measurement optical axis OL or the measurement optical axis OR. As a result, as shown in FIG. 3 , the positions of the optical axes deflected by the dichroic mirrors ML and MR change, and 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′ and OR′ becomes the interpupillary distance PD′, and the interpupillary distance is changed.

[0049] In some embodiments, the interpupillary distance is changed by moving the optical axis switching member SW in the X direction shown in FIG.

[0050] In some embodiments, the optical axis adjustment unit moves the optical axis switching member SW along the measurement optical axis OL or the measurement optical axis OR so that the optical axis of the OCT optical system 8 approximately coincides with either the measurement optical axis OL or OR.

[0051] In some embodiments, the optical axis switching member SW is moved by a movement mechanism (not shown) under the control of a control unit (described later). In this case, the function of the interpupillary distance adjustment unit is realized by the movement mechanism (and control unit) (not shown). In some embodiments, the optical axis switching member SW is moved manually by a movement mechanism (not shown). In this case, the function of the interpupillary distance adjustment unit is realized by the movement mechanism (not shown).

[0052] The ophthalmologic device 1 also includes a convergence angle adjustment unit that changes at least one of the orientation of the measurement optical axis OL that enters the left test eye EL through the pupil and the orientation of the measurement optical axis OR that enters the right test eye ER through the pupil, in accordance with the convergence angle of the test eye.

[0053] 4 is an explanatory diagram showing an example of the operation of the convergence angle adjusting unit in the ophthalmologic apparatus 1 according to the first embodiment. In Fig. 4, the same parts as those in Fig. 1 are given the same reference numerals, and the description thereof will be omitted as appropriate.

[0054] The convergence angle adjustment unit changes the orientation of at least one of the measurement optical axes OL and OR by changing the orientation of at least one of the dichroic mirror ML and the dichroic mirror MR. Here, the orientation of the dichroic mirror ML corresponds to the orientation (normal direction) of the optical path combining surface of the optical path combining member that combines the optical path (optical axis) of the measurement optical system 300 with the optical path (optical axis) of the fixation projection system 4L. Also, the orientation of the dichroic mirror MR corresponds to the orientation of the optical path combining surface of the optical path combining member that combines the optical path of the measurement optical system 300 with the optical path of the fixation projection system 4R.

[0055] For example, the optical path combining surface (deflection surface) of the dichroic mirror ML is configured to be rotatable around a rotation axis extending in the Y-axis direction. For example, the optical path combining surface (deflection surface) of the dichroic mirror MR is configured to be rotatable around a rotation axis extending in the Y-axis direction.

[0056] For example, when the deflection surface of the dichroic mirror ML is oriented in a first direction and the deflection surface of the dichroic mirror MR is oriented in a second direction, the measurement optical axes OL and OR are oriented substantially parallel to the optical axis direction of the measurement optical system 300. Here, the deflection surfaces of the dichroic mirrors ML and MR are changed to face inward. As a result, as shown in FIG. 4, the measurement optical axis OL deflected by the dichroic mirror ML becomes the measurement optical axis OL′, and the measurement optical axis OR becomes the measurement optical axis OR′, changing the convergence angle.

[0057] In some 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 below. In this case, the function of the convergence angle adjustment unit is realized by the moving mechanism (and control unit) not shown. In some embodiments, the dichroic mirrors ML and MR are rotated manually by a moving mechanism (rotating mechanism) not shown. In this case, the function of the convergence angle adjustment unit is realized by the moving mechanism not shown.

[0058] The convergence angle adjuster may change the direction of at least one of the measurement optical axes OL and OR by adjusting the deflection angle of the deflection surface by the optical axis switching member SW. For example, by adjusting the deflection angle of the deflection surface by the optical axis switching member SW, the incident direction of the optical axis of the measurement optical system 300 on the deflection surfaces of the dichroic mirrors ML and MR can be changed. As a result, the convergence angle is changed.

[0059] In some embodiments, the ophthalmologic apparatus 1 includes a height adjustment unit that changes the orientation (deflection direction) of the deflection surface of the optical axis switching member SW, the orientation of the deflection surface (optical path coupling surface) of the dichroic mirror ML, and the orientation of the deflection surface of the dichroic mirror MR. This adjusts the arrangement direction of the measurement optical axes OL and OR. For example, when the arrangement direction of the left and right patients EL and ER is not horizontal (X direction), the height adjustment unit can align the arrangement direction of the measurement optical axes OL and OR with the arrangement direction of the left and right patients EL and ER. The movement mechanisms that rotate the deflection surface of the optical axis switching member SW, the deflection surface (optical path coupling surface) of the dichroic mirror ML, and the deflection surface of the dichroic mirror MR are examples of a height adjustment unit.

[0060] The ophthalmologic apparatus 1 also includes an arithmetic processing unit that calculates intraocular parameters of the subject's eye based on the detection results of the interference light obtained by the OCT optical system 8. Specifically, the arithmetic processing unit calculates intraocular parameters of the left subject's 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 approximately coincide with the measurement optical axis OL, and calculates intraocular parameters of the right subject's 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 approximately coincide with the measurement optical axis OR.

[0061] The fixation projection system 4L is an example of a "first fixation optical system" according to the embodiment. The fixation projection system 4R is an example of a "second fixation optical system" according to the embodiment. The dichroic mirror ML is an example of a "first optical path coupling member" according to the embodiment. The dichroic mirror MR is an example of a "second optical path coupling member" according to the embodiment. The optical axis switching member SW (or the optical axis switching member SW and a moving mechanism that rotates the optical axis switching member SW) is an example of an "optical axis switching member" according to the embodiment. The moving mechanism that rotates the dichroic mirrors ML and MR is an example of a convergence angle adjustment unit. The convergence angle adjustment unit is an example of a "first adjustment unit" according to the embodiment. The moving mechanism that rotates the deflection surface of the optical axis switching member SW, the deflection surface (optical path coupling surface) of the dichroic mirror ML, and the deflection surface of the dichroic mirror MR is an example of a height adjustment unit. The height adjustment unit is an example of a "second adjustment unit" according to the embodiment. The interpupillary distance adjustment unit is an example of a "third adjustment unit" according to the embodiment.

[0062] The following describes an example of the configuration of the measurement optical system 300. Hereinafter, the left eye EL and the right eye ER may be simply referred to as the eyes to be inspected.

[0063] 5 and 6 show an example of the configuration of the measurement optical system 300 according to the first embodiment. FIG. 5 is a schematic diagram of the measurement optical system 300 as viewed from the side (X direction). FIG. 6 is a schematic diagram of the OCT unit 100 shown in FIG. 5. For ease of explanation, FIG. 5 shows the anterior eye cameras 15LA and 15RA arranged in the X direction, and the anterior eye cameras 15LB and 15RB arranged in the X direction. However, the configuration according to the embodiment is not limited to this. For ease of explanation, the dichroic mirrors ML and MR shown in FIG. 1 are not shown in FIG. 5. In FIG. 5, parts similar to those in FIG. 1 are designated by the same reference numerals, and their descriptions will be omitted where appropriate. In FIG. 6, parts similar to those in FIG. 5 are designated by the same reference numerals, and their descriptions will be omitted where appropriate.

[0064] The measurement optical system 300 includes an optical system for observing either the left or right subject eye EL or ER, an optical system for testing either the left or right subject eye EL or ER, and a dichroic mirror for wavelength separation of the optical paths of these optical systems. An anterior segment observation system 5 is provided as an optical system for observing either the left or right subject eye EL or ER. A keratometry system 3, a refractive power measurement optical system (refractive power measurement optical system), and an OCT optical system 8 are provided as optical systems for testing either the left or right subject eye EL or ER. As shown in FIG. 2, the refractive power measurement optical system includes a refractive power measurement projection system 6 and a refractive power measurement light-receiving system 7.

[0065] In the first embodiment, the keratoconstriction measurement system 3, the refraction measurement projection system 6, the refraction measurement light-receiving system 7, and the OCT optical system 8 are used in common for the examination of the left eye EL and the examination of the right eye ER. The optical axis of the OCT optical system 8 is coaxially coupled to the optical axis of the refraction measurement optical systems (the refraction measurement projection system 6 and the refraction measurement light-receiving system 7).

[0066] Specifically, the measurement optical system 300 includes an XY alignment system 2, a keratomileusis measurement system 3, an anterior-segment observation system 5, a refraction measurement projection system 6, a refraction measurement light-receiving system 7, an OCT optical system 8, and anterior-segment cameras 15LA, 15RA, 15LB, and 15RB. Hereinafter, for example, the anterior-segment observation system 5 uses light of 940 nm to 1000 nm, the refraction measurement optical systems (refraction measurement projection system 6 and refraction measurement light-receiving system 7) use light of 830 nm to 880 nm, and the OCT optical system 8 uses light of 800 nm to 900 nm. In this case, the fixation projection systems 4L and 4R shown in FIG. 1 can use light of 400 nm to 700 nm. In some embodiments, the OCT optical system 8 uses light of 1000 nm to 1100 nm.

[0067] (Anterior segment observation system 5) The anterior eye observation system 5 captures video of the anterior eye of the left subject's eye EL or the anterior eye of the right subject's eye ER on a measurement optical axis where the optical axis of the objective lens 51 (measurement optical system 300) is optically coaxially coupled. In the optical system via the anterior eye observation system 5, the imaging surface of the imaging element 59 is arranged at a pupil conjugate position. The anterior eye illumination light source 50 irradiates illumination light (e.g., infrared light) onto the anterior eye of the left subject's eye EL or the anterior eye of the right subject's eye ER.

[0068] In some embodiments, the anterior-segment illumination light source 50 includes a pair of illumination light sources for illuminating the anterior segment of the left test eye EL or the anterior segment of the right test eye ER from positions away from the measurement optical axes OL and OR. In some embodiments, the anterior-segment illumination light source 50 includes a pair of illumination light sources for illuminating the anterior segment of the left test eye EL from positions away from the measurement optical axis OL, and a pair of illumination light sources for illuminating the anterior segment of the right test eye ER from positions away from the measurement optical axis OR. In this case, one of the pair of illumination light sources for illuminating the anterior segment of the left test eye EL and one of the pair of illumination light sources for illuminating the anterior segment of the right test eye ER may be shared.

[0069] Light reflected by the anterior segment of the left eye EL or the anterior segment of the right eye ER passes through the objective lens 51, the dichroic mirror 52, the aperture formed in the diaphragm (telecentric diaphragm) 53, the half mirror 23, the relay lenses 55 and 56, and the dichroic mirror 76. The dichroic mirror 52 combines (separates) the optical path of the reflex measurement optical system and the optical path of the anterior segment observation system 5. The dichroic mirror 52 has an optical path combining surface that combines these optical paths and is positioned inclined with respect to the optical axis of the objective lens 51. The light transmitted through the dichroic mirror 76 is imaged by the imaging lens 58 on the imaging surface of the image sensor 59 (area sensor). The image sensor 59 captures images and outputs signals at a predetermined rate. The output (video signal) of the image sensor 59 is input to the processing unit 9, which will be described later. The processing unit 9 displays the anterior segment image of the left subject's eye EL or the anterior segment image of the right subject's eye ER based on this video signal on the later-described display unit 270. The anterior segment image of the left subject's eye EL or the anterior segment image of the right subject's eye ER is, for example, an infrared moving image.

[0070] (Anterior segment camera 15LA, 15RA, 15LB, 15LB) The anterior eye cameras 15LA and 15LB photograph the anterior eye of the left subject's eye EL. The anterior eye cameras 15LA and 15LB are, for example, video cameras that capture moving images at a predetermined frame rate. The anterior eye cameras 15LA and 15LB photograph the anterior eye from different directions substantially simultaneously. For example, the anterior eye cameras 15LA and 15LB are used to align the optical system with respect to the left subject's eye EL.

[0071] The number of anterior-segment cameras for photographing the anterior segment of the left eye EL to be examined may be any number equal to or greater than two, as long as they are configured to be able to photograph the anterior segment from two different directions substantially simultaneously. In addition, one anterior-segment camera may be the image sensor 59 in the anterior-segment observation system 5.

[0072] "Substantially simultaneously" means that the timing of photographing with two or more anterior eye cameras can be offset to the extent that eye movement can be ignored, allowing the two or more anterior eye cameras to capture images of the subject's eye in the same position (direction).

[0073] The anterior eye cameras 15RA and 15RB photograph the anterior eye of the right eye ER. The anterior eye cameras 15RA and 15RB are, for example, video cameras that capture moving images at a predetermined frame rate. The anterior eye cameras 15RA and 15RB photograph the anterior eye from different directions substantially simultaneously. For example, the anterior eye cameras 15RA and 15RB are used to align the optical system with respect to the right eye ER.

[0074] The number of anterior-segment cameras for photographing the anterior segment of the right eye ER may be any number greater than or equal to two, as long as they are configured to be able to photograph the anterior segment from two different directions substantially simultaneously. In addition, one anterior-segment camera may be the image sensor 59 in the anterior-segment observation system 5.

[0075] In some embodiments, a known optical lever type Z alignment system is provided instead of the anterior eye cameras 15LA and 15LB. In some embodiments, a known optical lever type Z alignment system is provided instead of the anterior eye cameras 15RA and 15RB.

[0076] (XY alignment system 2) The XY alignment system 2 irradiates the left or right eye EL or ER to be examined on a measurement optical axis, which is optically coaxially coupled to the optical axis of the anterior-segment observation system 5, with light (infrared light) for alignment in directions (left-right direction (X direction) and up-down direction (Y direction)) perpendicular to the optical axis of the anterior-segment observation system 5. The XY alignment system 2 includes an XY alignment light source 21 and a collimator lens 22, which are provided on an optical path branched from the optical path of the anterior-segment observation system 5 by a half mirror 23. The light output from the XY alignment light source 21 passes through the collimator lens 22, is reflected by the half mirror 23, and is projected onto the left or right eye EL or ER to be examined via the anterior-segment observation system 5. The light reflected by the cornea CLr of the left or right eye EL or CRr of the right eye ER is guided to an image sensor 59 via the anterior-segment observation system 5.

[0077] An image (XY bright spot image) based on light reflected from the cornea CLr is included in the anterior segment image of the left subject's eye EL. An image (XY bright spot image) based on light reflected from the cornea CRr is included in the anterior segment image of the right subject's eye ER. For example, the processing unit 9 displays an anterior segment image including an XY bright spot image and an alignment mark for the left subject's eye EL or the right subject's eye ER on the display unit. When performing XY alignment manually, the user moves the optical system to guide the XY bright spot image into the alignment mark. When performing automatic alignment, the processing unit 9 controls a mechanism for moving the optical system so that the displacement of the XY bright spot image relative to the alignment mark is canceled. In some embodiments, the processing unit 9 controls a mechanism for moving the optical system and a mechanism for moving the optical axis switching member SW and the dichroic mirrors ML and MR shown in FIG. 1 so that the displacement of the XY bright spot image relative to the alignment mark is canceled.

[0078] (Keratometry System 3) The keratometry system 3 projects a ring-shaped light beam (infrared light) onto the cornea CLr or CRr to measure the shape of the cornea CLr of the left eye EL or the shape of the cornea CRr of the right eye ER (corneal shape information). The keratoplate 31 is disposed between the objective lens 51 and the left eye EL or the right eye ER. A keratoplate light source 32 is provided on the back side (objective lens 51 side) of the keratoplate 31. A keratoplate pattern (transmitting portion) that transmits light from the keratoplate light source 32 is formed on the keratoplate 31 along a circumference centered on the optical axis of the objective lens 51 (measurement optical system 300). In some embodiments, the keratoplate 31 is formed with a keratoplate pattern (transmitting portion) that transmits light from the keratoplate light source 32 along a circumference centered on the optical axis. The keratoplate pattern may be formed in an arc shape (part of a circumference) centered on the optical axis. By illuminating the keratoplastor 31 with light from the keratoplastor light source 32, a ring-shaped light beam (an arc-shaped or circumferential measurement pattern) is projected onto the cornea CLr or CRr. The reflected light (keratoplastor image) from the cornea CLr or CRr is detected by the imaging element 59 together with an anterior segment image of the left subject's eye EL or an anterior segment image of the right subject's eye ER. The processing unit 9 performs known calculations based on this keratoplastor image to calculate corneal shape parameters representing the shape of the cornea CLr and corneal shape parameters representing the shape of the cornea CRr.

[0079] (Reflector measurement projection system 6, Reflector measurement light receiving system 7) The refractive measurement optical system includes a refractive measurement projection system 6 and a refractive measurement light-receiving system 7 used for refractive power measurement. The refractive measurement projection system 6 projects a light beam (e.g., a ring-shaped light beam) (infrared light) for refractive power measurement onto the fundus ELf of the left subject eye EL or the fundus ERf of the right subject eye ER on a measurement optical axis optically coaxially coupled to the optical axis of the objective lens 51 (measurement optical system 300). The refractive measurement light-receiving system 7 receives the return light of the light beam for refractive power measurement from the left subject eye EL or the right subject eye ER.

[0080] The reflex measurement projection system 6 is provided on an optical path branched by an aperture prism 65 provided on the optical path of the reflex measurement light-receiving system 7. The aperture formed in the aperture prism 65 is arranged at a pupil conjugate position of the left eye EL or the right eye ER on the measurement optical axis where the optical axis of the objective lens 51 (measurement optical system 300) is optically coaxially coupled. In the optical system passing through the reflex measurement light-receiving system 7, the imaging surface of the imaging element 59 is arranged at a fundus conjugate position.

[0081] In some embodiments, the reflector measurement light source 61 is a superluminescent diode (SLD) light source, which is a high-brightness light source. The reflector measurement light source 61 is movable in the optical axis direction. The reflector measurement light source 61 is disposed at a position conjugate with the fundus of the left subject's eye EL or the right subject's eye ER on the measurement optical axis, where the optical axis of the objective lens 51 (measurement optical system 300) is optically coaxially coupled.

[0082] Light output from the reflector measurement light source 61 passes through a relay lens 62 and is incident on the conical surface of a conical prism 63. The light incident on the conical surface is deflected and exits from the bottom surface of the conical prism 63. The light exiting from the bottom surface of the conical prism 63 passes through a ring-shaped light-transmitting portion formed in an annular diaphragm 64. The light passing through the light-transmitting portion of the annular diaphragm 64 (ring-shaped light beam) is reflected by a reflective surface formed around the hole of the aperture prism 65, passes through a rotary prism 66, and is reflected by a dichroic mirror 67. The light reflected by the dichroic mirror 67 is reflected by a dichroic mirror 52, passes through the objective lens 51, and is projected onto the left or right eye EL or ER to be examined on the measurement optical axis adjusted to approximately coincide with the optical axis of the objective lens 51. The rotary prism 66 is used to average the light intensity distribution of the ring-shaped light beam on the blood vessels or diseased areas of the fundus and to reduce speckle noise caused by the light source.

[0083] The return light of the ring-shaped light beam projected onto the fundus ELf of the left eye EL or the fundus ERf of the right eye ER passes through the objective lens 51 and is reflected by the dichroic mirror 52 and the dichroic mirror 67. The return light reflected by the dichroic mirror 67 passes through the rotary prism 66, passes through the hole in the aperture prism 65, passes through the relay lens 71, is reflected by the reflecting mirror 72, and passes through the relay lens 73 and the focusing lens 74. The focusing lens 74 is movable along the optical axis of the reflector measurement light-receiving system 7. The light that passed through the focusing lens 74 is reflected by the reflecting mirror 75 and the dichroic mirror 76, and is imaged by the imaging lens 58 on the imaging surface of the imaging element 59.

[0084] The processing unit 9 calculates the refractive power value of the left test eye EL or the right test eye ER by performing a known calculation based on the output from the image sensor 59. Specifically, the processing unit 9 identifies a ring pattern image from the left test eye EL or the right test eye ER based on the output from the image sensor 59, and calculates the refractive power value of the left test eye EL or the right test eye ER by performing a known calculation on the identified ring pattern image. By sequentially switching the optical axis of the reflex measurement optical system to the measurement optical axes OL and OR, the processing unit 9 can sequentially calculate the refractive power value of the left test eye EL and the refractive power value of the right test eye ER. For example, the refractive power value includes spherical power, astigmatic power and astigmatic axis angle, or equivalent spherical power.

[0085] In some embodiments, the measurement optics 300 includes fixation projection systems 4L, 4R.

[0086] (OCT optical system 8) The OCT optical system 8 is an optical system for performing OCT measurement. For example, based on the result of a refractive measurement performed before the OCT measurement, the position of the focusing lens 87 is adjusted so that the end face of the optical fiber f1 is conjugate with the imaging site (fundus or anterior segment) and the optical system.

[0087] The OCT optical system 8 is provided on an optical path that is wavelength-separated from the optical path of the reflex measurement optical system by a dichroic mirror 67. The optical axis of the OCT optical system 8 is coupled coaxially with the optical axis of the objective lens 51 (the optical axis of the reflex measurement optical system), and can be adjusted to approximately coincide with either one of the measurement optical axes OL and OR.

[0088] The OCT optical system 8 includes an OCT unit 100. As shown in FIG. 6, the OCT unit 100 is provided with an optical system for performing OCT measurement (OCT photography, OCT scanning) on ​​either the left subject eye EL or the right subject eye ER. This optical system has a configuration similar to that of a conventional spectral domain type OCT device. That is, this optical system is configured to split light (low coherence light) from a broadband light source into reference light and measurement light, cause the measurement light that has passed through the subject eye (OCT measurement site) to interfere with the reference light that has passed through the reference light path, generate interference light, and detect the spectral components of this interference light. This detection result (detection signal) is sent to the processing unit 9.

[0089] The light source unit 101 outputs broadband low-coherence light L0. The low-coherence light L0 has wavelength components in the near-infrared wavelength band (approximately 800 nm to 900 nm) and has a temporal coherence length of approximately several tens of micrometers. Alternatively, near-infrared light having a center wavelength of approximately 1040 to 1060 nm, which is not visible to the human eye, may be used as the low-coherence light L0.

[0090] Hereinafter, it is assumed that the light source unit 101 outputs low-coherence light L0 having a wavelength component of 840 nm.

[0091] The light source unit 101 includes a light output device such as a super luminescent diode (SLD), an LED, or an SOA (Semiconductor Optical Amplifier).

[0092] Low-coherence light L0 output from a light source unit 101 is guided by an optical fiber 102 to a fiber coupler 103, where it is split into a measurement light LS and a reference light LR.

[0093] The reference light LR is guided through an optical fiber 104 and reaches an attenuator (optical attenuator) 105. The attenuator 105 automatically adjusts the light intensity of the reference light LR guided through the optical fiber 104 under the control of the processing unit 9 using known technology. The reference light LR whose light intensity has been adjusted by the attenuator 105 is guided through the optical fiber 104 and reaches a polarization controller (polarization adjuster) 106. The polarization controller 106 is a device that adjusts the polarization state of the reference light LR guided through the optical fiber 104, for example, by applying external stress to the looped optical fiber 104. Note that the configuration of the polarization controller 106 is not limited to this, and any known technology can be used. The reference light LR whose polarization state has been adjusted by the polarization controller 106 reaches a fiber coupler 109.

[0094] The measurement light LS generated by the fiber coupler 103 is guided by the optical fiber f1 to the collimator lens 90 (FIG. 6), where it is collimated into a parallel beam by the collimator lens 90. The measurement light LS then passes through an optical path length changing unit 89, an optical scanner 88, a focusing lens 87, relay lenses 85 and 82, and a reflecting mirror 81, before reaching the dichroic mirror 67.

[0095] In some embodiments, the focusing lens 87 and the optical scanner 88 are housed in a single unit that is movable in the optical axis direction. This allows the focusing lens 87 and the optical scanner 88 to move in the optical axis direction while maintaining the optical positional relationship between them. By configuring the focusing lens 87 and the optical scanner 88 to be movable as a single unit in this manner, it is possible to adjust the optical system while maintaining the conjugate relationship between the optical scanner 88 and the subject's eye. Furthermore, with this configuration, the magnification relationship between the pupil of the subject's eye and the optical scanner 88 can be easily changed by changing the focal length f of the focusing lens 87.

[0096] In some embodiments, the focusing lens 87 and the optical scanner 88 are moved independently in the optical axis direction within the unit. In some embodiments, the focusing lens 87 and the optical scanner 88 are moved independently or integrally in the optical axis direction under control of the processing unit 9. For example, the pupil of the subject's eye is positioned at the focal position of the objective lens 51, and the deflection surface of the optical scanner 88 is positioned at the focal position of the focusing lens 87 (when the optical scanner 88 is positioned at the focal position of the focusing lens 87, a pupil conjugate relationship is maintained, and the deflection surface of the optical scanner 88 is positioned at the pupil conjugate position).

[0097] The optical path length changing unit 89 changes the optical path length of the measurement light LS. By changing the optical path length of the measurement light LS, it is possible to change the difference between the optical path length of the reference light LR and the optical path length of the measurement light LS. For example, the optical path length changing unit 89 includes a retroreflector that is movable along the optical path of the measurement light LS and the optical path of the return light of the measurement light LS, and changes the optical path length of the measurement light LS by moving the retroreflector.

[0098] The optical scanner 88 deflects the measurement light LS one-dimensionally or two-dimensionally.

[0099] In some 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 as to scan the OCT measurement region in a horizontal direction (X direction) perpendicular 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 as to scan the imaging region in a vertical direction (Y direction) perpendicular to the optical axis of the OCT optical system 8. Examples of scanning patterns of the measurement light LS by such optical scanner 88 include horizontal scan, vertical scan, cross scan, radial scan, circular scan, concentric scan, spiral scan, and Lissajous scan.

[0100] In some embodiments, the optical scanner 88 includes a MEMS scanner (MEMS mirror scanner) that two-dimensionally deflects the measurement light LS. The MEMS scanner deflects the measurement light LS so as to scan the OCT measurement region in horizontal and vertical directions perpendicular to the optical axis of the OCT optical system 8.

[0101] The optical scanner 88 may be configured to include a polygon mirror, a rotating mirror, a dowel prism, a double dowel prism, a rotation prism, etc., in addition to the galvanometer mirror and the MEMS scanner.

[0102] The measurement light LS that reaches the dichroic mirror 67 passes through the dichroic mirror 67, is reflected by the dichroic mirror 52, and is refracted by the objective lens 51. The measurement light LS refracted by the objective lens 51 is deflected toward the dichroic mirror ML or the dichroic mirror MR by the optical axis switching member SW. The measurement light LS deflected by the dichroic mirror ML or the dichroic mirror MR is irradiated onto the OCT measurement site of the left subject's eye EL or the right subject's eye ER. The measurement light LS is scattered (including reflected) at various depth positions in the OCT measurement site. Backscattered light of the measurement light LS by the OCT measurement site travels in the opposite direction along the same path as the outward path and is guided to the fiber coupler 103, and reaches the fiber coupler 109 via the optical fiber 108.

[0103] The fiber coupler 109 causes interference between the backscattered light of the measurement light LS and the reference light LR that has passed through the attenuator 105 and the like. The interference light LC thus generated is guided by an optical fiber 110 and emitted from an output end 111. The interference light LC is then collimated by a collimator lens 112, dispersed (spectrally resolved) by a diffraction grating (spectroscope) 113, and collected by a zoom optical system 114 to be projected onto the light-receiving surface of a CCD image sensor 115. Note that although the diffraction grating 113 shown in FIG. 8 is a transmissive type, it is also possible to use other types of spectroscopic elements, such as a reflective diffraction grating.

[0104] The CCD image sensor 115 is, for example, a line sensor that has two or more light receiving elements (detecting elements) arranged therein, and detects each spectral component of the dispersed interference light LC and converts it into an electric charge. The CCD image sensor 115 accumulates the electric charges to generate a detection signal, which is then sent to the processing unit 9.

[0105] Although a Michelson interferometer is used in this embodiment, any type of interferometer, such as a Mach-Zehnder interferometer, can be used as appropriate. Also, instead of a CCD image sensor, other types of image sensors, such as a CMOS (Complementary Metal Oxide Semiconductor) image sensor, can be used.

[0106] 5, the optical path length change unit 89 is configured to change the optical path length of the measurement light LS to change the difference between the optical path length of the measurement light LS and the optical path length of the reference light LR, but the configuration according to the embodiment is not limited to this. For example, the optical path length of the reference light LR may be changed by a known method to change the difference between the optical path length of the measurement light LS and the optical path length of the reference light LR.

[0107] The processing unit 9 is capable of calculating a refractive power value of the left subject eye EL from a measurement result obtained using the refraction measurement optical system, and moving the refraction measurement light source 61 in the optical axis direction to a position where the fundus ELf, the refraction measurement light source 61, and the image sensor 59 are conjugate with each other based on the calculated refractive power value. The processing unit 9 is also capable of calculating a refractive power value of the right subject eye ER from a measurement result obtained using the refraction measurement optical system, and moving the refraction measurement light source 61 in the optical axis direction to a position where the fundus ERf, the refraction measurement light source 61, and the image sensor 59 are conjugate with each other based on the calculated refractive power value. In some embodiments, the processing unit 9 moves the focusing lens 74 to a position corresponding to a composite refractive power value (e.g., intermediate diopter) calculated from the refractive power value of the left subject eye EL and the refractive power value of the right subject eye ER.

[0108] In some embodiments, the processing unit 9 moves the focusing lens 87 and the optical scanner 88 in the optical axis direction in conjunction with the movement of the focusing lens 74. In some embodiments, the processing unit 9 moves the liquid crystal panel 41L (fixation unit 40L) in the optical axis direction in conjunction with the movement of the reflector measurement light source 61 and the focusing lens 74. In some embodiments, the processing unit 9 moves the liquid crystal panel 41R (fixation unit 40R) in the optical axis direction in conjunction with the movement of the reflector measurement light source 61 and the focusing lens 74.

[0109] In the above embodiments, at least one function of the focusing lenses 74, 87 may be realized by a liquid crystal lens or a liquid lens.

[0110] The configuration of the optical system of the ophthalmologic apparatus 1 according to the embodiment is not limited to the configurations shown in FIGS.

[0111] <Example of anterior eye camera placement> FIG. 7 shows a schematic example of the arrangement of the anterior eye cameras 15LA, 15RA, 15LB, and 15LB shown in FIG.

[0112] 7, for example, the anterior eye camera 15LA is disposed to photograph the left subject eye EL from a direction forming a positive angle in the Y direction with respect to the measurement optical axis OL, and the anterior eye camera 15LB is disposed to photograph the left subject eye EL from a direction forming a negative angle in the Y direction with respect to the measurement optical axis OL. The anterior eye camera 15LA may be disposed to photograph the left subject eye EL from a direction forming a positive angle in the X direction with respect to the measurement optical axis OL, and the anterior eye camera 15LB may be disposed to photograph the left subject eye EL from a direction forming a negative angle in the X direction with respect to the measurement optical axis OL.

[0113] Similarly, for example, the anterior eye camera 15RA is disposed to photograph the right eye ER from a direction forming a positive angle in the Y direction with respect to the measurement optical axis OR, and the anterior eye camera 15RB is disposed to photograph the right eye ER from a direction forming a negative angle in the Y direction with respect to the measurement optical axis OR. The anterior eye camera 15RA may be disposed to photograph the right eye ER from a direction forming a positive angle in the X direction with respect to the measurement optical axis OR, and the anterior eye camera 15RB may be disposed to photograph the right eye ER from a direction forming a negative angle in the X direction with respect to the measurement optical axis OR.

[0114] A part of the functions of the anterior eye cameras 15LA, 15RA, 15LB, and 15LB may be realized by one anterior eye camera.

[0115] FIG. 8 shows a schematic example of an arrangement in which the functions of the anterior eye cameras 15LB and 15RB in FIG. 1 are realized by an anterior eye camera 15LR.

[0116] The anterior eye camera 15LR photographs the anterior eye of the left eye EL and the anterior eye of the right eye ER. As shown in Fig. 8, for example, the anterior eye camera 15LA is disposed so as to photograph the left eye EL from a direction forming a positive angle in the Y direction with respect to the measurement optical axis OL, and the anterior eye camera 15LR is disposed so as to photograph the left eye EL from a direction forming a negative angle in the Y direction with respect to the measurement optical axis OL. The anterior eye camera 15LA may be disposed so as to photograph the left eye EL from a direction forming a positive angle in the X direction with respect to the measurement optical axis OL, and the anterior eye camera 15LR may be disposed so as to photograph the left eye EL from a direction forming a negative angle in the X direction with respect to the measurement optical axis OL.

[0117] Similarly, for example, the anterior eye camera 15RA is disposed to photograph the right eye ER from a direction forming a positive angle in the Y direction with respect to the measurement optical axis OR, and the anterior eye camera 15LR is disposed to photograph the right eye ER from a direction forming a negative angle in the Y direction with respect to the measurement optical axis OR. The anterior eye camera 15LR may be disposed to photograph the right eye ER from a direction forming a positive angle in the X direction with respect to the measurement optical axis OR, and the anterior eye camera 15RA may be disposed to photograph the right eye ER from a direction forming a negative angle in the X direction with respect to the measurement optical axis OR.

[0118] The ophthalmic device 1 according to the embodiment can execute a refraction measurement (refractive power measurement) using the refraction measurement optical system and an OCT measurement using the OCT optical system 8 while sharing an objective lens at least in the refraction measurement optical system and the OCT optical system 8. Each of the refraction measurement and the OCT measurement can be sequentially executed for either the left eye to be examined or the right eye to be examined. In some embodiments, before performing an OCT measurement on one of the left eye to be examined EL and the right eye to be examined ER, the optical path length of the reference optical path is adjusted by controlling the OCT optical system 8 based on the axial length and refractive power of the other of the left eye to be examined EL and the right eye to be examined ER. Thereby, before performing an OCT measurement on one eye to be examined, a measurement environment estimated from the measurement environment of the other eye to be examined can be set, and the time required for the OCT measurement can be shortened.

[0119] The ophthalmic device 1 according to the first embodiment can adjust the optical axis (axis of the optical path of the measurement light) of the OCT optical system 8.

[0120] <Example of adjustment of the optical axis of the OCT optical system 8> FIG. 9A shows an explanatory diagram of a first example of adjusting the optical axis of the OCT optical system 8 according to the first embodiment. In FIG. 9A, the same parts as those in FIG. 1 are denoted by the same reference numerals, and the description thereof is omitted as appropriate.

[0121] The measurement optical system 300 includes deflection members DF1 and DF2. The deflection member DF1 deflects the optical axis of the OCT optical system 8 toward the deflection member DF2, and the deflection member DF2 deflects the optical axis deflected by the deflection member DF1 toward the optical axis switching member SW. For example, by moving the deflection member DF1 in the optical axis direction, the optical axis of the OCT optical system 8 can be adjusted so that one of the measurement optical axes OL and OR substantially coincides with the other. For example, at the position of the deflection member DF1′, the optical axis of the OCT optical system 8 can be made to substantially coincide with the measurement optical axis OL, and at the position of the deflection member DF1, the optical axis of the OCT optical system 8 can be made to substantially coincide with the measurement optical axis OR.

[0122] For example, the ophthalmologic apparatus 1 can move the deflecting member DF1 in accordance with the interpupillary distance of the subject, thereby making it possible to make the optical axis of the OCT optical system 8 substantially coincide with either one of the measurement optical axes OL and OR.

[0123] 5, an example of the deflecting member DF1 is a reflecting mirror 81. An example of the deflecting member DF2 is a dichroic mirror 52.

[0124] 9B shows an explanatory diagram of a second example of adjustment of the optical axis of the OCT optical system 8 according to the first embodiment. In FIG. 9B, the same parts as in FIG. 1 are denoted by the same reference numerals, and descriptions thereof will be omitted where appropriate.

[0125] The measurement optical system 300 (ophthalmologic apparatus 1) includes a movement mechanism that moves the OCT optical system 8 under the control of a control unit described below. For example, this movement mechanism moves the OCT optical system 8 (specifically, the OCT unit 100) independently of the optical elements on the path from the objective lens 51 to the collimator 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 it approximately coincides with one of the measurement optical axes OL and OR. For example, at the position of the OCT optical system 8′, the optical axis of the OCT optical system 8 can be approximately coincident with the measurement optical axis OL, and at the position of the OCT optical system 8, the optical axis of the OCT optical system 8 can be approximately coincident with the measurement optical axis OR.

[0126] 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 subject's interpupillary distance, thereby making the optical axis of the OCT optical system 8 approximately coincident with either one of the measurement optical axes OL or OR.

[0127] As a third example of adjustment of the optical axis of the OCT optical system 8 according to the first embodiment, the deflection direction of the optical axis of the OCT optical system 8 can be changed by an optical member in the path of the measurement light. Examples of optical members include the reflecting mirror 81 in FIG. 5 , the dichroic mirror 52, and a reflecting mirror (not shown). For example, the optical axis of the OCT optical system 8 is adjusted by changing the deflection direction of the OCT optical system 8 deflected by the optical member based on the interpupillary distance of the subject.

[0128] <Processing system configuration> The configuration of the processing system of the ophthalmologic apparatus 1 will be described.

[0129] 10 and 11 show an example of the functional configuration of the processing system of the ophthalmic apparatus 1. Fig. 10 shows an example of a functional block diagram of the processing system of the ophthalmic apparatus 1. Fig. 11 shows an example of a functional block diagram of the OCT optical system 8 of Fig. 10. In Fig. 10 and Fig. 11, parts that are the same as those in Fig. 1 or Fig. 5 are given the same reference numerals, and descriptions thereof will be omitted as appropriate.

[0130] The processing unit 9 controls each unit of the ophthalmologic apparatus 1. The processing unit 9 can also execute various types of arithmetic processing. The functions of the processing unit 9 are realized by a processing circuit. The processing unit 9 includes one or more processors. The functions of the processor are realized by circuits such as a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (e.g., an SPLD (Simple Programmable Logic Device), a CPLD (Complex Programmable Logic Device), or an FPGA (Field Programmable Gate Array)). The processing unit 9 realizes the functions according to the embodiment by, for example, reading and executing a program stored in a memory circuit or a storage device.

[0131] In some embodiments, processing unit 9 includes a single processor that implements functionality in accordance with embodiments. In some embodiments, processing unit 9 includes multiple processors, each processor implementing one or more functionality in accordance with embodiments.

[0132] The processing unit 9 includes a control unit 210 and an arithmetic processing unit 220. The ophthalmologic apparatus 1 also includes movement mechanisms 200, 310, 320, a display unit 270, an operation unit 280, and a communication unit 290.

[0133] The movement mechanism 200 is a mechanism for moving a head unit, which houses optical systems such as the anterior eye cameras 15LA, LB, RA, and RB, the XY alignment system 2, the keratometry system 3, the anterior eye observation system 5, the reflex measurement projection system 6, the reflex measurement light receiving system 7, and the OCT optical system 8, in the X, Y, and Z directions. For example, the movement mechanism 200 is provided with an actuator that generates a driving force for moving the head unit and a transmission mechanism that transmits this driving force. The actuator is, for example, constituted by a pulse motor. The transmission mechanism is, for example, constituted by a combination of gears or a rack-and-pinion. The control unit 210 (main control unit 211) controls the movement mechanism 200 by sending control signals to the actuator.

[0134] The movement mechanism 310 moves the optical axis switching member SW as shown in Fig. 3. For example, the movement mechanism 310 has the same configuration as the movement mechanism 200. The control unit 210 (main control unit 211) controls the movement mechanism 310 by sending a control signal to an actuator.

[0135] 4, the movement mechanism 320 rotates each of the dichroic mirrors ML and MR independently around a rotation axis. For example, the movement mechanism 320 is provided with an actuator that generates a driving force for rotating each of the dichroic mirrors ML and MR, and a transmission mechanism that transmits this driving force. The control unit 210 (main control unit 211) controls the movement mechanism 320 by sending a control signal to the actuator.

[0136] Although not shown, the ophthalmologic apparatus 1 may include a mechanism for adjusting the optical axis of the OCT optical system 8 shown in Figures 9A and 9B. For example, the mechanism has the same configuration as the moving mechanism 200 or the moving mechanism 320. The control unit 210 (main control unit 211) controls the mechanism by sending control signals to the actuators.

[0137] (control unit 210) The control unit 210 includes a processor and controls each unit of the ophthalmic apparatus 1. The control unit 210 includes a main control unit 211 and a storage unit 212. The storage unit 212 stores computer programs for controlling the ophthalmic apparatus 1 in advance. The computer programs include an anterior eye camera control program, an XY alignment system control program, a keratometry system control program, a fixation projection system control program, an anterior eye observation control program, a reflex measurement control program, an OCT measurement control program, a calculation processing program, a user interface program, and a communication control program. The main control unit 211 operates in accordance with these computer programs, causing the control unit 210 to execute control processing.

[0138] The main control unit 211 performs various controls of the ophthalmologic apparatus as a measurement control unit. The controls for the anterior eye cameras 15LA, 15LB, 15RA, and 15RB include exposure adjustment, gain adjustment, frame rate adjustment, shooting timing adjustment, shooting range adjustment, shooting magnification adjustment, synchronization control of the anterior eye cameras 15LA and 15LB, synchronization control of the anterior eye cameras 15RA and 15RB, and synchronization control of the anterior eye cameras 15LA, 15LB, 15RA, and 15RB.

[0139] The anterior ocular cameras 15LA and 15LB capture images of the anterior ocular segment of the left subject's eye EL from different directions substantially simultaneously. The main controller 211 controls the data processor 223 (described later) to determine the three-dimensional position of the left subject's eye EL from the two captured images acquired by the anterior ocular cameras 15LA and 15LB. The data processor 223 analyzes each of the two captured images acquired substantially simultaneously by the anterior ocular cameras 15LA and 15LB and applies known trigonometry to determine a characteristic position corresponding to a characteristic portion of the anterior ocular segment of the left subject's eye EL, as disclosed in, for example, Japanese Patent Application Laid-Open Publication No. 2013-248376. The characteristic portion of the anterior ocular segment is, for example, the pupil center. Furthermore, the data processor 223 determines the three-dimensional position of the left subject's eye EL based on the determined characteristic position. In this example, the position of the pupil center approximates the position of the subject's eye. In addition, the position of the corneal apex can be determined as the position of the test eye by using the distance between the corneal apex and the pupil in the test eye, or the distance between the corneal apex and the pupil in a standard eye (model eye, average value, etc.).

[0140] The anterior ocular cameras 15RA and 15RB capture images of the anterior ocular segment of the right eye ER from different directions substantially simultaneously. The main controller 211 controls the data processor 223 (described later) to identify the three-dimensional position of the right eye ER from the two captured images acquired by the anterior ocular cameras 15RA and 15RB. The data processor 223 analyzes each of the two captured images acquired substantially simultaneously by the anterior ocular cameras 15RA and 15RB and applies known trigonometry to identify characteristic positions corresponding to characteristic parts of the anterior ocular segment of the right eye ER. Furthermore, the data processor 223 identifies the three-dimensional position of the right eye ER based on the identified characteristic positions.

[0141] The main controller 211 can align the optical systems with the left and right test eyes EL and ER by controlling the moving mechanism 200 based on the three-dimensional positions of the left and right test eyes EL and ER specified by the data processor 223. The main controller 211 can also adjust the interpupillary distance and the convergence angle by controlling the moving mechanisms 310 and 320 based on the specified three-dimensional positions of the left and right test eyes EL and ER. Furthermore, the main controller 211 can perform optical axis adjustment to substantially align the optical axis of the OCT optical system 8 (i.e., the optical axis of the measurement optical system 300 or the optical axis of the objective lens 51) with either the measurement optical axis OL or OR based on the specified three-dimensional positions of the left and right test eyes EL and ER.

[0142] Control of the XY alignment system 2 includes control of the XY alignment light source 21. Control of the XY alignment light source 21 includes turning the light source on and off, adjusting the light intensity, and adjusting the aperture. This switches the XY alignment light source 21 on and off and changes the light intensity. The main control unit 211 receives a signal detected by the image sensor 59 and controls the data processing unit 223 to identify the position of a bright spot image based on the return light from the XY alignment light source 21 based on the received signal. The main control unit 211 controls the movement mechanism 200 to move the head unit left and right, up and down so that the displacement of the bright spot image relative to a predetermined target position is canceled (XY alignment).

[0143] The control of the keratometry system 3 includes control of the keratometry light source 32. The control of the keratometry light source 32 includes turning the light source on and off, adjusting the light intensity, and adjusting the aperture. This causes the keratometry light source 32 to be switched on and off, or to change the light intensity. The main control unit 211 causes the calculation processing unit 220 (data processing unit 223) to perform known calculations on the keratometry image detected by the image sensor 59. This allows the corneal shape parameters of the subject's eye to be determined.

[0144] Control of the fixation projection systems 4L and 4R includes control of the liquid crystal panels 41L and 41R, control of the movement of the fixation units 40L and 40R, etc. Control of the liquid crystal panels 41L and 41R includes turning on and off the display of the fixation target, switching the fixation target according to the type of test or measurement, and switching the display position of the fixation target.

[0145] Furthermore, for example, the fixation projection systems 4L and 4R are provided with movement mechanisms that move the liquid crystal panels 41L and 41R (or the fixation units 40L and 40R) in the optical axis direction, respectively. Similar to the movement mechanism 200, these movement mechanisms are provided with an actuator that generates a driving force for moving the movement mechanism and a transmission mechanism that transmits the driving force. The main controller 211 controls the movement mechanisms by sending a control signal to the actuator, and moves at least the liquid crystal panels 41L and 41R in the optical axis direction, respectively. As a result, the positions of the liquid crystal panels 41L and 41R are adjusted so that the liquid crystal panel 41L and the fundus ELf, and the liquid crystal panel 41R and the fundus ERf, respectively, are optically conjugate with each other.

[0146] Control of the anterior-segment observation system 5 includes control of the anterior-segment illumination light source 50, control of the lens movement mechanism that moves the relay lens 56, and control of the image sensor 59. Control of the anterior-segment illumination light source 50 includes turning the light source on and off, adjusting the light intensity, and adjusting the aperture. This controls the anterior-segment illumination light source 50 and changes the light intensity. Like the movement mechanism 200, the lens movement mechanism includes an actuator that generates a driving force for moving the movement mechanism and a transmission mechanism that transmits the driving force. The main controller 211 controls the lens movement mechanism by sending a control signal to the actuator, thereby moving the relay lens 56 in the optical axis direction. Control of the image sensor 59 includes adjustment of the exposure, gain, and detection rate of the image sensor 59. The main controller 211 captures signals detected by the image sensor 59 and causes the arithmetic processor 220 to perform processing such as forming an image based on the captured signals.

[0147] Control of the reflective measurement projection system 6 includes control of the reflective measurement light source 61 and control of the rotary prism 66. Control of the reflective measurement light source 61 includes turning the light source on and off, adjusting the light intensity, and so on. This allows the reflective measurement light source 61 to be switched on and off, or the light intensity to be changed. For example, the reflective measurement projection system 6 includes a movement mechanism that moves the reflective measurement light source 61 in the optical axis direction. Similar to the movement mechanism 200, this movement mechanism includes an actuator that generates a driving force for moving the movement mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the movement mechanism by sending a control signal to the actuator, thereby moving the reflective measurement light source 61 in the optical axis direction. Control of the rotary prism 66 includes control of the rotation of the rotary prism 66. For example, a rotation mechanism that rotates the rotary prism 66 is provided, and the main control unit 211 rotates the rotary prism 66 by controlling this rotation mechanism.

[0148] Control of the REF measurement light-receiving system 7 includes control of the focusing lens 74. Control of the focusing lens 74 includes control of movement of the focusing lens 74 in the optical axis direction. For example, the REF measurement light-receiving system 7 includes a movement mechanism that moves the focusing lens 74 in the optical axis direction. Similar to the movement mechanism 200, this movement mechanism is provided with an actuator that generates a driving force for moving the movement mechanism and a transmission mechanism that transmits the driving force. The main controller 211 controls the movement mechanism by sending a control signal to the actuator, and moves the focusing lens 74 in the optical axis direction. The main controller 211 can move the REF measurement light source 61 and the focusing lens 74 in the optical axis direction, for example, in accordance with the refractive power of the left test eye EL, the refractive power of the fundus ERf, or the combined refractive power of the refractive power of the left test eye EL and the refractive power of the fundus ERf, so that the REF measurement light source 61 and the fundus ELf or the fundus ERf and the image sensor 59 are optically conjugate.

[0149] Control of the OCT optical system 8 includes control of the light source unit 101, control of the attenuator 105, control of the polarization controller 106, control of the zoom optical system 114, control of the CCD image sensor 115, control of the focusing lens 87, control of the optical scanner 88, and control of the optical path length change unit 89.

[0150] Control of the light source unit 101 includes turning the light source on and off, adjusting the light intensity, and adjusting the aperture. Control of the attenuator 105 includes adjusting the light intensity of the reference light LR. Control of the polarization controller 106 includes adjusting the polarization state of the reference light LR. Control of the zoom optical system 114 includes controlling the optical magnification. Control of the CCD image sensor 115 includes adjusting the exposure, gain, and detection rate of the CCD image sensor 115. The main control unit 211 captures signals detected by the CCD image sensor 115 and causes the arithmetic processing unit 220 to perform processes such as forming an image based on the captured signals.

[0151] Control of the focusing lens 87 includes control of movement of the focusing lens 87 in the optical axis direction. For example, the OCT optical system 8 includes a movement mechanism that moves the focusing lens 87 in the optical axis direction. Similar to the movement mechanism 200, this movement mechanism is provided with an actuator that generates a driving force for moving the movement mechanism, and a transmission mechanism that transmits this driving force. The main control unit 211 controls the movement mechanism by sending a control signal to the actuator, and moves the focusing lens 87 in the optical axis direction.

[0152] In some embodiments, the ophthalmologic apparatus 1 is provided with holding members that hold the focusing lenses 74 and 87 and a drive unit that drives the holding members. The main controller 211 controls the drive unit to control the movement of the focusing lenses 74 and 87. For example, the main controller 211 may move the focusing lens 87 in conjunction with the movement of the focusing lens 74, and then move only the focusing lens 87 based on the intensity of the interference signal.

[0153] Control of the optical scanner 88 includes setting a scan mode for scanning the measurement site with a predetermined scan pattern, controlling the scan range, and controlling the scan speed. By controlling the scan range (scan start position and scan end position), it is possible to control the angle range of the deflection plane that deflects the measurement light LS. By controlling the scan speed, it is possible to control the speed at which the angle of the deflection plane is changed. The main control unit 211 controls at least one of the scan mode, scan range, and scan speed by outputting a control signal to the optical scanner 88.

[0154] The control of the optical path length changing unit 89 includes control of the optical path length of the measurement light 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 measurement light LS.

[0155] Furthermore, the main control unit 211 performs processing to write data to the storage unit 212 and processing to read data from the storage unit 212 .

[0156] (Storage unit 212) The storage unit 212 stores various types of data. Examples of data stored in the storage unit 212 include objective measurement results (OCT measurement results), image data of OCT images, image data of anterior eye images, subjective test results, and information about the eye to be examined. The information about the eye to be examined includes information about the subject, such as a patient ID and name, and information about the eye to be examined, such as identification information for the left eye or right eye. The storage unit 212 also stores various programs and data for operating the ophthalmologic apparatus.

[0157] (Calculation processing unit 220) The arithmetic processing unit 220 includes a processor and executes various types of arithmetic processing. A storage unit (not shown, for example, the storage unit 212) stores computer programs for executing the various types of arithmetic processing in advance. The processor operates in accordance with the computer programs to realize the functions of the units that execute the various types of arithmetic processing.

[0158] As shown in FIG. 10, the arithmetic processing unit 220 includes an eye refractive power calculation unit 221, an image formation unit 222, and a data processing unit 223.

[0159] The eye refractive power calculation unit 221 calculates the refractive power of each of the left and right test eyes EL and ER based on the results of refractive measurements performed sequentially on both eyes. The image formation unit 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 unit 223 performs various data processing (image processing) and analysis processing on the measurement results (detection results of the interference light LC, etc.) obtained using the optical system provided in the ophthalmologic apparatus 1 and the OCT image formed by the image formation unit 222.

[0160] (Eye refractive power calculation unit 221) The ocular refractive power calculation unit 221 analyzes a ring image (pattern image) obtained by the image sensor 59 receiving the return light of the ring-shaped light beam (ring-shaped measurement pattern) projected onto the fundus ELf by the refraction measurement projection system 6, and calculates the refractive power value of the left subject's eye EL. The ocular refractive power calculation unit 221 also analyzes a ring image (pattern image) obtained by the image sensor 59 receiving the return light of the ring-shaped light beam projected onto the fundus ERf by the refraction measurement projection system 6, and calculates the refractive power value of the right subject's eye ER. For example, for each ring image, the ocular refractive power calculation unit 221 determines the center of gravity of the ring image from the luminance distribution in the image in which the ring image is rendered, determines luminance distributions along multiple scanning directions extending radially from this center of gravity, and identifies the ring image from this luminance distribution. Next, the ocular refractive power calculation unit 221 calculates an ellipse approximating the identified ring image, and calculates the spherical power, the astigmatic power, and the astigmatic axis angle by substituting the major axis and minor axis of the ellipse into a known formula. Alternatively, the ocular refractive power calculation unit 221 can calculate parameters of the ocular refractive power based on the deformation and displacement of the ring image relative to the reference pattern.

[0161] Furthermore, the ocular refractive power calculation unit 221 calculates the corneal refractive power, the degree of corneal astigmatism, and the corneal astigmatic axis angle of the left subject's eye EL based on the keratinizing image of the left subject's eye EL acquired by the anterior-segment observation system 5. Similarly, the ocular refractive power calculation unit 221 calculates the corneal refractive power, the degree of corneal astigmatism, and the corneal astigmatic axis angle of the right subject's eye ER based on the keratinizing image of the right subject's eye ER acquired by the anterior-segment observation system 5. For example, for each keratinizing image, the ocular refractive power calculation unit 221 calculates the corneal radii of curvature of the principal meridian and the principal meridian of the anterior surface of the cornea by analyzing the keratinizing image, and calculates the above parameters based on the corneal radii of curvature.

[0162] (Image forming unit 222) The image forming unit 222 forms image data of an OCT image (tomographic image) of the subject's eye based on the detection signal of the interference light LC obtained by the CCD image sensor 115. That is, the image forming unit 222 forms image data of the subject's eye based on the detection result of the interference light LC by the interference optical system. This processing includes filtering, FFT (Fast Fourier Transform), and other processes, similar to conventional spectral-domain OCT. The image data acquired in this manner is a data set including a group of image data formed by imaging the reflection intensity profiles of multiple A-lines (paths of each measurement light LS within the subject's eye).

[0163] To improve image quality, multiple data sets collected by repeating the same scan pattern multiple times can be superimposed (averaged).

[0164] (Data processing unit 223) The data processing unit 223 performs various data processing (image processing) and analysis processing on the tomographic image formed by the image forming unit 222. For example, the data processing unit 223 executes correction processing such as brightness correction and dispersion correction of the image. In addition, the data processing unit 223 performs various image processing and analysis processing on the image (anterior eye image, etc.) obtained using the anterior eye observation system 5.

[0165] The data processing unit 223 can form volume data (voxel data) of the subject's eye by performing known image processing such as interpolation processing for interpolating pixels between tomographic images. When displaying an image based on the volume data, the data processing unit 223 performs rendering processing on the volume data to form a pseudo three-dimensional image as seen from a specific line of sight.

[0166] The data processing unit 223 can perform known image processing, such as interpolation processing that interpolates pixels between OCT images (tomographic images) formed by the image forming unit 222, to form image data of a three-dimensional image of the fundus or the anterior segment of the eye. Note that the image data of a three-dimensional image refers to image data in which pixel positions are defined by a three-dimensional coordinate system. Image data of a three-dimensional image includes image data consisting of three-dimensionally arranged voxels. This image data is called volume data or voxel data. When displaying an image based on the volume data, the data processing unit 223 performs rendering processing (volume rendering, MIP (Maximum Intensity Projection), etc.) on the volume data to form image data of a pseudo three-dimensional image as viewed from a specific line of sight. This pseudo three-dimensional image is displayed on a display device such as the display unit 270.

[0167] It is also possible to form stack data of multiple tomographic images as image data of a three-dimensional image. Stack data is image data obtained by arranging multiple tomographic images obtained along multiple scan lines in a three-dimensional manner based on the positional relationship of the scan lines. In other words, stack data is image data obtained by expressing multiple tomographic images that were originally defined using separate two-dimensional coordinate systems using a single three-dimensional coordinate system (i.e., embedding them in a single three-dimensional space).

[0168] The data processing unit 223 can perform various rendering operations on the acquired three-dimensional data set (volume data, stack data, etc.) to generate B-mode images (longitudinal and axial cross-sectional images) at any cross-section, C-mode images (transverse and horizontal cross-sectional images) at any cross-section, projection images, shadowgrams, and the like. Images of any cross-section, such as B-mode images and C-mode images, are generated by selecting pixels (voxels) on a specified cross-section from the three-dimensional data set. Projection images are generated by projecting the three-dimensional data set in a predetermined direction (Z direction, depth direction, axial direction). Shadowgrams are generated by projecting a portion of the three-dimensional data set (e.g., partial data corresponding to a specific layer) in a predetermined direction. Images viewed from the front side of the subject's eye, such as C-mode images, projection images, and shadowgrams, are called en-face images.

[0169] The data processing unit 223 can construct a B-mode image or a front image (a vessel-enhanced image, angiogram) in which retinal blood vessels and choroidal blood vessels are emphasized based on data collected in time series by OCT scanning (for example, B-scan image data). For example, time-series OCT data can be collected by repeatedly scanning approximately the same region of the subject's eye.

[0170] In some embodiments, the data processor 223 compares time-series B-scan images obtained by B-scanning approximately the same region, and constructs an enhanced image in which the changed region is emphasized by converting pixel values ​​of the changed region in signal intensity into pixel values ​​corresponding to the changed region. Furthermore, the data processor 223 extracts information of a predetermined thickness of the desired region from the constructed multiple enhanced images and constructs the information as an en-face image, thereby forming an OCTA image.

[0171] Images generated by the data processing unit 223 (for example, a three-dimensional image, a B-mode image, a C-mode image, a projection image, a shadowgram, and an OCTA image) are also included in the OCT image.

[0172] Furthermore, the data processing unit 223 identifies a characteristic position corresponding to a characteristic portion of the anterior eye by analyzing each of the two photographed images acquired substantially simultaneously by the two anterior eye cameras as described above. The data processing unit 223 calculates the three-dimensional position of the characteristic portion (i.e., the three-dimensional position of the subject's eye) by applying known trigonometry to the positions of the two anterior eye cameras and the identified characteristic positions corresponding to the characteristic portions in the two photographed images. The calculated three-dimensional position can be used to align the optical system with the subject's eye.

[0173] Furthermore, the ophthalmologic apparatus 1 can measure intraocular parameters by performing an OCT scan on the left or right subject eye EL or ER. Examples of the intraocular parameters include the axial length, the thickness of a predetermined layer region, and the distance between predetermined sites.

[0174] In the first embodiment, the data processing unit 223 calculates the axial length as an intraocular parameter calculation unit. In this case, the data processing unit 223 can calculate the distance between a position corresponding to the corneal apex and a position corresponding to the retinal pigment epithelium (RPE) layer as the axial length based on the detection results of the interference light LC obtained by performing an OCT scan. For example, the data processing unit 223 identifies the position of the corneal apex and the RPE layer by identifying the position of the maximum value of the intensity of the interference signal corresponding to the detection results of the interference light LC, and calculates the distance between the two identified positions as the axial length. For example, the data processing unit 223 performs a segmentation process on the OCT image formed based on the detection results of the interference light LC, identifies the position of the corneal apex and the RPE layer from the identified multiple layer regions, and calculates the distance between the two identified positions as the axial length.

[0175] (Display section 270, operation section 280) The display unit 270 serves as a user interface unit and displays information under the control of the control unit 210.

[0176] The operation unit 280 is used as a user interface unit to operate the ophthalmic apparatus. The operation unit 280 includes various hardware keys (joystick, buttons, switches, etc.) provided in the ophthalmic apparatus. The operation unit 280 may also include various software keys (buttons, icons, menus, etc.) displayed on a touch panel display screen.

[0177] At least a part of the display unit 270 and the operation unit 280 may be integrally configured. A typical example of this is a touch panel display screen.

[0178] (Communication unit 290) The communication unit 290 has a function for communicating with an external device (not shown). The communication unit 290 has a communication interface according to the connection form with the external device. An example of the external device is an eyeglass lens measuring device for measuring the optical characteristics of a lens. The eyeglass lens measuring device measures the power of the eyeglass lens worn by the subject and inputs the measurement data to the ophthalmic apparatus 1. The external device may also be any ophthalmic apparatus, a device (reader) that reads information from a recording medium, or a device (writer) that writes information to a recording medium. Furthermore, the external device may also be a hospital information system (HIS) server, a DICOM (Digital Imaging and Communication in Medicine) server, a doctor's terminal, a mobile terminal, a personal terminal, a cloud server, or the like. The communication unit 290 may be provided in, for example, the processing unit 9.

[0179] The members and mechanisms for adjusting the optical axis of the OCT optical system 8 in any of the first to third adjustment examples are an example of an "optical axis adjustment unit" according to the embodiment. The data processing unit 223 is an example of an "intraocular parameter calculation unit" according to the embodiment. The anterior eye cameras 15LA, 15LB, 15RA, 15RB, and 15LR are an example of "two or more imaging units" according to the embodiment. The anterior eye camera 15LA is an example of a "first imaging unit" according to the embodiment. The anterior eye camera 15LR is an example of a "second imaging unit" according to the embodiment. The anterior eye camera 15RA is an example of a "third imaging unit" according to the embodiment. The refraction measurement projection system 6 and the refraction measurement light receiving system 7 are an example of a "refractive power measurement optical system" according to the embodiment.

[0180] <Example of operation> An example of the operation of the ophthalmologic apparatus 1 according to the first embodiment will be described.

[0181] 12 and 13 show an example of the operation of the ophthalmic apparatus 1. FIG. 12 is a flow diagram of an example of the operation of the ophthalmic apparatus 1 when performing REF measurement and OCT measurement sequentially. FIG. 13 is a flow diagram of an example of the processing of step S2 in FIG. 12. The storage unit 212 stores a computer program for realizing the processing shown in FIGS. 12 and 13. The main control unit 211 operates in accordance with this computer program to execute the processing shown in FIGS. 12 and 13.

[0182] Here, it is assumed that, before the start of the flow shown in FIG. 12, it has been determined in advance that the examination will be performed in either the near vision state or the near vision state.

[0183] (S1: Adjust the convergence angle) First, the main control unit 211 controls the movement mechanism 320 that rotates the dichroic mirrors ML and MR in accordance with the target distance corresponding to a predetermined near vision or far vision state, and adjusts the convergence angle.

[0184] As shown in FIG. 4, the dichroic mirrors ML and MR change the deflection direction of the optical axis deflected by the optical axis switching member SW.

[0185] (S2: Alignment) Subsequently, the main control unit 211 performs alignment. Details of step S2 will be described later.

[0186] In step S2, the measurement optical system 300 is aligned with the left and right eyes EL and ER to be examined.

[0187] (S3: Acquire images of the anterior segments of both eyes) Next, the main controller 211 controls the anterior eye observation system 5 to acquire anterior eye images of both eyes.

[0188] Specifically, the main controller 211 controls the keratometry system 3 to turn on the keratometry ring light source 32 and project a ring-shaped light beam onto the cornea CLr of the left subject's eye EL. Next, the main controller 211 controls the anterior-segment illumination light source 50 to turn on the anterior-segment illumination light source 50 and illuminate the anterior segment of the left subject's eye EL. The main controller 211 then acquires an anterior-segment image of the left subject's eye EL, depicting the anterior segment of the left subject's eye EL with a superimposed keratometry ring image, by capturing the reception result of the return light of the illumination light on the imaging surface of the imaging element 59. Similarly, the main controller 211 controls the keratometry system 3 to turn on the keratometry ring light source 32 and project a ring-shaped light beam onto the cornea CRr of the right subject's eye ER. Next, the main controller 211 controls the anterior-segment illumination light source 50 to turn on the anterior-segment illumination light source 50 and illuminate the anterior segment of the right subject's eye ER. Thereafter, the main control unit 211 acquires the result of receiving the return light of the illumination light on the imaging surface of the imaging element 59, thereby acquiring an image of the anterior segment of the right subject's eye ER, in which the anterior segment of the right subject's eye ER is depicted with a keratinizing image superimposed thereon.

[0189] (S4: Corneal shape analysis) Next, the main controller 211 analyzes the anterior eye images of both eyes acquired in step S3 by controlling the eye refractive power calculator 221. As described above, the eye refractive power calculator 221 identifies the keratinization images of the left and right examinee eyes EL and ER depicted in the anterior eye images, and calculates the corneal refractive power, the degree of corneal astigmatism, and the corneal astigmatism axis angle of the left and right examinee eyes EL and ER from the identified keratinization images.

[0190] (S5: Provisional measurement for each eye) Next, the main control unit 211 performs a provisional measurement for the refractive measurement for each eye. In the provisional measurement, the focusing state in the refractive measurement optical system is changed according to the refractive power of each of the left and right test eyes EL and ER. In the refractive measurement (main measurement), the refractive power of each of the left and right test eyes EL and ER is measured while the focusing state of the left and right test eyes EL and ER is promoted based on the focusing state changed in the provisional measurement.

[0191] For example, the reflector measurement light source 61 and the focusing lenses 74 and 87 are moved in the optical axis direction and positioned at positions corresponding to the refractive power of the subject's eye. The main control unit 211 turns on the reflector measurement light source 61 and starts rotating the rotary prism 66.

[0192] Here, it is assumed that provisional measurement is performed on the left eye EL, and then provisional measurement is performed on the right eye ER.

[0193] The main control unit 211 projects the ring-shaped measurement pattern light beam onto the left test eye EL. A ring image based on the return light of the measurement pattern light beam from the left test eye EL is formed on the imaging surface of the imaging element 59.

[0194] The main controller 211 determines whether or not a ring image based on the return light from the fundus detected by the imaging element 59 has been acquired. For example, the main controller 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 or not the width of the image (the difference between the outer diameter and the inner diameter) is equal to or greater than a predetermined value. Alternatively, the main controller 211 may determine whether or not a ring image has been acquired by determining whether or not a ring can be formed based on points (images) that are equal to or greater than a predetermined height (ring diameter).

[0195] When it is determined that the ring image has been acquired, the eye refractive power calculation unit 221 analyzes the ring image based on the return light of the projected measurement pattern light beam for the left test eye EL using a known method, and calculates a provisional spherical power S and provisional astigmatic power C.

[0196] Based on the calculated provisional spherical power S and cylindrical power C, the main control unit 211 moves the reflector measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to positions of the equivalent spherical power (S+C / 2).

[0197] Again, the main controller 211 projects the ring-shaped measurement pattern light beam onto the left eye EL. A ring image based on the return light of the measurement pattern light beam from the left eye EL is formed on the imaging surface of the imaging element 59. The main controller 211 determines whether or not the ring image based on the return light from the fundus ELf detected by the imaging element 59 has been acquired.

[0198] When it is determined that the ring image has been acquired, the eye refractive power calculation unit 221 analyzes the ring image based on the return light of the projected measurement pattern light beam for the left test eye EL using a known method, and calculates a provisional spherical power S and provisional astigmatic power C.

[0199] Subsequently, for the right eye ER, the provisional spherical power S and provisional astigmatic power C are similarly determined. At this time, the optical axis of the reflex measurement optical system is switched by the optical axis switching member SW as described above.

[0200] The main controller 211 controls the eye refractive power calculator 221 to calculate the intermediate power positions of the left and right eyes EL and ER. For example, the intermediate power position may be a position corresponding to the intermediate power ((ESR+ESL) / 2) between the spherical equivalent power ESR of the left eye EL and the spherical equivalent power ESL of the right eye ER.

[0201] The main control unit 211 moves the reflector measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to a position of intermediate diopter, which corresponds to a tentative far point.

[0202] In some embodiments, the main control unit 211 moves the reflex measurement light source 61, the focusing lens 74, and the liquid crystal panel 41 to the position of the equivalent spherical power in the provisional measurement of each of the left test eye EL and the right test eye ER without determining the intermediate power position.

[0203] (S6: Prompts clouding of both eyes) Next, the main control unit 211 further moves the liquid crystal panel 41 from the position determined in the provisional measurement in step S5 to the fogging position, thereby promoting fogging of both eyes simultaneously.

[0204] (S7: Refractive power measurement for each eye) Next, the main control unit 211 performs reflex measurement for each eye.

[0205] Here, it is assumed that after the refractive measurement is performed on the left eye EL, the refractive measurement is performed on the right eye ER.

[0206] Specifically, the main control unit 211 turns on the reflector measurement light source 61 if it is turned off. Also, the main control unit 211 starts the rotation of the rotary prism 66 if it is stopped. When measuring in a far-viewing state, the fixation target is a position corresponding to the far point obtained in step S5, as described above. When measuring in a near-viewing state, the fixation target is a predetermined fixed position.

[0207] The main controller 211 controls the refraction measurement projection system 6 and the refraction measurement light-receiving system 7 to acquire a ring image, similar to the provisional measurement in step S5. That is, the refraction measurement optical system projects a measurement pattern light beam for the left eye to be examined so that the focal position is a position corresponding to an intermediate refractive power between the refractive power of the left eye EL and the refractive power of the right eye ER, thereby acquiring a ring image. The main controller 211 causes the ocular refractive power calculation unit 221 to calculate the spherical power, astigmatic power, and astigmatic axis angle from the analysis result of the ring image and the movement amount of the focusing lens 74. The calculated spherical power, astigmatic power, and astigmatic axis angle are stored in the memory unit 212.

[0208] Subsequently, reflex measurement is similarly performed on the right eye ER, at which time the optical axis of the reflex measurement optical system is switched by the optical axis switching member SW as described above.

[0209] That is, the reflex measurement optical system projects a measurement pattern light beam onto the left eye EL along the measurement optical axis OL via the objective lens 51, and projects a measurement pattern light beam onto the right eye ER along the measurement optical axis OR, and receives the return light of the measurement pattern light beam from the left eye EL and the return light of the measurement pattern light beam from the right eye ER. The eye refractive power calculation unit 221 calculates the refractive power of the left eye EL based on the result of receiving the return light of the measurement pattern light beam from the left eye EL, and calculates the refractive power of the right eye ER based on the result of receiving the return light of the measurement pattern light beam from the right eye ER.

[0210] In some embodiments, the acquisition of the anterior segment image in step S3 and the corneal topography analysis in step S4 are performed simultaneously in step S7. In some embodiments, the alignment in step S2 is performed before proceeding to step S8.

[0211] (S8: OCT measurement for each eye) Next, the main controller 211 controls the OCT optical system 8 to perform OCT measurement for each eye.

[0212] Here, it is assumed that OCT measurement is performed on the left eye EL, and then OCT measurement is performed on the right eye ER.

[0213] For example, the main controller 211 presents a fixation target for OCT measurement to the left subject's eye EL, controls the OCT optical system 8 to perform provisional OCT measurement, and acquires an adjustment tomographic image for adjusting the reference position of the measurement range in the depth direction. Specifically, the main controller 211 controls the optical scanner 88 to deflect the measurement light LS generated based on the light L0 emitted from the light source unit 101 and scan a predetermined portion of the left subject's eye EL (e.g., the fundus) with the deflected measurement light LS. The detection result of the interference light LC obtained by scanning with the measurement light LS is sent to the image forming unit 222. The image forming unit 222 forms a tomographic image (OCT image) of the left subject's eye EL from the obtained interference signal.

[0214] Next, the main controller 211 adjusts the reference position of the measurement range in the depth direction (Z direction). For example, the main controller 211 causes the data processor 223 to identify a predetermined site (e.g., the sclera) in the obtained tomographic image, and sets a position a predetermined distance away in the depth direction from the position of the identified predetermined site as the reference position of the measurement range. Alternatively, a predetermined position may be set as the reference position of the measurement range so that the optical path lengths of the measurement light LS and the reference light LR are approximately the same.

[0215] Next, the main controller 211 executes focus adjustment control and polarization adjustment control. For example, the main controller 211 moves the focusing lens 87 by a predetermined distance, and then controls the OCT unit 100 to perform OCT measurement.

[0216] The main controller 211 causes the data processor 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 processor 223 calculates a predetermined evaluation value related to the image quality of the OCT image and determines whether the calculated evaluation value is equal to or less than a threshold. In some embodiments, the focus adjustment is continued until the calculated evaluation value is equal to or less than the threshold. That is, when the evaluation value is equal to or less than the threshold, the focus state of the measurement light LS is determined to be appropriate, and the focus adjustment is continued until the focus state of the measurement light LS is determined to be appropriate.

[0217] In some embodiments, the main controller 211 performs the above-described repetitive OCT measurements to acquire interference signals, while monitoring the intensities (interference intensity, interference sensitivity) of the successively acquired interference signals. Furthermore, while performing this monitoring process, the main controller 211 moves the focusing lens 87 to search for the position of the focusing lens 87 where the interference intensity is maximized. By performing such focus adjustment, the focusing lens 87 can be guided to a position where the interference intensity is optimized.

[0218] Furthermore, the data processing unit 223 analyzes the detection results of the interference light obtained by the OCT measurement, and determines the polarization state of at least one of the measurement light LS and the reference light LR.

[0219] For example, the main control unit 211 performs repetitive OCT measurement while controlling the polarization controller 106 according to a predetermined algorithm. In some embodiments, the main control unit 211 controls the attenuator 105 to change the attenuation of the reference light LR. The data processing unit 223 calculates a predetermined evaluation value related to the image quality of the OCT image by analyzing the detection results of the interference light LC repeatedly acquired by the OCT measurement, and determines whether the calculated evaluation value is equal to or less than a threshold. This threshold is set in advance. The polarization adjustment is continued until the calculated evaluation value is equal to or less than the threshold. In other words, when the evaluation value is equal to or less than the threshold, it is determined that the polarization state of the measurement light LS is appropriate, and the polarization adjustment is continued until it is determined that the polarization state of the measurement light LS is appropriate.

[0220] In some embodiments, the main controller 211 can also monitor the interference intensity during polarization adjustment.

[0221] When the depth position adjustment, focus adjustment, and polarization adjustment are completed, the main controller 211 controls the optical scanner 88 to scan a predetermined region of the fundus of the left subject eye EL with the measurement light LS. For example, a detection signal obtained by scanning with the measurement light LS is sent to the image forming unit 222. The image forming unit 222 forms a tomographic image of the fundus from the obtained detection signal.

[0222] Next, OCT measurement is performed on the right eye ER in the same manner. At this time, the optical axis of the OCT optical system 8 is switched by the optical axis switching member SW as described above.

[0223] In some embodiments, before performing OCT measurement using the measurement light LS on one of the left test eye EL and the right test eye ER, the main controller 211 controls the OCT optical system 8 to adjust the optical path length of the reference optical path based on the axial length and refractive power of the other of the left test eye EL and the right test eye ER. That is, focusing on the fact that the optical path length of the reference optical path, which is one of the measurement environments for OCT measurement, can be correlated with the axial length and refractive power of the test eye and that the optical path lengths of the reference optical paths are often substantially the same for the left and right eyes, the optical path length of the reference optical path during the OCT measurement of the test eye performed first is determined based on the axial length and refractive power of the test eye, and the optical path length of the reference optical path during the OCT measurement of the test eye performed next is adjusted to the determined optical path length. This significantly reduces the time required for OCT measurement of both eyes.

[0224] The main controller 211 controls the data processor 223 for each of the left and right examinee eyes EL and ER to calculate the distance between the position corresponding to the corneal apex and the position corresponding to the RPE layer as the axial length based on the obtained detection signals or tomographic images. The data processor 223 can calculate intraocular parameters other than the axial length. For example, the main controller 211 controls the OCT optical system 8 to sequentially or simultaneously scan the fundus and cornea (anterior segment). The main controller 211 controls the data processor 223 to calculate the distance between the position corresponding to the corneal apex and the position corresponding to the RPE layer as the axial length based on the detection signals or tomographic images obtained by scanning the cornea and the detection signals or tomographic images obtained by scanning the fundus. A method for calculating such axial length is disclosed, for example, in Japanese Patent Application Laid-Open No. 2020-044027.

[0225] This is the end of the operation of the ophthalmologic apparatus 1 (END).

[0226] In some embodiments, the processing of steps S1 to S8 is performed for one of distance viewing and near viewing, and then the processing of steps S1 to S8 is performed for the other of distance viewing and near viewing, thereby performing the examination in both distance viewing and near viewing states.

[0227] Step S2 in FIG. 12 is executed as shown in FIG.

[0228] (S21: Identify the pupil positions of both eyes) First, the main controller 211 identifies characteristic positions of both eyes from captured images obtained by controlling the anterior eye cameras 15LA, 15RA, 15LB, and 15RB. In this embodiment, the main controller 211 identifies the pupil position as the characteristic position.

[0229] Specifically, the main controller 211 controls the anterior eye cameras 15LA and 15LB to capture images of the left subject's eye EL from different directions substantially simultaneously to acquire two captured images (anterior eye images). Similarly, the main controller 211 controls the anterior eye cameras 15RA and 15RB to capture images of the right subject's eye ER from different directions substantially simultaneously to acquire two captured images. In some embodiments, the two captured images of the left subject's eye EL and the two captured images of the right subject's eye ER are captured substantially simultaneously.

[0230] The process for specifying the pupil position of the left eye EL is the same as the process for specifying the pupil position of the right eye ER. Hereinafter, the process for specifying the pupil position of the left eye EL will be mainly described.

[0231] The main control unit 211 controls the data processing unit 223, which functions as a characteristic position identification unit, to analyze the two captured images obtained by the anterior eye cameras 15LA and 15LB and identify the pupil position (pupil center position or pupil center of gravity position) of the left test eye EL.

[0232] In this case, the data processing unit 223 identifies an image region corresponding to the pupil (pupil region) for each captured image based on the distribution of pixel values ​​(such as brightness values). Since the pupil is generally depicted with lower brightness than other parts of the body, the pupil region can be identified by searching for an image region with low brightness. At this time, the pupil region may be identified taking into consideration the shape of the pupil. In other words, the pupil region can be identified by searching for an image region with a substantially circular shape and low brightness.

[0233] Next, data processing unit 223 identifies the center position of the identified pupil region. Because the pupil is approximately circular as described above, the outline of the pupil region is identified, and the center position of this outline (an approximate circle or ellipse) is identified and can be used as the pupil center position. Alternatively, the center of gravity of the pupil region may be found, and this center position may be used as the pupil center position.

[0234] The data processing unit 223 can sequentially identify the pupil position for the images sequentially obtained by the anterior eye cameras 15LA and 15LB. The data processing unit 223 may also identify the pupil position for every arbitrary number of frames (one or more) for the images sequentially obtained by the anterior eye cameras 15LA and 15LB.

[0235] Next, the data processing unit 223, as a three-dimensional position calculation unit, specifies the three-dimensional position of the characteristic position as the three-dimensional position of the subject's eye based on the positions of the anterior eye cameras 15LA and 15LB and the specified pupil positions. For example, as disclosed in Japanese Patent Application Laid-Open No. 2013-248376, the data processing unit 223 calculates the three-dimensional position of the subject's eye by applying known trigonometry to the positions (known) of the two anterior eye cameras 15LA and 15LB and the pupil positions in the two captured images.

[0236] The pupil position of the right eye ER can also be identified by the same process as above.

[0237] (S22: Move the measurement optical axis) Based on the pupil positions of both eyes identified in step S21, the main control unit 211 controls the movement of the measurement optical system 300, the adjustment of the interpupillary distance using the optical axis switching member SW, and the position of the fixation target presented by the fixation projection systems 4L and 4R.

[0238] Specifically, the interpupillary distance is determined from the pupil positions of both eyes determined in step S21. For example, the main controller 211 adjusts at least one of the moving mechanism 200, the moving mechanism 310, and the fixation projection systems 4L and 4R so that the pupil positions of both eyes determined in step S21 are closest to (substantially coincide with) the known measurement optical axes OL and OR, respectively. The main controller 211 controls the moving mechanism 200 to change the relative position of the measurement optical system 300 with respect to the left and right eyes EL and ER. The main controller 211 controls the moving mechanism 310 to move the optical axis switching member SW to change the distance between the measurement optical axes OL and OR. The main controller 211 controls the fixation projection systems 4L and 4R to change the fixation positions (presentation positions of fixation targets) of the left and right eyes EL and ER, respectively.

[0239] As a result, the positions of the left eye EL in the X and Y directions are adjusted to approximately coincide with the positions of the measurement optical axis OL in the X and Y directions, and the distance in the Z direction is adjusted to a predetermined working distance.

[0240] In some embodiments, the main controller 211 determines whether the arrangement direction of the left eye EL and the right eye ER to be examined is parallel to the X direction (i.e., whether the heights of the eyes are misaligned) based on the pupil positions of the eyes identified in step S21. In this case, the main controller 211 can change at least one of the deflection direction of the optical axis switching member SW and the deflection directions of the dichroic mirrors ML and MR by controlling the movement mechanisms 310 and 320 based on the pupil positions of the eyes identified in step S21.

[0241] In some embodiments, when it is determined that the arrangement direction of the left eye EL and the right eye ER is not parallel to the X direction, the main controller 211 can control the display unit 270 to prompt the subject to tilt their face. The main controller 211 may also prompt the subject to tilt their face by outputting a sound.

[0242] (S23: Acquire images of the anterior segments of both eyes) Next, the main control unit 211 turns on the XY alignment light source 21, and then again controls the anterior eye cameras 15LA, 15RA, 15LB, and 15RB to acquire anterior eye images of both eyes in which XY bright spot images are depicted based on the reflected light from the XY alignment light source 21.

[0243] (S24: XY bright spot image detected?) Next, the main control unit 211 controls the data processing unit 223 to detect an XY bright point image from the anterior eye segment images of both eyes acquired in step S23.

[0244] For example, the data processing unit 223 detects whether or not an XY bright spot image is depicted based on pixel values ​​for each of the two anterior eye images of the left eye EL and the two anterior eye images of the right eye ER. When the data processing unit 223 detects that an XY bright spot image is depicted in all of the four anterior eye images (S24: Y), the operation of the ophthalmic apparatus 1 proceeds to step S25. When the data processing unit 223 detects that an XY bright spot image is not depicted in at least one of the four anterior eye images (S24: N), the operation of the ophthalmic apparatus 1 proceeds to step S22.

[0245] (S25: Identify the position of the XY bright spot image of both eyes) When XY bright point images are detected in the anterior eye images of both eyes in step S24 (S24:Y), the main controller 211 controls the data processor 223 to identify the positions of the XY bright point images of both eyes detected in step S24. In step S25, the positions of the XY bright point images of both eyes are identified by the same identification process as in step S21. That is, instead of the pupil positions of both eyes identified in step S21, the positions of the XY bright point images of both eyes identified in step S25 are identified.

[0246] (S26: Move the measurement optical axis) Based on the positions of the XY bright spot images of both eyes identified in step S25, the main control unit 211 controls the movement of the measurement optical system 300, the adjustment of the interpupillary distance using the optical axis switching member SW shown in Figure 3, and the position of the fixation target presented by the fixation projection systems 4L and 4R.

[0247] In step S26, the measurement optical axis is adjusted in the same manner as in step S22.

[0248] (S27: Acquire images of the anterior segments of both eyes) Next, the main controller 211 controls the anterior eye cameras 15LA, 15RA, 15LB, and 15RB to acquire anterior eye images of both eyes.

[0249] (S28: Identify the position of the XY bright spot image of both eyes) Next, similarly to step S25, the main controller 211 controls the data processor 223 to specify the positions of the XY bright spot images of both eyes from the anterior eye images of both eyes acquired in step S27.

[0250] (S29: Alignment complete?) Next, the main control unit 211 determines whether or not each of the positions of the XY bright point images of both eyes identified in step S28 is within a predetermined alignment completion range.

[0251] When it is determined that the positions of the XY bright spot images of both eyes are within the predetermined alignment completion range (S29: Y), the processing of step S2 in Fig. 12 is completed (END). When it is determined that at least one of the positions of the XY bright spot images of both eyes is not within the predetermined alignment completion range (S29: N), the operation of the ophthalmologic apparatus 1 proceeds to step S26.

[0252] As described above, in step S2 of Figure 12, the main control unit 211 changes the relative position of the OCT optical system 8 with respect to the left test eye EL and the right test eye ER based on two or more images obtained by two or more anterior eye cameras, and changes the direction of the measurement optical axis OL and the direction of the measurement optical axis OR, as well as the distance between the measurement optical axis OL and the measurement optical axis OR, so that the measurement optical axis OL coincides with the visual axis of the left test eye EL and the measurement optical axis OR coincides with the visual axis of the right test eye ER.

[0253] As described above, according to the first embodiment, the optical axis switching member SW is used to switch the optical axis of the measurement optical system 300 (specifically, the optical axis of the OCT optical system 8 and the reflex measurement optical system optically coaxially coupled with the optical axis of the OCT optical system 8) so that it substantially coincides with one of the measurement optical axes OL and OR that are arranged apart from each other. This makes it possible to perform OCT measurements on both eyes sequentially with both eyes open. This makes it possible to provide an ophthalmic device that is low-cost, space-saving, and capable of measuring the characteristics of both eyes with high accuracy. In particular, it is possible to reduce the size and cost of the optical system of an ophthalmic device that can perform OCT measurements on both eyes.

[0254] [Second embodiment] In the first embodiment, the fixation projection systems 4L and 4R are provided in the transmission direction of the dichroic mirrors ML and MR, but the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this. For example, the measurement optical system may include a fixation projection system common to both eyes.

[0255] The ophthalmic apparatus according to the second embodiment will be described below, focusing on the differences from the ophthalmic apparatus 1 according to the first embodiment.

[0256] 14 and 15 show an example of the configuration of the optical system of the ophthalmic apparatus according to the second embodiment. Similar to Fig. 1, Fig. 14 is a schematic diagram of the configuration of the optical system of the ophthalmic apparatus according to the second embodiment as viewed from above. Fig. 15 is a block diagram of an example of the configuration of the measurement optical system 300a of Fig. 14.

[0257] The configuration of the optical system of the ophthalmic apparatus 1a according to the second embodiment differs from the configuration of the optical system of the ophthalmic apparatus 1 according to the first embodiment in that a reflective mirror ML1 is provided instead of the dichroic mirror ML, a reflective 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.

[0258] The reflecting mirror ML1 deflects the measurement optical axis OL deflected by the optical axis switching member SW toward the left eye EL, and the reflecting mirror MR1 deflects the measurement optical axis OR deflected by the optical axis switching member SW toward the right eye ER.

[0259] As shown in FIG. 15, the measurement optical system 300a includes a keratometry system 3, a fixation projection system 4, an anterior segment observation system 5, a reflex measurement projection system 6, a reflex measurement light receiving system 7, and an OCT optical system 8.

[0260] Like the ophthalmic apparatus 1, the ophthalmic apparatus 1a also includes an optical axis adjustment unit, an interpupillary distance adjustment unit, and a convergence angle adjustment unit.

[0261] Fig. 16 is an explanatory diagram of an example of the operation of the interpupillary distance adjusting unit in the ophthalmologic apparatus 1a according to the second embodiment. In Fig. 16, the same parts as those in Fig. 3 or 14 are denoted by the same reference numerals, and the description thereof will be omitted as appropriate.

[0262] As in the first embodiment, the interpupillary distance adjustment unit changes the distance in the X direction between the measurement optical axes OL and OR by moving the optical axis switching member SW along the measurement optical axis OL or the measurement optical axis OR (Z direction, the optical axis of the measurement optical system 300). As a result, as shown in FIG. 16 , the positions of the optical axes deflected by the reflecting mirrors ML1 and MR2 change, and 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′ and OR′ becomes the interpupillary distance PD′, and the interpupillary distance is changed.

[0263] In some embodiments, the interpupillary distance is changed by moving the optical axis switching member SW in the X direction shown in FIG.

[0264] In some embodiments, the optical axis switching member SW is controlled by a control unit (described later) and moved by a movement mechanism (not shown). In this case, the function of the interpupillary distance adjustment unit is realized by the control unit and the movement mechanism (not shown). In some embodiments, the optical axis switching member SW is moved manually by a movement mechanism (not shown). In this case, the function of the interpupillary distance adjustment unit is realized by the movement mechanism (not shown).

[0265] 17 is an explanatory diagram showing an example of the operation of the convergence angle adjusting unit in the ophthalmologic apparatus 1a according to the second embodiment. In Fig. 17, the same parts as those in Fig. 4 or 14 are denoted by the same reference numerals, and the description thereof will be omitted as appropriate.

[0266] As in the first embodiment, the convergence angle adjuster changes the orientation of at least one of the reflecting mirror ML1 and the reflecting mirror MR1, thereby changing the orientation of at least one of the measurement optical axes OL and OR.

[0267] For example, the deflection surface of the reflecting mirror ML1 is configured to be rotatable around a rotation axis extending in the Y-axis direction. For example, the deflection surface of the reflecting mirror MR1 is configured to be rotatable around a rotation axis extending in the Y-axis direction. As a result, as shown in Fig. 17, the measurement optical axis OL deflected by the reflecting mirror ML1 becomes the measurement optical axis OL', and the measurement optical axis OR becomes the measurement optical axis OR', changing the convergence angle.

[0268] In some embodiments, the reflecting mirrors ML1 and MR1 are controlled by a control unit (described later) and rotated by a moving mechanism (rotating mechanism) not shown. In this case, the function of the convergence angle adjustment unit is realized by the control unit and the moving mechanism (not shown). In some embodiments, the reflecting mirrors ML1 and MR1 are rotated manually by a moving mechanism (rotating mechanism) not shown. In this case, the function of the convergence angle adjustment unit is realized by the moving mechanism (not shown).

[0269] Fig. 18 shows an example of the configuration of the measurement optical system 300a according to the second embodiment. Like Fig. 5, Fig. 18 is a schematic representation of an example of the configuration of the measurement optical system 300a viewed from the side (X direction). In Fig. 18, parts that are the same as those in Fig. 5 or 14 are given the same reference numerals, and descriptions thereof will be omitted where appropriate.

[0270] The configuration of the measurement optical system 300a differs from that of the measurement optical system 300 in that a dichroic mirror 83, a reflecting mirror 84, and a fixation projection system 4 are provided between the relay lens 82 and the relay lens 85, and the dichroic mirror 83 is configured to coaxially couple the optical path of the fixation projection system 4 to the optical path of the OCT optical system 8.

[0271] The dichroic mirror 83 transmits light having wavelength components in the visible region and reflects light having wavelength components in the near-infrared region (or infrared region). The fixation projection system 4 is disposed in the transmission direction of the dichroic mirror 83, and the OCT optical system 8 is disposed in the reflection direction of the dichroic mirror 83. Specifically, the dichroic mirror 83 is disposed between the relay lens 82 and the fixation projection system 4, and a reflecting mirror 84 is disposed between the dichroic mirror 83 and the OCT optical system 8.

[0272] The fixation projection system 4 projects a fixation light beam onto the fundus ELf of the left subject eye EL or the fundus ERf of the right subject eye ER, which is located on a measurement optical axis optically coaxially coupled to the optical axis of the objective lens 51 (measurement optical system 300), thereby presenting a fixation target to the left subject eye EL or the right subject 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 the fixation target under the control of the control unit. The fixation position of the left subject eye EL or the right subject eye ER can be changed by changing the display position of the pattern on the screen of the liquid crystal panel 41. The fixation unit 40 is also movable in the optical axis direction under the control of the control unit.

[0273] The light from the liquid crystal panel 41 passes through relay lenses 42 , 43 , and 44 , passes through a dichroic mirror 83 , and is projected onto the subject's eye along the same path as the measurement light LS from the OCT optical system 8 .

[0274] In some embodiments, the fixation unit 40 is movable in the optical axis direction independently of the relay lenses 43, 44.

[0275] Also in the second embodiment, as in the first embodiment, the optical axis of the OCT optical system 8 can be adjusted. For example, by using a reflecting mirror 84 as the deflecting member DF1 and a dichroic mirror 83 as the deflecting member DF2, the optical axis of the OCT optical system 8 can be adjusted as shown in the first adjustment example of FIG. 9A. Also in the second embodiment, the optical axis of the OCT optical system 8 can be adjusted as shown in the second adjustment example of FIG. 9B. Furthermore, in a third adjustment example in which the deflection direction of the optical axis of the OCT optical system 8 is changed by an optical member in the path of the measurement light, examples of the optical member that can be used include the reflecting mirror 81, dichroic mirror 52, dichroic mirror 83, reflecting mirror 84, and a reflecting mirror not shown in FIG. 18.

[0276] The fixation projection system 4 is an example of a "fixation optical system" according to the embodiment. The dichroic mirror 83 is an example of an "optical path coupling member" according to the embodiment. The reflecting mirror ML1 is an example of a "first reflecting member" according to the embodiment. The reflecting mirror MR1 is an example of a "second reflecting member" according to the embodiment. The convergence angle adjustment unit is an example of a "first adjustment unit" according to the embodiment. The deflection surface of the optical axis switching member SW, the deflection surface of the reflecting mirror ML1, and the movement mechanism that rotates the deflection surface of the reflecting mirror MR1 are examples of a "second adjustment unit" according to the embodiment.

[0277] Fig. 19 shows an example of the functional configuration of the processing system of the ophthalmic apparatus 1a according to the second embodiment. Fig. 19 shows an example of a functional block diagram of the processing system of the ophthalmic apparatus 1a. In Fig. 19, parts that are the same as those in Fig. 10 or 18 are given the same reference numerals, and descriptions thereof will be omitted as appropriate.

[0278] The configuration of the processing system of the ophthalmic apparatus 1a differs from the configuration of the processing system of the ophthalmic apparatus 1 shown in Figure 10 in that a fixation projection system 4 is provided instead of the fixation projection systems 4L and 4R, and a processing unit 9a is provided instead of the processing unit 9.

[0279] The configuration of the processing unit 9a differs from the configuration of the processing unit 9 shown in Fig. 10 in that a control unit 210a is provided instead of the control unit 210. The control unit 210a includes a main control unit 211a and a storage unit 212a. The main control unit 211a can perform the same control as the main control unit 211, except that the main control unit 211a controls the fixation projection system 4 instead of the control of the fixation projection systems 4L and 4R by the main control unit 211. The storage unit 212a stores the same programs as the storage unit 212, except for the process of executing control over the fixation projection systems 4L and 4R.

[0280] The operation of the ophthalmic apparatus 1a according to the second embodiment is almost the same as the operation of the ophthalmic apparatus 1 according to the first embodiment shown in FIGS.

[0281] In the second embodiment, with the same fixation target presented to both eyes with both eyes open, OCT measurement and REF measurement can be performed sequentially for each eye.

[0282] Specifically, instead of the main control unit 211 controlling the fixation projection systems 4L and 4R to present independent fixation targets to the left and right test eyes EL and ER, the main control unit 211a controls the fixation projection system 4 so as to present the same fixation target to the left and right test eyes EL and ER.

[0283] For example, when performing an examination in a distance viewing state in step S7 of Figure 12, the main control unit 211a presents a fixation target to both eyes from a position corresponding to the provisional spherical power S and provisional astigmatic power C (or equivalent spherical power) on the more positive side (distance viewing side) of the provisional spherical power S and provisional astigmatic power C (or equivalent spherical power) of the left test eye EL and the provisional spherical power S and provisional astigmatic power C (or equivalent spherical power) of the right test eye ER, which were calculated in step S5 of Figure 12.

[0284] For example, when performing an examination in a near vision state in step S7 of Fig. 12, the main controller 211a presents a fixation target to both eyes from a position similar to that in the examination in a far vision state. In some embodiments, when the subject has monovision, the main controller 211a presents a fixation target to both eyes from a position corresponding to the provisional spherical power S and provisional astigmatic power C (or equivalent spherical power) on the more negative side (near vision side) of the provisional spherical power S and provisional astigmatic power C (or equivalent spherical power) of the left eye EL and the provisional spherical power S and provisional astigmatic power C (or equivalent spherical power) of the right eye ER, which were calculated in step S5 of Fig. 12. At this time, the main controller 211a can adjust the convergence angle by controlling the reflecting mirrors ML1 and ML2 as necessary.

[0285] 13, the main controller 211a can determine whether the arrangement direction of the left eye EL and the right eye ER to be examined is parallel to the X direction (i.e., whether the heights of the eyes are misaligned) based on the pupil positions of the eyes identified in step S21. In this case, the main controller 211a, as the second adjuster, can adjust the arrangement directions of the measurement optical axis OL and the measurement optical axis OR by changing the deflection direction of the reflecting mirror ML1, the deflection direction of the reflecting mirror MR1, and the orientation of the deflection surface of the optical axis switching member SW based on the pupil positions of the eyes identified in step S21.

[0286] In some embodiments, the main controller 211a can perform refractive power measurement while viewing a fixation target with both eyes by switching the optical axis at high speed using the optical axis switching member SW. At this time, the main controller 211a acquires multiple ring images based on the return light of the measurement pattern light beams for the left and right eyes when switching the optical axis, and calculates the refractive power value by analyzing an image in which the acquired ring images are superimposed.

[0287] In some embodiments, in the configuration according to the second embodiment, a horopter may be provided in front of both eyes, or a trial lens may be placed.

[0288] As described above, according to the second embodiment, similar to the first embodiment, it is possible to provide an ophthalmic apparatus capable of measuring the characteristics of both eyes with high accuracy at low cost and in a small space. In particular, it is possible to reduce the size and cost of the optical system of the ophthalmic apparatus capable of performing OCT measurement on both eyes.

[0289] [Third embodiment] In the first embodiment, the fixation projection systems 4L and 4R are provided in the transmission direction of the dichroic mirrors ML and MR, but the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this. For example, a visual target presentation unit common to both eyes may be provided in the transmission direction of the dichroic mirrors ML and MR.

[0290] The ophthalmic apparatus according to the third embodiment will be described below, focusing on the differences from the ophthalmic apparatus 1 according to the first embodiment.

[0291] Fig. 20 shows an example of the configuration of the optical system of the ophthalmic apparatus according to the third embodiment. Similar to Fig. 1, Fig. 20 schematically shows the configuration of the optical system of the ophthalmic apparatus according to the third embodiment when viewed from above.

[0292] The difference between the configuration of the optical system of the ophthalmic device 1b according to the third embodiment and the configuration of the optical system of the ophthalmic device 1 according to the first embodiment is that a target presentation unit 400 is provided instead of the fixation projection systems 4L and 4R.

[0293] The optotype presentation unit 400 includes an optotype chart. For example, the optotype chart is a transmissive optotype chart that is placed between an illumination light source and the subject's eye and displays a fixation target. In some embodiments, the optotype chart is a transmissive film on which a fixation target is printed. Examples of fixation targets include a landscape chart and a dot optotype.

[0294] When performing reflex measurement, the control unit turns on the illumination light source and illuminates the target chart with light from the illumination light source. The light that passes through the target chart passes through the dichroic mirrors ML and MR as fixation light and is projected onto the left and right test eyes EL and ER.

[0295] The dichroic mirror ML is an example of a "first optical path coupling member" according to the embodiment. The dichroic mirror MR is an example of a "second optical path coupling member" according to the embodiment.

[0296] Fig. 21 shows an example of the functional configuration of a processing system of an ophthalmic apparatus 1b according to the third embodiment. Fig. 21 shows an example of a functional block diagram of the processing system of the ophthalmic apparatus 1b. In Fig. 21, parts that are the same as those in Fig. 10 or 20 are given the same reference numerals, and descriptions thereof will be omitted as appropriate.

[0297] The configuration of the processing system of the ophthalmic apparatus 1b differs from the configuration of the processing system of the ophthalmic apparatus 1 shown in Figure 10 in that the fixation projection systems 4L and 4R are omitted and that a processing unit 9b is provided instead of the processing unit 9.

[0298] The configuration of the processing unit 9b differs from the configuration of the processing unit 9 shown in Fig. 10 in that a control unit 210b is provided instead of the control unit 210. The control unit 210b includes a main control unit 211b and a storage unit 212b. The main control unit 211b can perform the same control as the main control unit 211, except that the control of the fixation projection systems 4L and 4R by the main control unit 211 is omitted. The storage unit 212b stores the same programs as the storage unit 212, except for the process of executing control over the fixation projection systems 4L and 4R.

[0299] The operation of the ophthalmic apparatus 1b according to the third embodiment is almost the same as the operation of the ophthalmic apparatus 1 according to the first embodiment shown in Figures 12 and 13, except that control of the fixation projection systems 4L and 4R is omitted.

[0300] In the third embodiment, the same fixation target is presented to both eyes in the REF measurement, keratometry, and OCT measurement. That is, with the same fixation target presented to both eyes with both eyes open, the REF measurement can be performed sequentially for each eye. Also, with the same fixation target presented to both eyes with both eyes open, the OCT measurement can be performed sequentially for each eye.

[0301] In some embodiments, the visual target presentation unit 400 presents the visual target in response to an operation by the examiner. In some embodiments, the visual target presentation unit 400 presents the visual target under control of the main controller 211b. In this case, the main controller 211b controls the visual target presentation unit 400 in the same manner as the control over the fixation projection system 4 according to the second embodiment.

[0302] In some embodiments, in the configuration according to the third embodiment, a horopter may be provided in front of both eyes, or a trial lens may be placed.

[0303] As described above, according to the third embodiment, it is possible to provide an ophthalmic apparatus capable of measuring the characteristics of both eyes with high accuracy at low cost and in a small space, similar to the first embodiment. In particular, it is possible to reduce the size and cost of the optical system of an ophthalmic apparatus capable of performing OCT measurement on both eyes.

[0304] [Effect] An ophthalmologic apparatus according to an embodiment will be described.

[0305] A first aspect of the embodiment is an ophthalmic apparatus (1, 1a, 1b) including an objective lens (51), an OCT optical system (8), an optical axis switching member (SW), control units (210, 210a, 210b, main control units 211, 211a, 211b), and an intraocular parameter calculation unit (data processing unit 223). The OCT optical system splits light (L0) from a light source (light source unit 101) into measurement light (LS) and reference light (LR), projects the measurement light via the objective lens onto a left subject's eye (EL) positioned on a first measurement optical axis (measurement optical axis OL) or a right subject's eye (ER) positioned on a second measurement optical axis (measurement optical axis OR), and detects interference light (LC) between return light of the measurement light from the left subject's eye or the right subject's eye and the reference light passing through the reference optical path. The optical axis switching member switches the optical axis of the OCT optical system so that it substantially coincides with either the first measurement optical axis or the second measurement optical axis. The control unit controls the optical axis switching member. The intraocular parameter calculation unit calculates an intraocular parameter (e.g., axial length) of the left subject's eye based on a detection result of the interference light obtained in a state where the optical axis of the OCT optical system is switched to approximately coincide with the first measurement optical axis, and calculates an intraocular parameter (e.g., axial length) of the right subject's eye based on a detection result of the interference light obtained in a state where the optical axis of the OCT optical system is switched to approximately coincide with the second measurement optical axis.

[0306] According to this aspect, it is possible to perform OCT measurement on both eyes with both eyes open using a single OCT optical system, thereby providing an ophthalmic apparatus that is low-cost, space-saving, and capable of measuring the characteristics of both eyes with high accuracy.

[0307] In a second aspect of the embodiment, in the first aspect, before performing OCT measurement using measurement light on one of the left test eye and the right test eye, the control unit controls the OCT optical system to adjust the optical path length of the reference optical path based on the axial length and refractive power of the other of the left test eye and the right test eye.

[0308] According to this aspect, before performing OCT measurement on one of the test eyes, it is possible to set a measurement environment estimated from the measurement environment of the other test eye, thereby shortening the time required for OCT measurement.

[0309] In a third aspect of the embodiment, in the first or second aspect, the optical axis switching member deflects the optical path of the measurement light. The ophthalmologic apparatus according to this aspect further includes a first fixation optical system (fixation projection system 4L) that projects a first fixation light beam onto the left eye to be examined, a first optical path combining member (dichroic mirror ML) that optically combines the optical path of the measurement light deflected by the optical axis switching member with 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 onto the right eye to be examined, and a second optical path combining member (dichroic mirror MR) that optically combines the optical path of the measurement light deflected by the optical axis switching member with the optical path of the second fixation light beam.

[0310] According to this aspect, it is possible to perform OCT measurement with both eyes open while presenting fixation targets independently to the left eye and the right eye with a simple configuration.

[0311] In a fourth aspect of the embodiment, in the first or second aspect, the optical axis switching member deflects the optical path of the measurement light. The ophthalmologic apparatus according to this aspect further includes a fixation optical system (4) that projects a fixation light beam onto either the left or right eye to be examined, an optical path combining member (dichroic mirror 83) that optically combines the optical path of the fixation light beam with the optical path of the measurement light and guides the fixation light beam to the objective lens, a first reflecting member (reflecting mirror ML1) that deflects the optical path of the measurement light deflected by the optical axis switching member toward the left eye to be examined, and a second reflecting member (reflecting mirror MR1) that deflects the optical path of the measurement light deflected by the optical axis switching member toward the right eye to be examined.

[0312] According to this embodiment, it becomes possible to perform OCT measurement with both eyes open while presenting the same fixation target to both eyes using a fixation projection system common to both eyes.

[0313] In a fifth aspect of the embodiment, in the first or second aspect, the optical axis switching member deflects the optical path of the measurement light. The ophthalmologic apparatus according to this aspect further includes a first optical path combining member (dichroic mirror ML) that deflects the optical path of the measurement light deflected by the optical axis switching member toward the left eye to be examined and transmits and guides a first fixation light beam from the transmission direction to the left eye to be examined, and a second optical path combining member (dichroic mirror MR) that deflects the optical path of the measurement light deflected by the optical axis switching member toward the right eye to be examined and transmits and guides a second fixation light beam from the transmission direction to the right eye to be examined.

[0314] According to this embodiment, a fixation projection system common to both eyes is arranged outside the device, and OCT measurement can be performed with both eyes open while presenting the same fixation target to both eyes.

[0315] A sixth aspect of the embodiment is the third or fifth aspect, and includes a first adjustment unit (a convergence angle adjustment unit, a moving mechanism that rotates the dichroic mirrors ML and MR) that changes the orientation of the first measurement optical axis and the orientation of the second measurement optical axis by changing 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.

[0316] According to this aspect, it becomes possible to perform OCT measurement with both eyes open while adjusting the convergence angle with a simple configuration.

[0317] A seventh aspect of the embodiment is the third, fifth, or sixth aspect, and includes a second adjustment unit (a height adjustment unit, a moving mechanism that rotates the deflection surface of the optical axis switching member SW, the deflection surface (optical path coupling surface) of the dichroic mirror ML, and the deflection surface of the dichroic mirror MR) that adjusts the arrangement direction of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the optical axis switching member, the orientation of the 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.

[0318] According to this aspect, when 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 test eye and the right test eye, the arrangement direction of the first measurement optical axis and the second measurement optical axis can be aligned with the arrangement direction of the left test eye and the right test eye with a simple configuration.

[0319] An eighth aspect of the embodiment is the fourth aspect, which includes a first adjustment unit (convergence angle adjustment unit, moving mechanism for rotating reflecting mirrors ML1 and MR1) that changes the orientation of the first measurement optical axis and the orientation of the second measurement optical axis by changing the orientation of the reflecting surface of the first reflecting member and the orientation of the reflecting surface of the second reflecting member.

[0320] According to this aspect, it becomes possible to perform OCT measurement with both eyes open while adjusting the convergence angle with a simple configuration.

[0321] A ninth aspect of the embodiment is the fourth or eighth aspect, which includes a second adjustment unit (a height adjustment unit, a moving mechanism that rotates the deflection surface of the optical axis switching member SW, the deflection surface of the reflecting mirror ML1, and the deflection surface of the reflecting mirror MR1) that adjusts the arrangement direction of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the optical axis switching member, the orientation of the reflecting surface of the first reflecting member, and the orientation of the reflecting surface of the second reflecting member.

[0322] According to this aspect, when 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 test eye and the right test eye, the arrangement direction of the first measurement optical axis and the second measurement optical axis can be aligned with the arrangement direction of the left test eye and the right test eye with a simple configuration.

[0323] A tenth aspect of the embodiment is any of the third to ninth aspects, and further includes a third adjustment unit (pupillary distance adjustment unit, movement mechanism 310) that changes the distance between the first measurement optical axis and the second measurement optical axis by moving the optical axis switching member along the first measurement optical axis or the second measurement optical axis.

[0324] According to this aspect, the first measurement optical axis and the second measurement optical axis can be aligned with the interpupillary distance of the subject with a simple configuration.

[0325] An eleventh aspect of the embodiment is any of the first to tenth aspects, and includes two or more imaging units (anterior segment cameras 15LA, 15LB, 15RA, 15RB) that capture images of the anterior segments of the left and right subjects from different directions, and a moving mechanism (200) that three-dimensionally moves at least the OCT optical system. The control unit changes the relative positions of the OCT optical systems with respect to the left and right subjects based on two or more images obtained by the two or more imaging units, and also changes the orientations of the first and second measurement optical axes and the distances between the first and second measurement optical axes so that the first measurement optical axis coincides with the visual axis of the left eye and the second measurement optical axis coincides with the visual axis of the right eye.

[0326] According to this aspect, it is possible to align an ophthalmic apparatus that is capable of performing OCT measurement for both eyes with both eyes open, with a simple configuration and a wide dynamic range.

[0327] In a twelfth aspect of the embodiment, in the eleventh aspect, the two or more photographing units include a first photographing unit (anterior eye camera 15LA) that photographs the anterior eye of the left subject eye, a second photographing unit (anterior eye camera 15LR) that photographs the anterior eye of the left subject eye and the anterior eye of the right subject eye, and a third photographing unit (anterior eye camera 15RA) that photographs the anterior eye of the right subject eye.

[0328] According to this embodiment, the number of anterior eye cameras can be reduced, and OCT measurement can be performed on both eyes with both eyes open at lower cost.

[0329] A thirteenth aspect of the embodiment is any of the first to twelfth aspects, and includes a refractive power measurement optical system (a refractive power measurement projection system 6 and a refractive power measurement light receiving system 7) and an eye refractive power calculation unit (221). The refractive power measurement optical system projects a first measurement pattern light beam onto the left eye to be examined along a first measurement optical axis via an objective lens, and projects a second measurement pattern light beam onto the right eye to be examined along a second measurement optical axis, and receives return light of the first measurement pattern light beam from the left eye to be examined and return light of the second measurement pattern light beam from the right eye to be examined. The eye refractive power calculation unit calculates the refractive power of the left eye to be examined based on the light receiving result of the return light of the first measurement pattern light beam, and calculates the refractive power of the right eye to be examined based on the light receiving result of the return light of the second measurement pattern light beam.

[0330] According to this aspect, it becomes possible to measure the refractive power of both eyes with both eyes open.

[0331] In a fourteenth aspect of the embodiment, in the thirteenth aspect, the refractive power measurement optical system projects the first measurement pattern light beam and the second measurement pattern light beam so that the focal position is a position corresponding to an intermediate power between the refractive power of the left eye to be examined and the refractive power of the right eye to be examined.

[0332] According to this aspect, even when the refractive powers of both eyes are different, refractive power measurement can be performed on both eyes.

[0333] <Other> The embodiment described above is merely one example for carrying out the present invention, and those who wish to carry out the present invention may make any modifications, omissions, additions, etc. within the scope of the gist of the present invention.

[0334] In the above embodiment, the ophthalmic apparatus performs OCT on the fundus, but the configuration of the ophthalmic apparatus according to the embodiment is not limited to this. For example, the present invention can be applied to an ophthalmic apparatus that performs OCT on the fundus and the anterior segment.

[0335] In the above embodiment, the optical axis switching member SW bends the optical axis within the XZ plane, but the configuration according to the embodiment is not limited to this. For example, the optical axis switching member SW may be configured to bend the optical axis in the Y direction (upward or downward relative to the subject). In this case, the interpupillary distance adjustment unit can adjust the interpupillary distance by moving or rotating the dichroic mirrors ML and MR. [Explanation of symbols]

[0336] 1, 1a, 1b Ophthalmic equipment 2 XY alignment system 3 Kerato measurement system 4, 4L, 4R fixation projection system 5 Anterior segment observation system 6 Reflector measurement projection system 7 Reflector measurement light receiving system 8 OCT optical system 9, 9a, 9b Processing section 40, 40L, 40R fixation units 41, 41L, 41R LCD panels 42, 43, 44, 42L, 43L, 44L, 42R, 43R, 44R relay lenses 51 Objective Lens 210, 210a, 210b control unit 211, 211a, 211b Main control unit 300, 300a measurement optical system 400 Visual target presentation unit CLr, CRr cornea EL Left eye ELf, ERf fundus ER right eye ML, MR dichroic mirror ML1, MR1 reflecting mirror OL, OR measurement optical axis SW Optical axis switching member

Claims

1. a measurement optical system including an objective lens; and an OCT optical system that splits light from a light source into measurement light and reference light, projects the measurement light via the objective lens onto a left eye to be examined that is positioned on a first measurement optical axis or a right eye to be examined that is positioned on a second measurement optical axis, and detects interference light between return light of the measurement light from the left eye to be examined or the right eye to be examined that has passed through the objective lens and the reference light that has passed through a reference optical path; an optical axis switching member that switches the optical axis of the measurement optical system so that the optical axis substantially coincides with either the first measurement optical axis or the second measurement optical axis; a control unit that controls the optical axis switching member; an intraocular parameter calculation unit that calculates intraocular parameters of the left eye to be examined based on a detection result of the interference light obtained in a state where the optical axis of the measurement optical system is switched to approximately coincide with the first measurement optical axis, and calculates intraocular parameters of the right eye to be examined based on the detection result of the interference light obtained in a state where the optical axis of the measurement optical system is switched to approximately coincide with the second measurement optical axis; 1. An ophthalmic device comprising:

2. Before performing OCT measurement using the measurement light on one of the left eye and the right eye, the control unit controls the OCT optical system to adjust the optical path length of the reference optical path based on the axial length and refractive power of the other of the left eye and the right eye.

2. An ophthalmic apparatus according to claim 1.

3. the optical axis switching member deflects the optical path of the measurement light, a first fixation optical system that projects a first fixation light beam onto the left eye to be examined; a first optical path coupling member that optically couples the optical path of the measurement light deflected by the optical axis switching member to the optical path of the first fixation light beam; a second fixation optical system that projects a second fixation light beam onto the right eye to be examined; a second optical path coupling member that optically couples the optical path of the measurement light deflected by the optical axis switching member to the optical path of the second fixation light beam; Contains 3. An ophthalmic apparatus according to claim 1 or 2.

4. the optical axis switching member deflects the optical path of the measurement light, a fixation optical system that projects a fixation light beam onto either the left eye or the right eye; an optical path coupling member that optically couples an optical path of the fixation light beam to an optical path of the measurement light and guides the fixation light beam to the objective lens; a first reflecting member that deflects the optical path of the measurement light deflected by the optical axis switching member toward the left eye to be examined; a second reflecting member that deflects the optical path of the measurement light deflected by the optical axis switching member toward the right eye to be examined; Contains 3. An ophthalmic apparatus according to claim 1 or 2.

5. the optical axis switching member deflects the optical path of the measurement light, a first optical path coupling member that deflects the optical path of the measurement light deflected by the optical axis switching member toward the left eye to be examined and transmits a first fixation light beam from a transmission direction and guides it to the left eye to be examined; a second optical path coupling member that deflects the optical path of the measurement light deflected by the optical axis switching member toward the right eye to be examined and transmits a second fixation light beam from a transmission direction and guides it to the right eye to be examined; Contains 3. An ophthalmic apparatus according to claim 1 or 2.

6. a first adjustment unit that changes the orientation of the first measurement optical axis and the orientation of the second measurement optical axis by changing 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; 6. An ophthalmic apparatus according to claim 3 or claim 5.

7. a second adjustment unit that adjusts the arrangement directions of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the optical axis switching member, the 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.

7. An ophthalmic apparatus according to claim 3, claim 5, or claim 6.

8. a first adjustment unit that changes the orientation of the first measurement optical axis and the orientation of the second measurement optical axis by changing the orientation of the reflecting surface of the first reflecting member and the orientation of the reflecting surface of the second reflecting member; 5. An ophthalmic apparatus according to claim 4.

9. a second adjustment unit that adjusts the arrangement directions of the first measurement optical axis and the second measurement optical axis by changing the deflection direction of the optical axis switching member, the orientation of the reflecting surface of the first reflecting member, and the orientation of the reflecting surface of the second reflecting member.

9. An ophthalmic apparatus according to claim 4 or claim 8.

10. a third adjustment unit that changes the distance between the first measurement optical axis and the second measurement optical axis by moving the optical axis switching member along the first measurement optical axis or the second measurement optical axis; The ophthalmic apparatus according to any one of claims 3 to 9.

11. two or more photographing units for photographing the anterior segment of the left eye to be examined and the anterior segment of the right eye to be examined from different directions; a moving mechanism for moving at least the OCT optical system three-dimensionally; Including, The control unit changes the relative position of the OCT optical system with respect to the left eye and the right eye, based on two or more images obtained by the two or more imaging units, and also changes the orientations 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 and the second measurement optical axis coincides with the visual axis of the right eye. The ophthalmic apparatus according to any one of claims 1 to 10.

12. The two or more imaging units are a first imaging unit that images an anterior segment of the left eye to be examined; a second photographing unit that photographs an anterior segment of the left eye to be examined and an anterior segment of the right eye to be examined; a third imaging unit that images an anterior segment of the right eye to be examined; Contains The ophthalmic apparatus according to claim 11 .

13. a refractive power measurement optical system that projects a first measurement pattern light beam onto the left eye to be examined along the first measurement optical axis via the objective lens, projects a second measurement pattern light beam onto the right eye to be examined along the second measurement optical axis, and receives return light of the first measurement pattern light beam from the left eye to be examined and return light of the second measurement pattern light beam from the right eye to be examined; an eye refractive power calculation unit that 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 beam, 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 beam; include The ophthalmic apparatus according to any one of claims 1 to 12.

14. The refractive power measurement optical system projects the first measurement pattern light beam and the second measurement pattern light beam so that a position corresponding to an intermediate power between the refractive power of the left eye to be examined and the refractive power of the right eye to be examined becomes a focal position.

14. An ophthalmic apparatus according to claim 13.

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