ophthalmic devices

Abstract

To provide a new technology to measure at least characteristics of both eyes with a high degree of precision while saving costs and space.SOLUTION: An ophthalmologic apparatus includes an objective lens, an OCT optical system, an optical axis adjustment part, a control part, and an intraocular parameter calculation part. A first measurement optical axis and a second measurement optical axis arranged separately from each other pass through the objective lens. The OCT optical system executes OCT for a left eye to be examined arranged on the first measurement optical axis or for a right eye to be examined arranged on the second measurement optical axis using measurement light. The optical axis adjustment part adjusts an optical axis of the OCT optical system. The control part controls the optical axis adjustment part so that the optical axis roughly matches either the first measurement optical axis or the second measurement optical axis. The intraocular parameter calculation part calculates the intraocular parameter of the left eye to be examined or the right eye to be examined on the basis of a result of the detection of interference light obtained in a state where the optical axis of the OCT optical system is adjusted so as to roughly match either the first measurement optical axis or the second measurement optical axis.SELECTED DRAWING: Figure 1

Description

Technical Field

[0001] This invention relates to an ophthalmic apparatus.

Background Art

[0002] An ophthalmic apparatus capable of performing a plurality of examinations and measurements on an eye to be examined is known. Examinations and measurements on an eye to be examined include subjective examinations and objective measurements. A subjective examination obtains results based on responses from the subject. An objective measurement obtains information regarding the eye to be examined mainly using physical methods without referring to responses from the subject.

[0003] For example, Patent Document 1 discloses an ophthalmic apparatus capable of subjective examinations and objective measurements. As objective measurements, this ophthalmic apparatus can perform refractive power measurement, corneal shape measurement, and imaging and measurement using optical coherence tomography. This ophthalmic apparatus includes an optical system common to the left and right eyes, and it is possible to perform subjective examinations and objective measurements on one of the left and right eyes using this optical system.

[0004] Also, for example, Patent Document 2 discloses an ophthalmic apparatus capable of presenting fixation targets independently for each of the left and right eyes and performing refractive power measurement on one of the left and right eyes using one optical system.

[0005] On the other hand, for example, Patent Document 3 discloses an ophthalmic apparatus including two optical systems provided independently for the left and right eyes, and capable of simultaneously performing refractive power measurement and corneal shape measurement on the left and right eyes using the two optical systems.

[0006] Also, for example, Patent Document 4 discloses an ophthalmic apparatus capable of simultaneously acquiring Hartmann images of the left and right eyes and simultaneously measuring wavefront aberrations of the left and right eyes.

Prior Art Documents

Patent Documents

[0007]

Patent Document 1

[0008] However, the configurations disclosed in Patent Documents 1 and 2 measure one eye at a time, making it impossible to measure the characteristics of both eyes with both eyes open. In contrast, the configuration disclosed in Patent Document 3 allows simultaneous measurement of both eyes with both eyes open, but this leads to a larger device and higher costs. Furthermore, the configuration disclosed in Patent Document 4 may lead to a larger device when performing measurements other than wavefront aberration measurement, or it may lead to a decrease in measurement accuracy because measurements other than wavefront aberration cannot be performed under optimal conditions.

[0009] This invention was made in view of these circumstances, and one of its objectives is to provide a new technology that can measure the characteristics of both eyes with high precision at low cost and in a space-saving manner. [Means for solving the problem]

[0010] One embodiment of the OCT apparatus includes: an objective lens through which a first measuring optical axis and a second measuring optical axis, which are spaced apart from each other, pass; an OCT optical system that splits light from a light source into measuring light and reference light, projects the measuring light onto a left eye under examination located on the first measuring optical axis or a right eye under examination located on the second measuring optical axis via the objective lens, and detects interference light between the return light of the measuring light from the left eye under examination or the right eye under examination and the reference light that has passed through the reference optical path; an optical axis adjustment unit for adjusting the optical axis of the OCT optical system; a control unit for controlling the optical axis adjustment unit so that it substantially coincides with either the first measuring optical axis or the second measuring optical axis; and an intraocular parameter calculation unit that calculates intraocular parameters of the left eye under examination based on the detection result of the interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the first measuring optical axis, and calculates intraocular parameters of the right eye under examination based on the detection result of the interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the second measuring optical axis. [Effects of the Invention]

[0011] According to the present invention, a new technology is available that enables high-precision measurement of binocular characteristics at low cost and in a space-saving manner. [Brief explanation of the drawing]

[0012] [Figure 1] This is a schematic diagram showing an example of the configuration of the optical system of an ophthalmic device according to the first embodiment. [Figure 2] This is a schematic diagram showing an example of the configuration of the optical system of an ophthalmic device according to the first embodiment. [Figure 3] This is a schematic diagram illustrating the optical system of an ophthalmic device according to the first embodiment. [Figure 4] This is a schematic diagram illustrating the optical system of an ophthalmic device according to the first embodiment. [Figure 5] This is a schematic diagram illustrating the optical system of an ophthalmic device according to the first embodiment. [Figure 6] This is a schematic diagram showing an example of the configuration of the optical system of an ophthalmic device according to the first embodiment. [Figure 7]It is a schematic diagram showing a configuration example of an optical system of an ophthalmic device according to the first embodiment. [Figure 8] It is a schematic diagram showing a configuration example of an optical system of an ophthalmic device according to the first embodiment. [Figure 9] It is a schematic diagram for explaining an optical system of an ophthalmic device according to the first embodiment. [Figure 10] It is a schematic diagram for explaining an optical system of an ophthalmic device according to the first embodiment. [Figure 11A] It is a schematic diagram for explaining an optical system of an ophthalmic device according to the first embodiment. [Figure 11B] It is a schematic diagram for explaining an optical system of an ophthalmic device according to the first embodiment. [Figure 11C] It is a schematic diagram for explaining an optical system of an ophthalmic device according to the first embodiment. [Figure 12] It is a schematic diagram showing a configuration example of a processing system of an ophthalmic device according to the first embodiment. [Figure 13] It is a schematic diagram showing a configuration example of a processing system of an ophthalmic device according to the first embodiment. [Figure 14] It is a schematic diagram showing a flow of an operation example of an ophthalmic device according to the first embodiment. [Figure 15] It is a schematic diagram showing a flow of an operation example of an ophthalmic device according to the first embodiment. [Figure 16] It is a schematic diagram showing a configuration example of an optical system of an ophthalmic device according to the second embodiment. [Figure 17] It is a schematic diagram showing a configuration example of an optical system of an ophthalmic device according to the second embodiment. [Figure 18] It is a schematic diagram for explaining an optical system of an ophthalmic device according to the second embodiment. [Figure 19] It is a schematic diagram for explaining an optical system of an ophthalmic device according to the second embodiment. [Figure 20] It is a schematic diagram showing a configuration example of an optical system of an ophthalmic device according to the second embodiment. [Figure 21] It is a schematic diagram showing a configuration example of a processing system of an ophthalmic device according to the second embodiment. [Figure 22]This is a schematic diagram showing an example of the optical system configuration of an ophthalmic device according to the third embodiment. [Figure 23] This is a schematic diagram showing an example of the configuration of the processing system of an ophthalmic device according to the third embodiment. [Modes for carrying out the invention]

[0013] Examples of embodiments of the ophthalmic apparatus according to this invention will be described in detail with reference to the drawings. It is possible to apply the contents of the referenced documents and any prior art cited in this specification to the following embodiments.

[0014] The ophthalmic apparatus according to this embodiment can perform 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 types. In particular, the ophthalmic apparatus according to this embodiment can perform OCT measurements on both eyes and calculate intraocular parameters for each eye. By sharing an objective lens for OCT measurements on both eyes, the apparatus can be made smaller and less expensive.

[0015] In some embodiments, the ophthalmic device further includes at least one objective measurement optical system for performing objective measurements different from OCT measurements, and a subjective examination optical system for performing subjective examinations. In such an ophthalmic device, the device can be miniaturized and cost-effective by sharing the objective lens among multiple optical systems corresponding to different types of examinations and measurements.

[0016] Objective measurement is a measurement method that obtains information about the eye under examination using primarily physical methods, without referring to the subject's response. Objective measurement includes measurements to obtain the characteristics of the eye under examination and imaging to obtain an image of the eye under examination. Other objective measurements include intraocular pressure measurement and fundus photography. In some embodiments, the ophthalmic device can perform refractive power measurement (refractive measurement) and OCT measurement as objective measurements. In some embodiments, the ophthalmic device can perform refractive power measurement, corneal topography measurement, and OCT measurement as objective measurements.

[0017] The following describes the case in which the ophthalmic device according to the embodiment performs OCT measurements on the anterior segment of the eye and the fundus. In the following embodiment, the case in which the spectral domain type OCT method is used will be described in particular detail. However, it is also possible to apply the configuration according to the embodiment to ophthalmic devices that use other types (e.g., swept-source type, time-domain type) OCT.

[0018] Subjective examinations are measurement techniques that obtain information by utilizing the responses of the subject. Examples of subjective examinations include subjective refraction measurements such as distance vision tests, near vision tests, contrast tests, and glare tests, as well as visual field tests.

[0019] Hereinafter, the fundus conjugate position refers to the position that is approximately optically conjugate to the fundus of the eye under examination when alignment is complete, and means the position that is optically conjugate to the fundus of the eye under examination or its vicinity. Similarly, the pupil conjugate position refers to the position that is approximately optically conjugate to the pupil of the eye under examination when alignment is complete, and means the position that is optically conjugate to the pupil of the eye under examination or its vicinity.

[0020] Furthermore, in the following embodiment, 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> Figures 1 and 2 show examples of the optical system configuration of the ophthalmic device according to the first embodiment. Figure 1 schematically represents the optical system configuration of the ophthalmic device according to the first embodiment as viewed from above. Figure 2 shows a block diagram of the example configuration of the measuring optical system 300 in Figure 1.

[0022] The ophthalmic apparatus 1 according to the first embodiment includes a measuring optical system 300, dichroic mirrors ML and MR, prism mirror PR, fixation projection system 4L, and fixation projection system 4R. The measuring optical system 300 may also include dichroic mirrors ML and MR, prism mirror PR, fixation projection system 4L, and fixation projection system 4R.

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

[0024] As shown in Figure 2, the measurement optical system 300 includes, in addition to the objective lens described above, a keratometer measurement system 3, an anterior segment observation system 5, refractometer measurement projection systems 6L and 6R, a refractometer 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 corneal CLr of the left eye (EL) and information representing the shape of the corneal 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 using the objective lens mentioned above, and to receive the reflected light of the corneal shape measurement light.

[0026] The anterior segment observation system 5 is configured to illuminate the anterior segment of the left eye EL and the anterior segment of the right eye ER, and to receive the reflected light of the illumination light through the objective lens.

[0027] The refractometer projection system 6L projects refractometer light onto the left eye EL via the objective lens, projecting a measurement pattern (ring pattern) centered on the measurement optical axis OL onto the fundus ELf. The refractometer projection system 6R projects refractometer light onto the right eye ER via the objective lens, projecting a measurement pattern (ring pattern) centered on the measurement optical axis OR onto the fundus ERf.

[0028] The refractometer light receiving system 7 is configured to receive reflected light from the fundus ELf and reflected light from the fundus ERf via the 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 through the objective lens onto the left eye EL positioned on the measurement optical axis OL or the right eye ER positioned on the measurement optical axis OR, and detects the interference light between the reflected light from the left eye EL or right 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 (or infrared) region. Here, the fixation beam projected by the fixation projection systems 4L and 4R has wavelength components in the visible region, and the light projected by the measurement optical system 300 has wavelength components in the near-infrared (or infrared) region.

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

[0032] (Prism Mirror PR) The prism mirror PR is positioned between the measuring optical system 300 and the dichroic mirrors ML and MR. The prism mirror PR includes deflection surfaces M1 and M2. The prism mirror PR deflects the optical axis from the dichroic mirror ML toward the measuring optical system 300 at deflection surface M1, and deflects the optical axis from the dichroic mirror MR toward the measuring optical system 300 at deflection surface M2.

[0033] (Fixation projection system 4L, 4R) The fixation projection system 4L presents a fixation target to the left eye EL by projecting a fixation beam onto the fundus ELf of the left eye EL under examination. 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 receives control from the control unit described later and displays a pattern representing the fixation target. The fixation position of the left eye EL under examination can be changed by changing the display position of the pattern on the screen of the liquid crystal panel 41L. The fixation unit 40L is also movable in the optical axis direction under control from the control unit described later.

[0034] Light from the liquid crystal panel 41L passes through relay lenses 42L, 43L, and 44L, through the dichroic mirror ML, and is projected onto the fundus ELf. In some embodiments, the fixation unit 40L is movable in the optical axis direction independently of the relay lenses 43L and 44L.

[0035] Similarly, the fixation projection system 4R presents a fixation target to the right eye ER by projecting a fixation beam onto the fundus ERf of 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 receives control from the control unit described later and displays a pattern representing the fixation target. 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. The fixation unit 40R is also movable in the optical axis direction under control from the control unit described later.

[0036] Light from the liquid crystal panel 41R passes through relay lenses 42R, 43R, and 44R, through the dichroic mirror MR, and is projected onto the fundus ERf. In some embodiments, the fixation unit 40R is movable in the optical axis direction independently of the relay lenses 43R and 44R.

[0037] The fixation unit 40L can move independently of the fixation unit 40R in the optical axis direction. That is, the fixation units 40L and 40R can move independently in the optical axis direction according to the refractive power of the left eye EL and the right eye ER, respectively.

[0038] The fixation positions for the left eye (EL) and the right eye (ER) include positions for acquiring images centered on the macula of the fundus, positions for acquiring images centered on the optic nerve head, and positions for acquiring images centered on the fundus center between the macula and the optic nerve head. The display position of the pattern representing the fixation target can be arbitrarily changed.

[0039] The ophthalmic device 1 can perform keratometry, refractometry, and OCT measurement on the left eye EL using the measurement optical system 300 while a fixation target is presented to the left eye EL by the fixation projection system 4L. Furthermore, the ophthalmic device 1 can perform keratometry, refractometry, and OCT measurement on the right eye ER using the measurement optical system 300 while a fixation target is presented to the right eye ER by the fixation projection system 4R. In some embodiments, the ophthalmic device 1 simultaneously performs at least one of keratometry and refractometry on the left eye EL and the right eye ER using the measurement optical system 300 while fixation targets are presented to the left eye EL and the right eye ER respectively by the fixation projection systems 4L and 4R. In some embodiments, the ophthalmic device 1, with fixation targets presented to the left eye EL and right eye ER respectively by fixation projection systems 4L and 4R, sequentially performs at least one of keratometry, refractometry, and OCT measurement on each of the left eye EL and right eye ER using the measurement optical system 300.

[0040] Such an ophthalmic device 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. The optical axis adjustment unit receives control from the control unit described later and can adjust the optical axis of the OCT optical system 8 by controlling the optical elements in the path of the measurement light to deflect the measurement light or move 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 substantially coincides with either the measurement optical axis OL or OR.

[0041] Furthermore, the ophthalmic device 1 includes an interpupillary distance adjustment unit that changes the distance in the X direction between the measurement optical axes OL and OR to match the interpupillary distance of the subject.

[0042] Figure 3 shows an explanatory diagram of an example of the operation of the interpupillary distance adjustment unit in the ophthalmic device 1 according to the first embodiment. In Figure 3, the same reference numerals are used for parts that are the same as in Figure 1, and explanations are omitted as appropriate.

[0043] The interpupillary distance adjustment unit changes the distance in the X direction between the measurement optical axes OL and OR by moving the prism mirror PR, which has deflection surfaces M1 and M2, along the measurement optical axis OL or measurement optical axis OR (Z direction, optical axis of the measurement optical system 300). For example, when the prism mirror PR 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 a constant distance in the X direction between the left and right measurement optical axes passing through the objective lens of the measurement optical system 300, the prism mirror PR is moved from its initial position along the measurement optical axis OL or measurement optical axis OR. As a result, as shown in Figure 3, the position of the optical axis deflected by the dichroic mirrors ML and MR changes, and the measurement optical axis OL becomes the measurement optical axis OL', and the measurement optical axis OR becomes the measurement optical axis OR'. Consequently, 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.

[0044] In some embodiments, the interpupillary distance is changed by moving the prism mirror PR in the X direction as shown in Figure 3.

[0045] In some embodiments, the optical axis adjustment unit moves the prism mirror PR along the measurement optical axis OL or measurement optical axis OR so that the optical axis of the OCT optical system 8 substantially coincides with either the measurement optical axis OL or OR.

[0046] In some embodiments, the prism mirror PR is moved by a moving 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 moving mechanism (and control unit) (not shown). In some embodiments, the prism mirror PR is moved manually by a moving mechanism (not shown). In this case, the function of the interpupillary distance adjustment unit is realized by the moving mechanism (not shown).

[0047] Furthermore, the ophthalmic device 1 includes a convergence angle adjustment unit that changes the direction of at least one of the measuring optical axis OL that enters the left eye EL through the pupil, and the direction of the measuring optical axis OR that enters the right eye ER through the pupil, in accordance with the convergence angle of the eye being examined.

[0048] Figure 4 shows an explanatory diagram of an example of the operation of the convergence angle adjustment unit in the ophthalmic device 1 according to the first embodiment. In Figure 4, the same reference numerals are used for parts that are the same as in Figure 1, and explanations are omitted as appropriate.

[0049] 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 coupling surface of the optical path coupling member that couples the optical path (optical axis) of the measurement optical system 300 and the optical path (optical axis) of the fixation projection system 4L. The orientation of the dichroic mirror MR corresponds to the orientation of the optical path coupling surface of the optical path coupling member that couples the optical path of the measurement optical system 300 and the optical path of the fixation projection system 4R.

[0050] For example, the optical path coupling surface (deflection surface) of the dichroic mirror ML is configured to be rotatable around a pivot axis extending in the Y-axis direction. For example, the optical path coupling surface (deflection surface) of the dichroic mirror MR is configured to be rotatable around a pivot axis extending in the Y-axis direction.

[0051] For example, when the deflection plane of the dichroic mirror ML is oriented in the first direction and the deflection plane of the dichroic mirror MR is oriented in the second direction, the directions of the measurement optical axes OL and OR are approximately parallel to the optical axis direction of the measurement optical system 300. Now, the directions of the deflection planes of the dichroic mirrors ML and MR are changed inward. As a result, as shown in Figure 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', and the convergence angle is changed.

[0052] In some embodiments, the dichroic mirrors ML and MR are rotated by a moving mechanism (rotating mechanism) (not shown) under control from a control unit described later. 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).

[0053] In some embodiments, the prism mirror PR may include a reflective mirror having a deflection surface M1 and a reflective mirror having a deflection surface M2.

[0054] Figure 5 shows another configuration example of the ophthalmic device 1 according to the first embodiment. In Figure 5, the same reference numerals are used for parts that are the same as in Figure 1, and their descriptions are omitted as appropriate.

[0055] As shown in Figure 5, the prism mirror PR includes a reflective mirror RML having a deflection surface M1 and a reflective mirror RMR having a deflection surface M2. Similar to Figure 1, the optical axis of the measurement optical system 300 is deflected toward the dichroic mirror ML by the deflection surface M1 and toward the dichroic mirror MR by the deflection surface M2.

[0056] The reflective mirrors RML and RMR may be independently movable. For example, each of the reflective mirrors RML and RMR can be moved independently along the measurement optical axis. As a result, the measurement optical axes OL and OR are deflected by the dichroic mirrors ML and MR while the reflective mirrors RML and RMR are moved to different positions in the Z direction relative to each other. Consequently, compared to moving the prism mirror PR as shown in Figure 3, it becomes possible to adjust the interpupillary distance with high precision by changing the intermediate position of the measurement optical axes OL and OR.

[0057] For example, the orientations of the reflective mirrors RML and RMR can be changed independently. As a result, the measurement optical axes OL and OR are deflected by the dichroic mirrors ML and MR while the reflective mirrors RML and RMR are deflected at different angles relative to the Z direction. Therefore, as shown in Figure 4, it becomes possible to adjust the convergence angle without changing the orientations of the dichroic mirrors ML and MR.

[0058] In some embodiments, the reflective mirrors RML and RMR are controlled by a control unit (described later) and rotated by a moving mechanism (rotating mechanism) (not shown).

[0059] In some embodiments, the ophthalmic device 1 includes a height adjustment unit that changes the orientation (deflection direction) of the deflection surface M1 of the prism mirror PR or reflective mirror RML, the orientation of the deflection surface M2 of the prism mirror PR or reflective mirror RMR, the orientation of the deflection surface (optical path coupling surface) of the dichroic mirror ML, and the orientation of the deflection surface of the dichroic mirror MR. This adjusts the alignment direction of the measurement optical axes OL and OR. For example, when the alignment direction of the left eye EL and the right eye ER is not horizontal (X direction), the height adjustment unit can be used to make the alignment direction of the measurement optical axes OL and OR match the alignment direction of the left eye EL and the right eye ER. A movement mechanism that rotates the deflection surface M1 of the prism mirror PR or reflective mirror RML, the deflection surface M2 of the prism mirror PR or reflective mirror RMR, the deflection surface (optical path coupling surface) of the dichroic mirror ML, and the deflection surface of the dichroic mirror MR is an example of a height adjustment unit.

[0060] Furthermore, the ophthalmic device 1 includes a calculation processing unit that calculates intraocular parameters of the eye under examination based on the detection results of interference light obtained by the OCT optical system 8. Specifically, the calculation processing unit calculates the intraocular parameters of the left eye under examination EL based on the detection results of interference light obtained when the optical axis of the OCT optical system 8 is adjusted to approximately coincide with the measurement optical axis OL, and calculates the intraocular parameters of the right eye under examination ER based on the detection results of interference light obtained when 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 the "first fixation optical system" according to the embodiment. The fixation projection system 4R is an example of the "second fixation optical system" according to the embodiment. The dichroic mirror ML is an example of the "first optical path coupling member" according to the embodiment. The dichroic mirror MR is an example of the "second optical path coupling member" according to the embodiment. The prism mirror PR or reflective mirror RML is an example of the "first deflection member" according to the embodiment. The prism mirror PR or reflective mirror RMR is an example of the "second deflection member" according to the embodiment. The movement mechanism that rotates the dichroic mirrors ML and MR is an example of the convergence angle adjustment unit. The convergence angle adjustment unit is an example of the "first adjustment unit" according to the embodiment. The movement mechanism that rotates the deflection surface M1 of the prism mirror PR or reflective mirror RML, the deflection surface M2 of the prism mirror PR or reflective mirror RMR, the deflection surface (optical path coupling surface) of the dichroic mirror ML, and the deflection surface of the dichroic mirror MR is an example of the height adjustment unit. The height adjustment section is an example of the "second adjustment section" according to the embodiment. The interpupillary distance adjustment section is an example of the "third adjustment section" according to the embodiment. The deflection surface M1 is an example of the "first deflection surface as a first deflection member" according to the embodiment. The deflection surface M2 is an example of the "second deflection surface as a second deflection member" according to the embodiment.

[0062] The following describes an example configuration of the measurement optical system 300. Hereafter, the left eye EL and the right eye ER will sometimes be simply referred to as the "eyes under examination."

[0063] Figures 6 to 8 show examples of the configuration of the measurement optical system 300 according to the first embodiment. Figure 6 schematically shows an example of the configuration of the measurement optical system 300 viewed from the side (X direction). Figure 7 schematically shows an example of the configuration of the reflector measurement projection systems 6L and 6R in Figure 6. Figure 8 schematically shows an example of the configuration of the OCT unit 100 in Figure 6. In Figure 6, for the sake of explanation, the anterior segment cameras 15LA and 15RA are shown to be arranged in the X direction, and the anterior segment cameras 15LB and 15RB are shown to be arranged in the X direction, but the configuration according to the embodiment is not limited to this. Also, for the sake of explanation, the dichroic mirrors ML and MR shown in Figure 1 are omitted from Figure 6. In Figures 6 and 8, the same reference numerals are used for parts that are the same as in Figure 1, and explanations are omitted as appropriate. In Figure 7, the same reference numerals are used for parts that are the same as in Figure 6, and explanations are omitted as appropriate.

[0064] The measuring optical system 300 includes an optical system for observing the left eye EL and the right eye ER, an optical system for examining the left eye EL and the right eye 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 the optical system for observing the left eye EL and the right eye ER. A keratometry system 3, a refractor measurement optical system (refractive power measurement optical system), and an OCT optical system 8 are provided as the optical system for examining the left eye EL and the right eye ER. As shown in Figure 2, the refractor measurement optical system includes refractor measurement projection systems 6L and 6R and a refractor measurement light receiving system 7.

[0065] In the first embodiment, the keratometry system 3, the refractometry light receiving system 7, and the OCT optical system 8 are shared for the examination of the left eye EL and the right eye ER, the refractometry projection system 6L is used for the examination of the left eye EL (refractive power measurement), and the refractometry projection system 6R is used for the examination of the right eye ER (refractive power measurement).

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

[0067] (Anterior segment observation system 5) The anterior segment observation system 5 captures video of the anterior segment of the left eye EL and the anterior segment of the right eye ER. In the optical system via the anterior segment observation system 5, the imaging surface of the image sensor 59 is positioned at the pupil conjugate position. The anterior segment illumination light source 50 illuminates the anterior segment of the left eye EL and the anterior segment of the right eye ER with illumination light (e.g., infrared light).

[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 eye EL and the anterior segment of the right eye ER from a position away from the measurement optical axis OL, 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 eye EL from a position away from the measurement optical axis OL, and a pair of illumination light sources for illuminating the anterior segment of the right eye ER from a position 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 eye EL and one of the pair of illumination light sources for illuminating the anterior segment of the right eye ER may be shared.

[0069] As described above, the objective lens 51 is positioned so that the measurement optical axes OL and OR pass through it (when alignment is complete). Light reflected from the anterior segment of the left eye EL and the anterior segment of the right eye ER passes through the objective lens 51, through the dichroic mirror 52, through the hole formed in the aperture (telecentral aperture) 53, through the half mirror 23, through the relay lenses 55 and 56, and through the dichroic mirror 76. The dichroic mirror 52 combines (separates) the optical path of the refractor measurement optical system and the optical path of the anterior segment observation system 5. The dichroic mirror 52 is positioned so that the optical path combining surface that combines these optical paths is inclined with respect to the optical axis of the objective lens 51. The light that has passed through the dichroic mirror 76 is imaged onto the imaging surface of the image sensor 59 (area sensor) by the imaging lens 58. The image sensor 59 performs imaging and signal output at a predetermined rate. The output (video signal) from the image sensor 59 is input to the processing unit 9, which will be described later. The processing unit 9 displays the anterior segment images of the left eye EL and the right eye ER based on this video signal on the display unit 270, which will be described later, for example, in a horizontal direction. The anterior segment images of the left eye EL and the right eye ER are, for example, infrared motion images.

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

[0071] The number of anterior segment cameras used to photograph the anterior segment of the left eye EL may be two or more, as long as the configuration allows for substantially simultaneous imaging of the anterior segment from two different directions. Alternatively, one of the anterior segment cameras may be the image sensor 59 in the anterior segment observation system 5.

[0072] "Substantially simultaneous" means that when taking images with two or more anterior segment cameras, a timing difference in the images taken is acceptable to the extent that eye movements can be ignored. This allows images to be acquired by two or more anterior segment cameras when the subject's eye is in the same position (orientation).

[0073] The anterior segment cameras 15RA and 15RB capture images of the anterior segment of the right eye ER. The anterior segment cameras 15RA and 15RB are, for example, video cameras that capture video at a predetermined frame rate. The anterior segment cameras 15RA and 15RB capture images of the anterior segment from different directions substantially simultaneously. For example, the anterior segment 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 used to image the anterior segment of the right eye ER may be two or more, as long as the configuration allows for substantially simultaneous imaging of the anterior segment from two different directions. Alternatively, one of the anterior segment cameras 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 segment cameras 15LA and 15LB.

[0076] (XY alignment system 2) The XY alignment system 2 illuminates the left eye EL and the right eye ER with light (infrared light) for alignment in directions perpendicular to the optical axis of the anterior segment observation system 5 (left-right direction (X direction), up-down direction (Y direction)). The XY alignment system 2 includes an XY alignment light source 21 and a collimator lens 22, which are located in 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 eye EL and the right eye ER through the anterior segment observation system 5. The reflected light from the cornea CLr of the left eye EL is guided to the image sensor 59 through the anterior segment observation system 5. The reflected light from the cornea CRr of the right eye ER is guided to the image sensor 59 through the anterior segment observation system 5.

[0077] Images based on reflected light from the corneal CLr (XY bright spot images) are included in the anterior segment image of the left eye EL. Images based on reflected light from the corneal CRr (XY bright spot images) are included in the anterior segment image of the right eye ER. For example, the processing unit 9 displays the anterior segment image including the XY bright spot images and the alignment marks on the display unit for both the left eye EL and the right eye ER. When performing XY alignment manually, the user moves the optical system to guide the XY bright spot images into the alignment marks. When performing alignment automatically, the processing unit 9 controls the mechanism that moves the optical system so that the displacement of the XY bright spot images relative to the alignment marks is canceled. In some embodiments, the processing unit 9 controls the mechanism that moves the optical system and the mechanism that moves the prism mirror PR, dichroic mirrors ML and MR shown in Figure 1 so that the displacement of the XY bright spot images relative to the alignment marks is canceled.

[0078] (Keratometry system 3) The keratometry system 3 projects a ring-shaped beam of light (infrared light) onto the corneal CLr of the left eye (EL) and the corneal CRr of the right eye (ER) (corneal shape information) to measure their respective shapes. The keratometry plate 31 is positioned between the objective lens 51 and the left eye (EL) and right eye (ER). A keratometry ring light source 32 is provided on the back side (objective lens 51 side) of the keratometry plate 31. The keratometry plate 31 has a keratometry pattern (transmitting portion) formed along the circumference centered on the respective measurement optical axes OL and OR, which transmits light from the keratometry ring light source 32. In some embodiments, the keratometry plate 31 has a keratometry pattern (transmitting portion) formed along the circumference centered on the optical axis which transmits light from the keratometry ring light source 32. The keratometry pattern may be formed in an arc shape (part of the circumference) centered on the optical axis. By illuminating the keratin plate 31 with light from the keratin light source 32, a ring-shaped light beam (arc-shaped or circumferential measurement pattern) is projected onto the corneal CLr and CRr. The reflected light from the corneal CLr and CRr (keratin image) is detected by the image sensor 59 along with the anterior segment image of the left eye EL and the anterior segment image of the right eye ER. The processing unit 9 calculates corneal shape parameters representing the shape of the corneal CLr and corneal shape parameters representing the shape of the corneal CRr by performing known calculations based on this keratin image.

[0079] (Ref measurement projection system 6L, 6R, Ref measurement light receiving system 7) The refractometer optical system includes refractometer projection systems 6L and 6R and a refractometer light receiving system 7 used for refractive power measurement. The refractometer projection system 6L projects a light beam for refractive power measurement (e.g., a ring-shaped light beam) (infrared light) onto the fundus ELf of the left eye under examination EL. The refractometer projection system 6R projects a light beam for refractive power measurement (e.g., a ring-shaped light beam) (infrared light) onto the fundus ERf of the right eye under examination ER. The refractometer light receiving system 7 receives the reflected light from the left eye under examination EL and the reflected light from the right eye under examination ER of the light beam for refractive power measurement.

[0080] As shown in Figure 7, the refractometer projection system 6L is located in an optical path branched by a perforated prism 65L, which is located in the optical path of the refractometer light-receiving system 7 on the measurement optical axis OL passing through the objective lens 51. The refractometer projection system 6R is located in an optical path branched by a perforated prism 65R, which is located in the optical path of the refractometer light-receiving system 7 on the measurement optical axis OR passing through the objective lens 51. The perforation formed in the perforated prism 65L is positioned at the pupil conjugate position of the left eye under examination EL. The perforation formed in the perforated prism 65R is positioned at the pupil conjugate position of the right eye under examination ER. In the optical system passing through the refractometer light-receiving system 7, the imaging surface of the image sensor 59 is positioned at the fundus conjugate position.

[0081] In some embodiments, at least one of the refractometer light sources 61L, 61R is a high-luminosity light source, specifically a Superluminescent Diode (SLD) light source. Each of the refractometer light sources 61L, 61R is movable in the optical axis direction. The refractometer light source 61L is positioned at the fundus conjugate position of the left eye under examination (EL). The refractometer light source 61R is positioned at the fundus conjugate position of the right eye under examination (ER). In some embodiments, the functions of the refractometer light sources 61L, 61R are realized by a single light source. In some embodiments, the functions of the relay lenses 62L, 62R are realized by a single relay lens.

[0082] Light output from the refractometer light source 61L passes through the relay lens 62L and is incident on the conical surface of the conical prism 63L. The light incident on the conical surface is deflected and exits from the bottom surface of the conical prism 63L. The light exiting from the bottom surface of the conical prism 63L passes through the ring-shaped light-transmitting section formed in the ring diaphragm 64L. The light that has passed through the light-transmitting section of the ring diaphragm 64L (ring-shaped light beam) is reflected by the reflective surface formed around the hole in the perforated prism 65L, passes through the rotary prism 66, and is reflected by the dichroic mirror 67. The light reflected by the dichroic mirror 67 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the left eye under examination EL. The rotary prism 66 is used to average the light intensity distribution of the ring-shaped light beam to the blood vessels and diseased areas of the fundus and to reduce speckle noise caused by the light source.

[0083] The reflected light from the ring-shaped beam projected onto the fundus ELf of the left eye under examination passes through the objective lens 51 and is reflected by the dichroic mirror 52 and the dichroic mirror 67. The reflected light from the dichroic mirror 67 passes through the rotary prism 66, through the opening of the perforated prism 65L, through the relay lens 71, is reflected by the reflection mirror 72, and then passes through the relay lens 73 and the focusing lens 74. The focusing lens 74 is movable along the optical axis of the refractor measurement and light receiving system 7. The light that has passed through the focusing lens 74 is reflected by the reflection mirror 75, reflected by the dichroic mirror 76, and is imaged onto the imaging surface of the image sensor 59 by the imaging lens 58.

[0084] Similarly, light output from the reflector light source 61R passes through the relay lens 62R and is incident on the conical surface of the conical prism 63R. The light incident on the conical surface is deflected and exits from the bottom surface of the conical prism 63R. The light exiting from the bottom surface of the conical prism 63R passes through the ring-shaped light-transmitting section formed in the ring aperture 64R. The light that has passed through the light-transmitting section of the ring aperture 64R (ring-shaped luminous beam) is reflected by the reflective surface formed around the hole in the perforated prism 65R, passes through the rotary prism 66, and is reflected by the dichroic mirror 67. The light reflected by the dichroic mirror 67 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the right eye under examination ER.

[0085] The ring-shaped beam of light projected onto the fundus ERf of the right eye under examination passes through the objective lens 51 and is reflected by the dichroic mirror 52 and the dichroic mirror 67. The reflected light from the dichroic mirror 67 passes through the rotary prism 66, through the perforation of the perforated prism 65R, through the relay lens 71, is reflected by the reflective mirror 72, and then passes through the relay lens 73 and the focusing lens 74. The light that has passed through the focusing lens 74 is reflected by the reflective mirror 75, reflected by the dichroic mirror 76, and is imaged onto the imaging surface of the image sensor 59 by the imaging lens 58.

[0086] The processing unit 9 calculates the refractive power values ​​of the left eye EL and the right eye ER by performing known calculations based on the output from the image sensor 59. Specifically, the processing unit 9 identifies a ring pattern image from the left eye EL based on the output from the image sensor 59 and calculates the refractive power value of the left eye EL by performing known calculations on the identified ring pattern image. The processing unit 9 also identifies a ring pattern image from the right eye ER based on the output from the image sensor 59 and calculates the refractive power value of the right eye ER by performing known calculations on the identified ring pattern image. For example, the refractive power value includes spherical power, astigmatism power and astigmatism axis angle, or equivalent spherical power.

[0087] In some embodiments, the measurement optical system 300 includes fixation projection systems 4L and 4R.

[0088] (OCT optical system 8) The OCT optical system 8 is an optical system for performing OCT measurements. For example, based on the refraction measurement results 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 to the imaging site (fundus or anterior segment) and the optical system.

[0089] The OCT optical system 8 is positioned in an optical path wavelength-separated from the optical path of the reflector measurement optical system by a dichroic mirror 67. The optical axis of the OCT optical system 8 can be adjusted to substantially coincide with either the measurement optical axis OL or OR.

[0090] The OCT optical system 8 includes an OCT unit 100. As shown in Figure 8, the OCT unit 100 is equipped with an optical system for performing OCT measurement (OCT imaging, OCT scanning) on ​​either the left eye EL or the right 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, interfere the measurement light that has passed through the eye (OCT measurement site) with the reference light that has passed through the reference light path to generate interference light, and detect the spectral components of this interference light. This detection result (detection signal) is sent to the processing unit 9.

[0091] The light source unit 101 outputs broadband low-coherence light L0. Low-coherence light L0 has wavelength components in the near-infrared region (approximately 800 nm to 900 nm) and has a temporal coherence length of several tens of micrometers. Alternatively, near-infrared light with a wavelength range invisible to the human eye, for example, a central wavelength of approximately 1040 to 1060 nm, may be used as low-coherence light L0.

[0092] Hereinafter, the light source unit 101 will output low-coherence light L0 having a wavelength component of 840 nm.

[0093] The light source unit 101 is composed of optical output devices such as a superluminescent diode (SLD), an LED, and a semiconductor optical amplifier (SOA).

[0094] The low-coherence light L0 output from the light source unit 101 is guided by the optical fiber 102 to the fiber coupler 103, where it is split into measurement light LS and reference light LR.

[0095] The reference light LR is guided by the optical fiber 104 and reaches the attenuator 105. The attenuator 105 automatically adjusts the amount of light LR guided by the optical fiber 104 under the control of the processing unit 9 using known technology. The reference light LR, whose amount has been adjusted by the attenuator 105, is guided by the optical fiber 104 and reaches the polarization controller 106. The polarization controller 106 is a device that adjusts the polarization state of the reference light LR guided within the optical fiber 104 by, for example, 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 the fiber coupler 109.

[0096] The measurement light LS generated by the fiber coupler 103 is guided by the optical fiber f1 to the collimator lens 90 (Figure 6), where it is made into a parallel beam. Furthermore, the measurement light LS passes through the optical path length changing unit 89, the optical scanner 88, the focusing lens 87, the relay lenses 85 and 82, and the reflective mirror 81 before reaching the dichroic mirror 67.

[0097] 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 movement in the optical axis direction while maintaining the optical positional relationship between the focusing lens 87 and the optical scanner 88. By configuring the focusing lens 87 and the optical scanner 88 to be movable as a single unit, it becomes possible to adjust the optical system while maintaining the conjugate relationship between the optical scanner 88 and the eye under examination. Furthermore, in this configuration, the magnification relationship between the pupil of the eye under examination and the optical scanner 88 can be easily changed by changing the focal length f of the focusing lens 87.

[0098] 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 from the processing unit 9. For example, the pupil of the eye under examination 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, the pupil-conjugate relationship is maintained, and the deflection surface of the optical scanner 88 is positioned at the pupil-conjugate position).

[0099] 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 can move along the optical path of the measurement light LS and the optical path of the return light of the measurement light LS, and the optical path length of the measurement light LS is changed by moving the retroreflector.

[0100] The optical scanner 88 deflects the measurement light LS in one or two dimensions.

[0101] 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 to scan the OCT measurement area 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 to scan the imaging area in a vertical direction (Y direction) perpendicular to the optical axis of the OCT optical system 8. Examples of scanning modes for the measurement light LS by such an optical scanner 88 include horizontal scanning, vertical scanning, cross scanning, radial scanning, circular scanning, concentric circle scanning, spiral scanning, and Lissajous scanning.

[0102] In some embodiments, the optical scanner 88 includes a MEMS scanner (MEMS mirror scanner) that deflects the measurement light LS in two dimensions. The MEMS scanner deflects the measurement light LS to scan the OCT measurement site in horizontal and vertical directions perpendicular to the optical axis of the OCT optical system 8.

[0103] In addition to the galvanometer mirror and MEMS scanner, the optical scanner 88 may also be composed of a polygon mirror, a rotating mirror, a dove prism, a double dove prism, a rotation prism, and the like.

[0104] 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 by the prism mirror PR towards the dichroic mirror ML or the dichroic mirror MR. 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 eye EL or the right eye ER. The measurement light LS is scattered (including reflected) at various depth positions of the OCT measurement site. The backscattered light of the measurement light LS from the OCT measurement site travels in the reverse direction along the same path as the forward path and is guided to the fiber coupler 103, and reaches the fiber coupler 109 via the optical fiber 108.

[0105] The fiber coupler 109 interferes the backscattered light of the measurement light LS with the reference light LR that has passed through the attenuator 105, etc. The resulting interference light LC is guided by the optical fiber 110 and emitted from the output end 111. Furthermore, the interference light LC is made into a parallel beam by the collimator lens 112, spectrally decomposed by the diffraction grating (spectrometer) 113, focused by the zoom optical system 114, and projected onto the light-receiving surface of the CCD image sensor 115. Although the diffraction grating 113 shown in Figure 8 is a transmissive type, it is also possible to use other types of spectroscopic elements, such as a reflective diffraction grating.

[0106] The CCD image sensor 115 is, for example, a line sensor, and has two or more light-receiving elements (detection elements) arranged in a row. It detects each spectral component of the spectrally separated interference light LC and converts it into an electric charge. The CCD image sensor 115 stores this charge to generate a detection signal, which it sends to the processing unit 9.

[0107] In this embodiment, a Michelson interferometer is employed, but any type of interferometer, such as a Mach-Zehnder type, can be used as appropriate. Furthermore, other types of image sensors, such as a CMOS (Complementary Metal Oxide Semiconductor) image sensor, can be used instead of a CCD image sensor.

[0108] Furthermore, in the configuration shown in Figure 6, the difference between the optical path length of the measurement light LS and the optical path length of the reference light LR is changed by changing the optical path length of the measurement light LS using the optical path length changing unit 89. However, the configuration according to this embodiment is not limited to this. For example, the difference between the optical path length of the measurement light LS and the optical path length of the reference light LR may be changed by changing the optical path length of the reference light LR using a known method.

[0109] The processing unit 9 calculates the refractive power value of the left eye EL from the measurement results obtained using the refractometer optical system, and moves the refractometer light source 61L in the optical axis direction to a position where the fundus ELf, the refractometer light source 61L, and the image sensor 59 are conjugate, based on the calculated refractive power value. The processing unit 9 also calculates the refractive power value of the right eye ER from the measurement results obtained using the refractometer optical system, and moves the refractometer light source 61R in the optical axis direction to a position where the fundus ERf, the refractometer light source 61R, and the image sensor 59 are conjugate, based on the calculated refractive power value. In some embodiments, the processing unit 9 moves the focusing lens 74 to a position corresponding to the combined refractive value (e.g., intermediate power) obtained from the refractive value of the left eye EL and the refractive value of the right eye ER.

[0110] 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 61L 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 61R and the focusing lens 74.

[0111] In the above embodiment, at least one function of the focusing lenses 74 and 87 may be realized by a liquid crystal lens or a liquid lens.

[0112] The optical system configuration of the ophthalmic apparatus 1 according to this embodiment is not limited to the configuration shown in Figures 1 to 8.

[0113] <Example of anterior segment camera placement> Figure 9 schematically shows an example of the arrangement of the anterior segment cameras 15LA, 15RA, 15LB, and 15LB as shown in Figure 1.

[0114] As shown in Figure 9, for example, the anterior segment camera 15LA is positioned to photograph the left eye EL from a direction that forms a positive angle in the Y direction with respect to the measurement optical axis OL, and the anterior segment camera 15LB is positioned to photograph the left eye EL from a direction that forms a negative angle in the Y direction with respect to the measurement optical axis OL. Alternatively, the anterior segment camera 15LA may be positioned to photograph the left eye EL from a direction that forms a positive angle in the X direction with respect to the measurement optical axis OL, and the anterior segment camera 15LB may be positioned to photograph the left eye EL from a direction that forms a negative angle in the X direction with respect to the measurement optical axis OL.

[0115] Similarly, for example, the anterior segment camera 15RA is positioned to photograph the right eye ER from a direction that forms a positive angle in the Y direction with respect to the measurement optical axis OR, and the anterior segment camera 15RB is positioned to photograph the right eye ER from a direction that forms a negative angle in the Y direction with respect to the measurement optical axis OR. The anterior segment camera 15RA may be positioned to photograph the right eye ER from a direction that forms a positive angle in the X direction with respect to the measurement optical axis OR, and the anterior segment camera 15RB may be positioned to photograph the right eye ER from a direction that forms a negative angle in the X direction with respect to the measurement optical axis OR.

[0116] Some of the functions of the anterior segment cameras 15LA, 15RA, 15LB, and 15LB may be implemented in a single anterior segment camera.

[0117] Figure 10 schematically shows an example of the configuration when the functions of the anterior segment cameras 15LB and 15RB in Figure 1 are implemented using the anterior segment camera 15LR.

[0118] The anterior segment camera 15LR captures images of the anterior segment of the left eye EL and the anterior segment of the right eye ER. As shown in Figure 10, for example, the anterior segment camera 15LA is positioned to capture images of the left eye EL from a direction that forms a positive angle in the Y direction with respect to the measurement optical axis OL, and the anterior segment camera 15LR is positioned to capture images of the left eye EL from a direction that forms a negative angle in the Y direction with respect to the measurement optical axis OL. Alternatively, the anterior segment camera 15LA may be positioned to capture images of the left eye EL from a direction that forms a positive angle in the X direction with respect to the measurement optical axis OL, and the anterior segment camera 15LR may be positioned to capture images of the left eye EL from a direction that forms a negative angle in the X direction with respect to the measurement optical axis OL.

[0119] Similarly, for example, the anterior eye camera 15RA captures the right eye to be examined 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 arranged to capture the right eye to be examined 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 arranged to capture the right eye to be examined 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 arranged to capture the right eye to be examined ER from a direction forming a negative angle in the X direction with respect to the measurement optical axis OR.

[0120] The ophthalmic apparatus 1 according to the embodiment can execute refraction measurement (refractive power measurement) using the refraction measurement optical system and OCT measurement using the OCT optical system 8 while sharing the objective lens at least in the refraction measurement optical system and the OCT optical system 8. The refraction measurement can be executed simultaneously for the left eye to be examined and the right eye to be examined. The OCT measurement can be executed sequentially for either the left eye to be examined or the right eye to be examined. In some embodiments, before performing the 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 the OCT measurement on one eye to be examined, the 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.

[0121] The ophthalmic apparatus 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.

[0122] <Example of adjustment of the optical axis of the OCT optical system 8> FIG. 11A 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. 11A, the same parts as those in FIG. 1 are denoted by the same reference numerals, and the description thereof is omitted as appropriate.

[0123] ​The measurement optical system 300 includes deflection members DF1 and DF2. Deflection member DF1 deflects the optical axis of the OCT optical system 8 toward deflection member DF2, and deflection member DF2 deflects the optical axis deflected by deflection member DF1 toward the prism mirror PR. For example, by moving deflection member DF1 in the optical axis direction, 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 deflection member DF1', the optical axis of the OCT optical system 8 can be approximately coincided with the measurement optical axis OL, and at the position of deflection member DF1, the optical axis of the OCT optical system 8 can be approximately coincided with the measurement optical axis OR.

[0124] For example, the ophthalmic device 1 can adjust the optical axis of the OCT optical system 8 to approximately coincide with either the measurement optical axis OL or OR by moving the deflection member DF1 according to the interpupillary distance of the subject.

[0125] In Figure 6, a reflective mirror 81 is an example of a deflection member DF1. A dichroic mirror 52 is an example of a deflection member DF2.

[0126] Figure 11B shows an explanatory diagram of a second adjustment example of the optical axis of the OCT optical system 8 according to the first embodiment. In Figure 11B, the same reference numerals are used for parts that are the same as in Figure 1, and explanations are omitted as appropriate.

[0127] The measuring optical system 300 (ophthalmic device 1) includes a moving mechanism that moves the OCT optical system 8 under the control of the control unit described later. For example, this moving mechanism moves the OCT optical system 8 (specifically the OCT unit 100) independently of the optical elements in 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 coincided 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 coincided with the measurement optical axis OR.

[0128] For example, the ophthalmic device 1 can adjust the position of the optical axis of the OCT optical system 8 (OCT unit 100) to approximately coincide with either the measurement optical axis OL or OR by moving the position of the optical axis of the OCT optical system 8 according to the interpupillary distance of the subject.

[0129] Figure 11C shows an explanatory diagram of a third adjustment example of the optical axis of the OCT optical system 8 according to the first embodiment. In Figure 11C, the same reference numerals are used for parts that are the same as in Figure 1, and explanations are omitted as appropriate.

[0130] The measuring optical system 300 (ophthalmic device 1) includes a moving mechanism that moves a prism mirror PR (or a reflective mirror RML, RMR shown in Figure 5) in the X direction under control from the control unit described later. This moving mechanism may also move the prism mirror PR in a direction intersecting the Z direction. For example, by moving the prism mirror PR in the X direction, 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, OR to the other. For example, at the position of the prism mirror PR', the optical axis of the OCT optical system 8 can be approximately aligned with the measurement optical axis OL, and at the position of the prism mirror PR, the optical axis of the OCT optical system 8 can be approximately aligned with the measurement optical axis OR.

[0131] For example, the ophthalmic device 1 can adjust the optical axis of the OCT optical system 8 to approximately coincide with either the measurement optical axis OL or OR by moving the prism mirror PR in the X direction according to the interpupillary distance of the subject.

[0132] Furthermore, as a fourth example of adjusting the optical axis of the OCT optical system 8 according to the first embodiment, it is possible to change the deflection direction of the optical axis of the OCT optical system 8 by using optical elements in the path of the measurement light. Examples of optical elements include the reflective mirror 81 and dichroic mirror 52 shown in Figure 6, and reflective mirrors 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, which is deflected by the optical elements based on the interpupillary distance of the subject.

[0133] <System Configuration> The configuration of the processing system for ophthalmic device 1 will be explained.

[0134] Figures 12 and 13 show examples of the functional configuration of the processing system of the ophthalmic device 1. Figure 12 represents an example of a functional block diagram of the processing system of the ophthalmic device 1. Figure 13 represents an example of a functional block diagram of the OCT optical system 8 in Figure 12. In Figures 12 and 13, the same reference numerals are used for parts that are the same as those in Figure 1 or Figure 6, and explanations are omitted as appropriate.

[0135] The processing unit 9 controls each part of the ophthalmic device 1. The processing unit 9 is also capable of performing various calculations. The functions of the processing unit 9 are realized by processing circuits. The processing unit 9 includes one or more processors. The functions of the processors are realized by circuits such as a CPU (Central Processing Unit), GPU (Graphics Processing Unit), ASIC (Application Specific Integrated Circuit), and programmable logic devices (e.g., SPLD (Simple Programmable Logic Device), CPLD (Complex Programmable Logic Device), FPGA (Field Programmable Gate Array)). The processing unit 9 realizes the functions according to the embodiment by, for example, reading and executing programs stored in memory circuits or memory devices.

[0136] In some embodiments, the processing unit 9 includes a single processor that implements the functions according to the embodiment. In some embodiments, the processing unit 9 includes a plurality of processors, each implementing one or more functions according to the embodiment.

[0137] The processing unit 9 includes a control unit 210 and an arithmetic processing unit 220. The ophthalmic device 1 also includes moving mechanisms 200, 310, and 320, a display unit 270, an operation unit 280, and a communication unit 290.

[0138] The moving mechanism 200 is a mechanism for moving the head unit, which houses optical systems such as the anterior segment cameras 15LA, LB, RA, RB, XY alignment system 2, keratometry system 3, anterior segment observation system 5, refractometry projection systems 6L, 6R, refractometry light receiving system 7, and OCT optical system 8, in the X, Y, and Z directions. For example, the moving 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 composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears or a rack and pinion. The control unit 210 (main control unit 211) controls the moving mechanism 200 by sending control signals to the actuator.

[0139] The moving mechanism 310 moves the prism mirror PR as shown in Figure 3. For example, the moving mechanism 310 has the same configuration as the moving mechanism 200. The control unit 210 (main control unit 211) controls the moving mechanism 310 by sending control signals to the actuator.

[0140] As shown in Figure 4, the moving mechanism 320 rotates the dichroic mirrors ML and MR independently around their respective pivot axes. For example, the moving mechanism 320 is provided with actuators that generate driving force to rotate 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 moving mechanism 320 by sending control signals to the actuators.

[0141] Although not shown in the diagrams, the ophthalmic device 1 may include a mechanism for adjusting the optical axis of the OCT optical system 8 shown in Figures 11A to 11C. For example, the above 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 above mechanism by sending control signals to the actuators.

[0142] (Control unit 210) The control unit 210 includes a processor and controls each part of the ophthalmic device 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 device 1 in advance. The computer programs include a program for controlling the anterior segment camera, a program for controlling the XY alignment system, a program for controlling the keratometry system, a program for controlling the fixation projection system, a program for controlling anterior segment observation, a program for controlling refraction measurement, a program for controlling OCT measurement, a program for calculation processing, a program for the user interface, a program for communication control, and the like. The control unit 210 executes control processing by operating the main control unit 211 according to these computer programs.

[0143] The main control unit 211, as a measurement control unit, performs various controls on the ophthalmic equipment. Controls for the anterior segment 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 anterior segment cameras 15LA and 15LB, synchronization control of anterior segment cameras 15RA and 15RB, and synchronization control of anterior segment cameras 15LA, 15LB, 15RA, and 15RB.

[0144] The anterior segment cameras 15LA and 15LB capture images of the anterior segment of the left eye EL from different directions substantially simultaneously. The main control unit 211 controls the data processing unit 223 (described later) to determine the three-dimensional position of the left eye EL from the two images acquired by the anterior segment cameras 15LA and 15LB. The data processing unit 223 identifies characteristic positions corresponding to characteristic parts of the anterior segment of the left eye EL by analyzing each of the two images obtained substantially simultaneously by the anterior segment cameras 15LA and 15LB and applying known trigonometry, as disclosed in, for example, Japanese Patent Application Publication No. 2013-248376. The characteristic part of the anterior segment is, for example, the pupil center. Furthermore, the data processing unit 223 determines the three-dimensional position of the left eye EL based on the identified characteristic positions. In this example, the position of the pupil center approximates the position of the eye. Furthermore, the position of the corneal apex can be determined as the position of the eye under examination by using the distance between the corneal apex and the pupil in the eye under examination, or the distance between the corneal apex and the pupil in a standard eye (model eye, average value, etc.).

[0145] The anterior segment cameras 15RA and 15RB capture images of the anterior segment of the right eye ER from different directions substantially simultaneously. The main control unit 211 controls the data processing unit 223 (described later) to determine the three-dimensional position of the right eye ER from the two images acquired by the anterior segment cameras 15RA and 15RB. The data processing unit 223 analyzes each of the two images obtained substantially simultaneously by the anterior segment cameras 15RA and 15RB and applies known trigonometry to identify feature locations corresponding to characteristic parts of the anterior segment of the right eye ER. Furthermore, the data processing unit 223 determines the three-dimensional position of the right eye ER based on the identified feature locations.

[0146] The main control unit 211 can perform optical system alignment for the left eye EL and the right eye ER by controlling the movement mechanism 200 based on the three-dimensional positions of the left eye EL and the right eye ER identified by the data processing unit 223. Furthermore, the main control unit 211 can adjust the interpupillary distance and convergence angle by controlling the movement mechanisms 310 and 320 based on the identified three-dimensional positions of the left eye EL and the right eye ER. In addition, the main control unit 211 can perform optical axis adjustment to approximate the optical axis of the OCT optical system 8 to either the measurement optical axis OL or OR based on the identified three-dimensional positions of the left eye EL and the right eye ER.

[0147] 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 allows the XY alignment light source 21 to be switched on and off, or its light intensity to be changed. The main control unit 211 acquires the signal detected by the image sensor 59 and controls the data processing unit 223 to determine the position of the bright spot image based on the reflected light from the XY alignment light source 21 based on the acquired signal. The main control unit 211 controls the movement mechanism 200 to move the head unit in the left, right, up, and down directions so that the displacement between the position of the bright spot image and a predetermined target position is canceled out (XY alignment).

[0148] Control of the keratography measurement system 3 includes control of the keratography light source 32. Control of the keratography light source 32 includes turning the light source on and off, adjusting the light intensity, and adjusting the aperture. This switches the keratography light source 32 on and off, and changes the light intensity. The main control unit 211 causes the calculation processing unit 220 (data processing unit 223) to perform known calculations on the keratography image detected by the image sensor 59. This determines the corneal shape parameters of the eye being examined.

[0149] Control of the fixation projection systems 4L and 4R includes control of the liquid crystal panels 41L and 41R, and movement control of the fixation units 40L and 40R. Control of the liquid crystal panels 41L and 41R includes turning the display of the fixation target on and off, switching the fixation target according to the type of examination or measurement, and switching the display position of the fixation target.

[0150] Furthermore, for example, the fixation projection systems 4L and 4R are provided with a moving mechanism that moves each of the liquid crystal panels 41L and 41R (or fixation units 40L and 40R) in the direction of the optical axis. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the moving mechanism by sending control signals to the actuator, thereby moving at least each of the liquid crystal panels 41L and 41R in the direction of the optical axis. 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, are optically conjugate.

[0151] 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 switches the anterior segment illumination light source 50 on and off, and changes the light intensity. The lens movement mechanism, like the movement mechanism 200, is provided with an actuator that generates a driving force to move the movement mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the lens movement mechanism by sending a control signal to the actuator, moving the relay lens 56 in the optical axis direction. Control of the image sensor 59 includes exposure adjustment, gain adjustment, and detection rate adjustment of the image sensor 59. The main control unit 211 takes in the signal detected by the image sensor 59 and causes the arithmetic processing unit 220 to perform processing such as image formation based on the acquired signal.

[0152] Control of the reflector measurement projection systems 6L and 6R includes control of the reflector measurement light sources 61L and 61R, and control of the rotary prism 66. Control of the reflector measurement light sources 61L and 61R includes turning the light sources on and off, and adjusting the light intensity. This allows switching between on and off, and changing the light intensity of the reflector measurement light sources 61L and 61R. For example, the reflector measurement projection system 6L includes a moving mechanism that moves the reflector measurement light source 61L in the direction of the optical axis, and the reflector measurement projection system 6R includes a moving mechanism that moves the reflector measurement light source 61R in the direction of the optical axis. These moving mechanisms are provided with an actuator that generates a driving force to move the moving mechanism and a transmission mechanism that transmits this driving force, similar to the moving mechanism 200. The main control unit 211 controls the moving mechanisms by sending control signals to the actuators, and moves each of the reflector measurement light sources 61L and 61R independently in the direction of the optical axis. In some embodiments, the reflector measurement light sources 61L and 61R are moved together as a single unit. Control of the rotary prism 66 includes controlling its rotation. For example, a rotation mechanism is provided to rotate the rotary prism 66, and the main control unit 211 rotates the rotary prism 66 by controlling this rotation mechanism.

[0153] Control of the refractometer light-receiving system 7 includes control of the focusing lens 74. Control of the focusing lens 74 includes control of its movement in the optical axis direction. For example, the refractometer 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 to move 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 focusing lens 74 in the optical axis direction. The main control unit 211 can move the refractometer light source 61L and the focusing lens 74 in the optical axis direction, for example, according to the refractive power of the left eye EL, so that the refractometer light source 61L, the fundus ELf, and the image sensor 59 are optically conjugate. Furthermore, the main control unit 211 can move the refractometer light source 61R and the focusing lens 74 in the optical axis direction, for example, according to the refractive power of the right eye ER, so that the refractometer light source 61R, the fundus ERf, and the image sensor 59 are optically conjugate.

[0154] 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 changing unit 89.

[0155] 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 L and R. Control of the polarization controller 106 includes adjusting the polarization state of the reference light L and R. 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 takes in the signal detected by the CCD image sensor 115 and causes the arithmetic processing unit 220 to perform processing such as image formation based on the acquired signal.

[0156] Control of the focusing lens 87 includes controlling its movement 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 to move 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 focusing lens 87 in the optical axis direction.

[0157] In some embodiments, the ophthalmic device 1 is provided with a holding member for holding the focusing lenses 74 and 87, and a drive unit for driving the holding member. The main control unit 211 controls the movement of the focusing lenses 74 and 87 by controlling the drive unit. For example, the main control unit 211 may move the focusing lens 87 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.

[0158] Control of the optical scanner 88 includes setting a scan mode for scanning the measurement area 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 angular 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 changes. 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.

[0159] The control of the optical path length changing unit 89 includes controlling 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.

[0160] Furthermore, the main control unit 211 performs processes to write data to the storage unit 212 and processes to read data from the storage unit 212.

[0161] (Storage unit 212) The memory unit 212 stores various types of data. Examples of data stored in the memory unit 212 include objective measurement results (OCT measurement results), OCT image data, anterior segment image data, subjective examination results, and subject eye information. Subject eye information includes patient information such as patient ID and name, and information about the subject eye such as left / right eye identification. The memory unit 212 also stores various programs and data necessary for operating the ophthalmic device.

[0162] (Processing unit 220) The arithmetic processing unit 220 includes a processor and performs various arithmetic operations. A storage unit (for example, storage unit 212), not shown in the diagram, stores computer programs for performing various arithmetic operations in advance. The processor operates according to these computer programs, thereby realizing the functions of each unit that performs various arithmetic operations.

[0163] As shown in Figure 12, the calculation processing unit 220 includes an eye refractive power calculation unit 221, an image forming unit 222, and a data processing unit 223.

[0164] The refractive power calculation unit 221 calculates the refractive values ​​of the left eye EL and the right eye ER based on the results of refractometer measurements performed simultaneously on both eyes. The image forming unit 222 forms an OCT image based on the detection results of interference light LC acquired using the OCT optical system 8. The data processing unit 223 performs various data processing (image processing) and analysis processes on the measurement results (such as the detection results of interference light LC) obtained using the optical system of the ophthalmic device 1 and the OCT image formed by the image forming unit 222.

[0165] (Eye refractive power calculation unit 221) The refractive power calculation unit 221 analyzes the ring image (pattern image) obtained when the image sensor 59 receives the reflected light of the ring-shaped light beam (ring-shaped measurement pattern) projected onto the fundus ELf by the refractometer measurement projection system 6L, and calculates the refractive power value of the left eye EL. The refractive power calculation unit 221 also analyzes the ring image (pattern image) obtained when the image sensor 59 receives the reflected light of the ring-shaped light beam projected onto the fundus ERf by the refractometer measurement projection system 6R, and calculates the refractive power value of the right eye ER. For example, for each ring image, the refractive power calculation unit 221 determines the centroid position of the ring image from the brightness distribution in the image in which the ring image is depicted, determines the brightness distribution along multiple scanning directions extending radially from this centroid position, and identifies the ring image from this brightness distribution. Next, the refractive power calculation unit 221 determines an approximate ellipse of the identified ring image, and calculates the spherical power, astigmatism power, and astigmatism axis angle by substituting the major and minor axes of this approximate ellipse into known formulas. Alternatively, the refractive power calculation unit 221 can determine the parameters of the refractive power based on the deformation and displacement of the ring image relative to the reference pattern.

[0166] Furthermore, the refractive power calculation unit 221 calculates the corneal refractive power, corneal astigmatism, and corneal astigmatism axis angle of the left eye EL and the right eye ER, respectively, based on the keratling images of the left eye EL and the right eye ER obtained by the anterior segment observation system 5. For example, for each keratling image, the refractive power calculation unit 221 calculates the corneal curvature radius of the strong principal meridian and weak principal meridian on the anterior surface of the cornea by analyzing the keratling image, and calculates the above parameters based on the corneal curvature radius.

[0167] (Image forming unit 222) The image forming unit 222 forms OCT image (tomographic image) data of the eye under examination based on the detection signal of the interferential light LC obtained by the CCD image sensor 115. That is, the image forming unit 222 forms image data of the eye under examination based on the detection result of the interferential light LC by the interferometric optical system. This process includes processing such as filtering and FFT (Fast Fourier Transform), similar to conventional spectral domain type OCT. The image data acquired in this way is a dataset containing a group of image data formed by imaging the reflectance intensity profiles of multiple A lines (paths of each measurement light LS within the eye under examination).

[0168] To improve image quality, multiple datasets collected by repeatedly scanning the same pattern can be superimposed (averaged).

[0169] (Data processing unit 223) The data processing unit 223 performs various data processing (image processing) and analysis processes on the tomographic image formed by the image forming unit 222. For example, the data processing unit 223 performs correction processes such as brightness correction and dispersion correction on the image. The data processing unit 223 also performs various image processing and analysis processes on the image obtained using the anterior segment observation system 5 (anterior segment image, etc.).

[0170] The data processing unit 223 can form volume data (voxel data) of the eye under examination by performing known image processing, such as interpolation, which interpolates pixels between tomographic images. When displaying an image based on the volume data, the data processing unit 223 performs rendering processing on this volume data to form a pseudo-3D image as seen from a specific line of sight direction.

[0171] The data processing unit 223 can perform known image processing, such as interpolation, to interpolate pixels between OCT images (tomographic images) formed by the image forming unit 222, thereby forming image data of a three-dimensional image of the fundus or anterior segment of the eye. Three-dimensional image data refers to image data in which the position of pixels is defined by a three-dimensional coordinate system. Three-dimensional image data can consist of voxels arranged in three dimensions. This image data is called volume data or voxel data. When displaying an image based on volume data, the data processing unit 223 performs rendering processing (such as volume rendering or MIP (Maximum Intensity Projection)) on this volume data to form pseudo-three-dimensional image data 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.

[0172] Furthermore, it is possible to form stacked data of multiple tomographic images as 3D image data. Stacked data is image data obtained by arranging multiple tomographic images obtained along multiple scan lines in a 3D manner based on the positional relationship of the scan lines. In other words, stacked data is image data obtained by representing multiple tomographic images, which were originally defined by separate 2D coordinate systems, using a single 3D coordinate system (i.e., embedding them in a single 3D space).

[0173] The data processing unit 223 can perform various rendering operations on the acquired 3D dataset (volume data, stack data, etc.) to form B-mode images (longitudinal images, axial images), C-mode images (transverse images, horizontal images), projection images, shadowgrams, etc., in arbitrary cross-sections. Images of arbitrary cross-sections, such as B-mode and C-mode images, are formed by selecting pixels (voxels) on a specified cross-section from the 3D dataset. Projection images are formed by projecting the 3D dataset in a predetermined direction (Z-direction, depth direction, axial direction). Shadowgrams are formed by projecting a portion of the 3D dataset (for example, partial data corresponding to a specific layer) in a predetermined direction. Images such as C-mode images, projection images, and shadowgrams, which are viewed from the front of the eye being examined, are called en-face images.

[0174] The data processing unit 223 can construct B-mode images and frontal images (vascular-enhanced images, angiograms) that highlight retinal and choroidal blood vessels based on data collected in time series by OCT scanning (e.g., B-scan image data). For example, time-series OCT data can be collected by repeatedly scanning approximately the same area of ​​the eye being examined.

[0175] In some embodiments, the data processing unit 223 compares time-series B-scan images obtained by B-scanning substantially the same area and constructs an enhanced image in which the changed portion is emphasized by converting the pixel values ​​of the changed portion to pixel values ​​corresponding to the change. Furthermore, the data processing unit 223 extracts a predetermined thickness of information from the multiple enhanced images constructed for a desired area and constructs it as an en-face image to form an OCTA image.

[0176] Images generated by the data processing unit 223 (e.g., 3D images, B-mode images, C-mode images, projection images, shadowgrams, OCTA images) are also included in the OCT image.

[0177] Furthermore, as described above, the data processing unit 223 identifies feature locations corresponding to feature regions of the anterior segment by analyzing each of the two captured images acquired substantially simultaneously by the two anterior segment cameras. The data processing unit 223 calculates the three-dimensional position of the feature region (i.e., the three-dimensional position of the eye under examination) by applying known trigonometry to the positions of the two anterior segment cameras and the feature locations corresponding to the feature regions in the two identified captured images. The calculated three-dimensional position can be used to align the optical system with respect to the eye under examination.

[0178] Furthermore, the ophthalmic device 1 can measure intraocular parameters by performing an OCT scan on the left eye EL or the right eye ER. Examples of intraocular parameters include axial length, thickness of a predetermined layer region, and distance between predetermined regions.

[0179] 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 axial length as the distance between a position corresponding to the corneal apex and a position corresponding to the retinal pigment epithelium (RPE) layer, based on the detection results of 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 intensity of the interference signal corresponding to the detection results of interference light LC, and calculates the axial length as the distance between the two identified positions. For example, the data processing unit 223 performs segmentation processing on the OCT image formed based on the detection results of interference light LC, identifies the position of the corneal apex and the RPE layer from a plurality of identified layer regions, and calculates the axial length as the distance between the two identified positions.

[0180] (Display section 270, operation section 280) The display unit 270, acting as a user interface unit, displays information under the control of the control unit 210.

[0181] The control unit 280 is used as a user interface to operate the ophthalmic device. The control unit 280 includes various hardware keys (joysticks, buttons, switches, etc.) provided on the ophthalmic device. The control unit 280 may also include various software keys (buttons, icons, menus, etc.) displayed on a touch panel screen.

[0182] At least a portion 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.

[0183] (Communications Section 290) The communication unit 290 has a function for communicating with an external device (not shown). The communication unit 290 is equipped with a communication interface according to the connection configuration with the external device. An example of an external device is an eyeglass lens measuring device for measuring the optical properties of lenses. The eyeglass lens measuring device measures the power of eyeglass lenses worn by the subject and inputs this measurement data into the ophthalmic device 1. The external device may also be any ophthalmic device, a device that reads information from a recording medium (reader), or a device that writes information to a recording medium (writer). Furthermore, the external device may also be a hospital information system (HIS) server, a DICOM (Digital Imaging and Communication in Medicine) server, a physician terminal, a mobile terminal, a personal terminal, or a cloud server. The communication unit 290 may be provided, for example, in the processing unit 9.

[0184] The member and mechanism for adjusting the optical axis of the OCT optical system 8 in any of the first to fourth adjustment examples are examples of the "optical axis adjustment unit" according to the embodiment. The data processing unit 223 is an example of the "intraocular parameter calculation unit" according to the embodiment. The anterior segment cameras 15LA, 15LB, 15RA, 15RB, and 15LR are examples of "two or more imaging units" according to the embodiment. The anterior segment camera 15LA is an example of the "first imaging unit" according to the embodiment. The anterior segment camera 15LR is an example of the "second imaging unit" according to the embodiment. The anterior segment camera 15RA is an example of the "third imaging unit" according to the embodiment. The refractometer projection systems 6L and 6R, and the refractometer light receiving system 7 are examples of the "refractive power measurement optical system" according to the embodiment. The refractometer projection system 6L is an example of the "first projection system" according to the embodiment. The refractometer projection system 6R is an example of the "second projection system" according to the embodiment. The refractometer light receiving system 7 is an example of the "light receiving system" according to the embodiment.

[0185] <Example of operation> An example of operation of the ophthalmic device 1 according to the first embodiment will be described.

[0186] Figures 14 and 15 show examples of the operation of the ophthalmic device 1. Figure 14 is a flowchart of an example of the operation of the ophthalmic device 1 when refractory measurement and OCT measurement are performed sequentially. Figure 15 is a flowchart of an example of the process in step S2 of Figure 14. The memory unit 212 stores a computer program for realizing the processes shown in Figures 14 and 15. The main control unit 211 executes the processes shown in Figures 14 and 15 by operating according to this computer program.

[0187] Here, it is assumed that, prior to the start of the flow shown in Figure 14, it has been decided that the inspection will be performed in either a near-view or near-view state.

[0188] (S1: Adjust the convergence angle) First, the main control unit 211 controls the movement mechanism 320 that rotates the dichroic mirrors ML and MR according to the target distance corresponding to the predetermined near-view or far-view state, and adjusts the convergence angle.

[0189] As shown in Figure 4, the dichroic mirrors ML and MR change the direction of the deflection of the optical axis deflected by the prism mirror PR.

[0190] (S2: Alignment) Next, the main control unit 211 performs alignment. Details of step S2 will be described later.

[0191] In step S2, the measurement optical system 300 is aligned with respect to the left eye EL and the right eye ER.

[0192] (S3: Obtain images of the anterior segment of both eyes) Next, the main control unit 211 controls the anterior segment observation system 5 to acquire anterior segment images of both eyes.

[0193] Specifically, the main control unit 211 controls the keratometry system 3 to light up the keratin ring light source 32 and project a ring-shaped light beam onto the corneal CLr of the left eye EL and the corneal CRr of the right eye ER. Subsequently, the main control unit 211 controls the anterior segment illumination light source 50 to light up the anterior segment of the left eye EL and the anterior segment of the right eye ER. After that, the main control unit 211 acquires an anterior segment image of both eyes by capturing the result of receiving the reflected light of the illumination light on the imaging surface of the image sensor 59, thereby depicting the anterior segment of the left eye EL with the keratin ring superimposed and the anterior segment of the right eye ER with the keratin ring superimposed.

[0194] In some embodiments, a ring-shaped beam of light is projected sequentially onto the left eye EL and the right eye ER to sequentially acquire an anterior segment image of the left eye EL with a superimposed keratin ring image, and an anterior segment image of the right eye ER with a superimposed keratin ring image. By combining the sequentially acquired anterior segment images of the left eye EL and the right eye ER, an anterior segment image of both eyes is obtained.

[0195] (S4: Corneal shape analysis) Next, the main control unit 211 controls the refractive power calculation unit 221 to analyze the anterior segment images of both eyes acquired in step S3. As described above, the refractive power calculation unit 221 identifies the keratin images of the left eye EL and the right eye ER depicted in the anterior segment images, and calculates the corneal refractive power, corneal astigmatism, and corneal astigmatism axis angle of the left eye EL and the right eye ER from the identified keratin images.

[0196] (S5: Provisional measurement) Next, the main control unit 211 performs a preliminary measurement for refractometry of both eyes. In the preliminary measurement, the focus state in the refractometry optical system is changed according to the refractive power of the left eye EL and the right eye ER. In the refractometry (main measurement), the refractive power of the left eye EL and the right eye ER is measured while promoting fogging of the left eye EL and the right eye ER based on the focus state changed in the preliminary measurement.

[0197] For example, the reflector measurement light sources 61L and 61R, and the focusing lenses 74 and 87 are moved in the optical axis direction and positioned to correspond to the refractive power of the eye under examination. The main control unit 211 turns on the reflector measurement light sources 61L and 61R and starts the rotation of the rotary prism 66. Next, the main control unit 211 projects a ring-shaped measurement pattern light beam onto the left eye EL and the right eye ER, respectively. A ring image based on the reflected light of the measurement pattern light beam from the left eye EL and the right eye ER is formed on the imaging surface of the image sensor 59.

[0198] The main control unit 211 determines whether or not a ring image has been acquired based on the reflected light from the fundus ELf and ERf detected by the image sensor 59. For example, the main control unit 211 detects the position (pixel) of the edge of the image based on the reflected light detected by the image sensor 59 and determines whether or not the width of the image (difference between the outer diameter and the inner diameter) is greater than or equal to a predetermined value. Alternatively, the main control unit 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) of a predetermined height (ring diameter) or greater.

[0199] When it is determined that a ring image has been acquired, the refractive power calculation unit 221 analyzes the ring image based on the reflected light of the projected measurement pattern luminous beam for each of the left eye EL and the right eye ER using a known method, and determines the provisional spherical power S and provisional astigmatism power C.

[0200] Based on the determined provisional spherical power S and astigmatism power C, the main control unit 211 moves the reflector measurement light sources 61L and 61R, the focusing lens 74, and the liquid crystal panels 41L and 41R to positions corresponding to the equivalent spherical power (S + C / 2).

[0201] Again, the main control unit 211 projects a ring-shaped measurement pattern light beam onto the left eye EL and the right eye ER, respectively. A ring image based on the reflected light from the measurement pattern light beams from the left eye EL and the right eye ER is formed on the imaging surface of the image sensor 59. The main control unit 211 determines whether or not it was possible to acquire a ring image based on the reflected light from the fundus ELf and ERf detected by the image sensor 59.

[0202] When it is determined that a ring image has been acquired, the refractive power calculation unit 221 analyzes the ring image based on the reflected light of the projected measurement pattern luminous beam for each of the left eye EL and the right eye ER using a known method, and determines the provisional spherical power S and provisional astigmatism power C.

[0203] The main control unit 211 controls the refractive power calculation unit 221 to calculate the intermediate power position of the left eye EL and the right eye ER. For example, the intermediate power position may be the position corresponding to the intermediate power ((ESR + ESL) / 2) between the equivalent spherical power ESR of the left eye EL and the equivalent spherical power ESL of the right eye ER.

[0204] The main control unit 211 moves the reflector measurement light sources 61L and 61R, the focusing lens 74, and the liquid crystal panels 41L and 41R to intermediate power positions for the left eye EL and the right eye ER, respectively. The moved positions correspond to the temporary far point.

[0205] In some embodiments, the main control unit 211 moves the refractometer light sources 61L and 61R, the focusing lens 74, and the liquid crystal panels 41L and 41R to the equivalent spherical power position for the left eye EL and the right eye ER, respectively, without determining the intermediate power position.

[0206] In step S5, if the results of the preliminary measurements for both eyes do not converge due to anisometropia or other reasons, preliminary measurements may be performed on one eye at a time. In this case, by blocking the light path of the fixation projection system on the side not being measured with a shutter or the like, and performing preliminary measurements on one eye at a time, it is possible to calculate the intermediate power position of the left eye EL and the right eye ER from the equivalent spherical power obtained, as described above.

[0207] (S6: Promote clouding and mist in both eyes) Next, the main control unit 211 moves the liquid crystal panels 41L and 41R to the respective cloud positions from the positions determined in the preliminary measurement in step S5, thereby simultaneously promoting clouding of both eyes.

[0208] (S7: Refractive power measurement) Next, the main control unit 211 performs refractometer measurements simultaneously for both eyes.

[0209] Specifically, the main control unit 211 turns on the reflector measurement light sources 61L and 61R if they are turned off. Also, the main control unit 211 starts the rotation of the rotary prism 66 if it has stopped rotating. When measuring in the far-view state, the fixation target is at the position corresponding to the far point obtained in step S5, as described above. When measuring in the near-view state, the fixation target is at a predetermined fixed position.

[0210] The main control unit 211 acquires a ring image by controlling the refractometer projection systems 6L and 6R and the refractometer light receiving system 7, similar to the preliminary measurement in step S5. That is, the refractometer optical system projects measurement pattern light beams for the left eye and measurement pattern light beams for the right eye so that the focal position is at a position corresponding to the intermediate power between the refractive power of the left eye EL and the refractive power of the right eye ER, thereby acquiring a ring image for each eye. For each eye, the main control unit 211 causes the eye refractive power calculation unit 221 to calculate the spherical power, astigmatism power, and astigmatism axis angle from the analysis results of the ring image and the amount of movement of the focusing lens 74. The calculated spherical power, astigmatism power, and astigmatism axis angle are stored in the memory unit 212.

[0211] Specifically, the refrometric 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 also projects a measurement pattern light beam onto the right eye ER along the measurement optical axis OR, and receives the reflected light of the measurement pattern light beam from the left eye EL and the reflected light of the measurement pattern light beam from the right eye ER. The refractive power calculation unit 221 calculates the refractive power of the left eye EL based on the reception result of the reflected 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 reception result of the reflected light of the measurement pattern light beam from the right eye ER.

[0212] In some embodiments, step S7 is performed simultaneously with the acquisition of anterior segment images in step S3 and the corneal topography analysis in step S4.

[0213] (S8: Adjust the optical axis of the OCT optical system to match the measurement optical axis of one eye.) Next, the main control unit 211 adjusts the optical axis of the OCT optical system 8 to match the measurement optical axis of one eye. The main control unit 211 can adjust the optical axis of the OCT optical system 8 to match the measurement optical axis of one eye as shown in Figures 3, 4, or 11A to 11C.

[0214] For example, the main control unit 211 moves the optical axis of the OCT optical system 8 in the Y direction as shown in Figure 11B, and moves the optical axis of the OCT optical system 8 in the X direction as shown in Figure 11A, based on the interpupillary distance calculated from the pupil positions of both eyes, which are identified in the alignment process in step S2, as described later.

[0215] In some embodiments, the alignment in step S2 is performed before the OCT measurement in step S9.

[0216] (S9: OCT measurement) Next, the main control unit 211 controls the OCT optical system 8 to perform OCT measurement.

[0217] For example, the main control unit 211 causes the eye to be measured to present a fixation target for OCT measurement, controls the OCT optical system 8 to perform a preliminary OCT measurement, and acquires an adjustment tomographic image to adjust the reference position of the measurement range in the depth direction. Specifically, the main control unit 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 scans a predetermined part of the eye (e.g., the fundus) with the deflected measurement light LS. The detection result of the interference light LC obtained by scanning 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 eye from the obtained interference signal.

[0218] Next, the main control unit 211 adjusts the reference position of the measurement range in the depth direction (Z direction). For example, the main control unit 211 causes the data processing unit 223 to identify a predetermined area (e.g., the sclera) in the obtained tomographic image, and sets a position that is a predetermined distance away in the depth direction from the position of the identified predetermined area as the reference position of the measurement range. Alternatively, a predetermined position that is set in advance so that the optical path lengths of the measurement light LS and the reference light LR are approximately the same may be set as the reference position of the measurement range.

[0219] Next, the main control unit 211 performs focus adjustment control and polarization adjustment control. For example, after moving the focusing lens 87 by a predetermined distance, the main control unit 211 controls the OCT unit 100 to perform OCT measurement.

[0220] The main control unit 211 causes the data processing unit 223 to determine the focus state of the measurement light LS based on the detection results of interference light obtained by OCT measurement. For example, the data processing unit 223 calculates a predetermined evaluation value related to the image quality of the OCT image and determines whether the calculated evaluation value is below a threshold. In some embodiments, focus adjustment is continued until the calculated evaluation value is below a threshold. That is, when the evaluation value is below a threshold, it is determined that the focus state of the measurement light LS is appropriate, and focus adjustment is continued until it is determined that the focus state of the measurement light LS is appropriate.

[0221] In some embodiments, the main control unit 211 performs the above-described iterative OCT measurement to acquire interference signals while monitoring the strength of the successively acquired interference signals (interference intensity, interference sensitivity). Furthermore, while performing this monitoring process, the main control unit 211 moves the focusing lens 87 to search for a position of the focusing lens 87 that maximizes the interference intensity. Through such focus adjustment, the focusing lens 87 can be guided to a position where the interference intensity is optimized.

[0222] Furthermore, the data processing unit 223 analyzes the detection results of interference light obtained by OCT measurement and determines the polarization state of at least one of the measurement light LS and the reference light LR.

[0223] For example, the main control unit 211 performs iterative OCT measurements 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 amount of the reference light LR. The data processing unit 223 analyzes the detection results of the interference light LC repeatedly acquired by the OCT measurement to calculate a predetermined evaluation value for the image quality of the OCT image and determines whether the calculated evaluation value is below a threshold. This threshold is set in advance. Polarization adjustment continues until the calculated evaluation value is below the threshold. That is, when the evaluation value is below the threshold, it is determined that the polarization state of the measurement light LS is appropriate, and polarization adjustment continues until it is determined that the polarization state of the measurement light LS is appropriate.

[0224] In some embodiments, the main control unit 211 can also monitor interference intensity during polarization adjustment.

[0225] Once depth position adjustment, focus adjustment, and polarization adjustment are complete, the main control unit 211 controls the optical scanner 88 to scan a predetermined area of ​​the fundus of the eye being measured with the measurement light LS. For example, the detection signal obtained from 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.

[0226] The main control unit 211 controls the data processing unit 223 to calculate the axial length of the eye, based on the obtained detection signal or tomographic image, the distance between the position corresponding to the corneal apex and the position corresponding to the RPE layer. The data processing unit 223 can calculate intraocular parameters other than the axial length of the eye. For example, the main control unit 211 controls the OCT optical system 8 to scan the fundus and cornea (anterior segment) sequentially or simultaneously. The main control unit 223 controls the data processing unit 223 to calculate the axial length of the eye, based on the detection signal or tomographic image obtained by scanning the cornea and the detection signal or tomographic image obtained by scanning the fundus, the distance between the position corresponding to the corneal apex and the position corresponding to the RPE layer. Such a method for calculating the axial length of the eye is disclosed, for example, in Japanese Patent Application Publication No. 2020-044027.

[0227] In some embodiments, when OCT measurements are performed on one eye at a time, before performing an OCT measurement using the measurement light LS on one of the left eye (EL) and the right eye (ER), the main control unit 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 eye (EL) and the right eye (ER). That is, noting that the optical path length of the reference optical path, which is one of the measurement environments for OCT measurements, can be related to the axial length and refractive power of the eye being measured, and that the optical path lengths of the reference optical path are often almost the same for the left and right eyes, the optical path length of the reference optical path for the next eye being measured is determined from the optical path length of the first eye being measured, based on the axial length and refractive power of the eye being measured next, and the optical path length is adjusted to the determined length. This makes it possible to significantly reduce the time required for OCT measurements on both eyes.

[0228] (S10: Is the measurement of both eyes complete?) Next, the main control unit 211 determines whether or not the measurement of both eyes has been completed. If it is determined that the measurement of both eyes has been completed (S10:Y), the operation of the ophthalmic device 1 ends (end). If it is determined that the measurement of both eyes has not been completed (S10:N), the operation of the ophthalmic device 1 proceeds to step S8.

[0229] In some embodiments, the process from steps S1 to S10 is performed for one of the conditions, either for distance viewing or near viewing, and then the process from steps S1 to S10 is performed for the other condition, thereby performing the inspection in both the distance viewing and near viewing states. In some embodiments, the refractive power measurement from steps S1 to S7 is performed for one of the conditions, either for distance viewing or near viewing, and then the refractive power measurement from steps S1 to S7 is performed for the other condition, either for distance viewing or near viewing.

[0230] Step S2 in Figure 14 is performed as shown in Figure 15.

[0231] (S21: Identify the position of the pupils in both eyes) First, the main control unit 211 controls the anterior segment cameras 15LA, 15RA, 15LB, and 15RB to identify characteristic positions of both eyes from the captured images. In this embodiment, the pupil position is identified as the characteristic position.

[0232] Specifically, the main control unit 211 controls the anterior segment cameras 15LA and 15LB to capture images of the left eye EL from different directions substantially simultaneously, thereby acquiring two images (anterior segment images). Similarly, the main control unit 211 controls the anterior segment cameras 15RA and 15RB to capture images of the right eye ER from different directions substantially simultaneously, thereby acquiring two images. In some embodiments, the two images of the left eye EL and the two images of the right eye ER are captured substantially simultaneously.

[0233] The process for determining the pupil position of the left eye (EL) is the same as the process for determining the pupil position of the right eye (ER). Below, we will mainly explain the process for determining the pupil position of the left eye (EL).

[0234] The main control unit 211 controls the data processing unit 223, which functions as a feature location identification unit, to analyze the two images obtained by the anterior segment cameras 15LA and 15LB, and to identify the pupil position (pupillary center position or pupillary centroid position) of the left eye EL under examination.

[0235] In this case, the data processing unit 223 identifies the image region corresponding to the pupil (pupil region) for each captured image based on the distribution of pixel values ​​(such as brightness values). Generally, the pupil is drawn with lower brightness than other parts, so the pupil region can be identified by searching for low-brightness image regions. At this time, the pupil region may also be identified by considering the shape of the pupil. That is, the system can be configured to identify the pupil region by searching for a roughly circular, low-brightness image region.

[0236] Next, the data processing unit 223 determines the center position of the identified pupil region. As the pupil is approximately circular as described above, the contour of the pupil region can be identified, the center position of this contour (approximately a circle or ellipse) can be identified, and this can be set as the pupil center position. Alternatively, the centroid of the pupil region can be determined, and this centroid position can be set as the pupil centroid position.

[0237] The data processing unit 223 can sequentially identify the pupil position in the images captured sequentially by the anterior segment cameras 15LA and 15LB. Alternatively, the data processing unit 223 may identify the pupil position at any number of frames (one or more) in the images captured sequentially by the anterior segment cameras 15LA and 15LB.

[0238] Next, the data processing unit 223, acting as a 3D position calculation unit, identifies the 3D position of the feature location as the 3D position of the eye under examination based on the positions of the anterior segment cameras 15LA and 15LB and the identified pupil position. For example, as disclosed in Japanese Patent Application Publication No. 2013-248376, the data processing unit 223 calculates the 3D position of the eye under examination by applying a known trigonometric method to the positions of the two anterior segment cameras 15LA and 15LB (which are known) and the pupil position in the two captured images.

[0239] The pupil position of the right eye under examination (ER) can also be determined using the same process as described above.

[0240] (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 measuring optical system 300, the adjustment of the interpupillary distance using the prism mirror PR shown in Figure 3, and the position of the fixation targets presented by the fixation projection systems 4L and 4R.

[0241] Specifically, the interpupillary distance is determined from the pupil positions of both eyes identified in step S21. For example, the main control unit 211 adjusts the moving mechanism 200, the moving mechanism 310, and at least one of the fixation projection systems 4L, 4R so that the pupil positions of both eyes identified in step S21 are as close as possible (approximately coincide) with the known measurement optical axes OL, OR, respectively. The main control unit 211 can change the relative position of the measurement optical system 300 with respect to the left eye EL and the right eye ER by controlling the moving mechanism 200. The main control unit 211 can change the distance between the measurement optical axes OL and OR by moving the prism mirror PR by controlling the moving mechanism 310. The main control unit 211 can change the fixation positions (positions of the fixation target) of the left eye EL and the right eye ER, respectively, by controlling the fixation projection systems 4L, 4R.

[0242] As a result, the positions of the left eye under examination 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.

[0243] In some embodiments, the main control unit 211 determines, based on the pupil positions of both eyes identified in step S21, whether the alignment direction of the left eye EL and the right eye ER is parallel to the X direction (i.e., whether the heights of the two eyes are misaligned). In this case, the main control unit 211 can change at least one of the deflection directions of the prism mirrors PR (deflection surfaces M1, M2) and the dichroic mirrors ML, MR by controlling the movement mechanisms 310, 320 based on the pupil positions of both eyes identified in step S21.

[0244] In some embodiments, when it is determined that the alignment direction of the left eye EL and the right eye ER is not parallel to the X direction, the main control unit 211 can control the display unit 270 to prompt the subject to tilt their head. The main control unit 211 may also prompt the subject to tilt their head by outputting sound.

[0245] (S23: Obtain images of the anterior segment of both eyes) Next, the main control unit 211 turns on the XY alignment light source 21 and then controls the anterior segment cameras 15LA, 15RA, 15LB, and 15RB again to acquire anterior segment images of both eyes in which XY bright spot images based on the reflected light from the XY alignment light source 21 are depicted.

[0246] (S24: XY bright spot image detected?) Next, the main control unit 211 controls the data processing unit 223 to detect XY bright spot images in the anterior segment images of both eyes acquired in step S23.

[0247] For example, the data processing unit 223 detects whether XY bright spot images are depicted in each of the two anterior segment images of the left eye EL and the two anterior segment images of the right eye ER, based on the pixel values. When the data processing unit 223 detects that XY bright spot images are depicted in all four anterior segment images (S24:Y), the operation of the ophthalmic device 1 proceeds to step S25. When the data processing unit 223 detects that XY bright spot images are not depicted in at least one of the four anterior segment images (S24:N), the operation of the ophthalmic device 1 proceeds to step S22.

[0248] (S25: Identify the positions of the XY bright spot images in both eyes) When XY bright spot images are detected in the anterior segment images of both eyes in step S24 (S24:Y), the main control unit 211 controls the data processing unit 223 to determine the positions of the XY bright spot images of both eyes detected in step S24. In step S25, the positions of the XY bright spot images of both eyes are determined by the same determination process as in step S21. That is, the positions of the XY bright spot images of both eyes, determined in step S25, are determined instead of the pupil positions of both eyes determined in step S21.

[0249] (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 prism mirror PR shown in Figure 3, and the position of the fixation targets presented by the fixation projection systems 4L and 4R.

[0250] In step S26, the measurement optical axis is adjusted, similar to step S22.

[0251] (S27: Obtain images of the anterior segment of both eyes) Next, the main control unit 211 controls the anterior segment cameras 15LA, 15RA, 15LB, and 15RB to acquire anterior segment images of both eyes.

[0252] (S28: Identify the positions of the XY bright spot images in both eyes) Next, the main control unit 211 controls the data processing unit 223, similar to step S25, to determine the positions of the XY bright spot images of both eyes from the anterior segment images of both eyes acquired in step S27.

[0253] (S29: Alignment complete?) Next, the main control unit 211 determines whether the positions of the XY bright spot images of both eyes, which were identified in step S28, are within a predetermined alignment completion range.

[0254] 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 process in step S2 of Figure 14 is completed (end). When it is determined that the positions of at least one of the XY bright spot images of both eyes are not within the predetermined alignment completion range (S29:N), the operation of the ophthalmic device 1 proceeds to step S26.

[0255] As described above, in step S2 of Figure 14, the main control unit 211 changes the relative position of the OCT optical system 8 with respect to the left eye EL and the right eye ER based on two or more images obtained by two or more anterior segment cameras, and also changes the orientation of the measurement optical axis OL, the orientation of the measurement optical axis OR, and 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 eye EL and the measurement optical axis OR coincides with the visual axis of the right eye ER.

[0256] As described above, according to the first embodiment, the optical axis of the OCT optical system 8 for performing OCT measurement via an objective lens through which the measurement optical axes OL and OR, which are arranged to be spaced apart from each other, pass is adjusted to substantially coincide with either the measurement optical axis OL or OR. This allows for sequential OCT measurement of both eyes with both eyes open. This makes it possible to provide an ophthalmic device that can measure the characteristics of both eyes with high precision at low cost and in a small space. In particular, it is possible to miniaturize and reduce the cost of the optical system of an ophthalmic device that can perform OCT measurement on both eyes. Furthermore, by performing refractive power measurement via an objective lens through which the measurement optical axes OL and OR pass, it is also possible to perform refractive power measurement of both eyes simultaneously with both eyes open.

[0257] [Second Embodiment] In the first embodiment, a case was described in which fixation projection systems 4L and 4R are provided in the transmission direction of the dichroic mirrors ML and MR, but the configuration of the ophthalmic apparatus according to the embodiment is not limited thereto. For example, the measuring optical system may include a fixation projection system common to both eyes.

[0258] Hereinafter, the ophthalmic apparatus according to the second embodiment will be described focusing on the differences from the ophthalmic apparatus 1 according to the first embodiment.

[0259] FIGS. 16 and 17 show a configuration example of the optical system of the ophthalmic apparatus according to the second embodiment. FIG. 16 schematically shows the configuration of the optical system of the ophthalmic apparatus according to the second embodiment as viewed from above, similar to FIG. 1. FIG. 17 shows a block diagram of a configuration example of the measurement optical system 300a in FIG. 16.

[0260] The differences in the configuration of the optical system of the ophthalmic apparatus 1a according to the second embodiment from the configuration of the optical system of the ophthalmic apparatus 1 according to the first embodiment are that a reflection mirror ML1 is provided instead of the dichroic mirror ML, a reflection 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.

[0261] The reflection mirror ML1 deflects the measurement optical axis OL deflected by the deflection surface M1 of the prism mirror PR toward the left eye to be examined EL. The reflection mirror MR1 deflects the measurement optical axis OR deflected by the deflection surface M2 of the prism mirror PR toward the right eye to be examined ER.

[0262] As shown in FIG. 17, the measurement optical system 300a includes a keratometry system 3, a fixation projection system 4, an anterior eye observation system 5, refraction measurement projection systems 6L and 6R, a refraction measurement light receiving system 7, and an OCT optical system 8.

[0263] Similar to 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.

[0264] [[ID=​​​The interpupillary distance adjustment unit, similar to the first embodiment, changes the distance in the X direction between the measurement optical axes OL and OR by moving the prism mirror PR having deflection surfaces M1 and M2 along the measurement optical axis OL or measurement optical axis OR (Z direction, optical axis of the measurement optical system 300). As a result, as shown in Figure 18, the position of the optical axis deflected by the reflective mirrors ML1 and MR2 changes, and the measurement optical axis OL becomes the measurement optical axis OL', and the measurement optical axis OR becomes the measurement optical axis OR'. Consequently, 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.

[0266] In some embodiments, the interpupillary distance is changed by moving the prism mirror PR in the X direction as shown in Figure 18.

[0267] In some embodiments, the prism mirror PR is moved by a moving mechanism (not shown) under the control of a control unit described later. In this case, the functions of the interpupillary distance adjustment unit are realized by the control unit and the moving mechanism (not shown). In some embodiments, the prism mirror PR is moved manually by a moving mechanism (not shown). In this case, the functions of the interpupillary distance adjustment unit are realized by the moving mechanism (not shown).

[0268] Figure 19 shows an explanatory diagram of an example of the operation of the convergence angle adjustment unit in the ophthalmic device 1a according to the second embodiment. In Figure 19, the same reference numerals are used for parts that are the same as those in Figure 4 or Figure 16, and their descriptions are omitted as appropriate.

[0269] Similar to the first embodiment, 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 reflection mirrors ML1 and MR1.

[0270] For example, the deflection surface of the reflective mirror ML1 is configured to be rotatable around a pivot axis extending in the Y-axis direction. For example, the deflection surface of the reflective mirror MR1 is configured to be rotatable around a pivot axis extending in the Y-axis direction. As a result, as shown in Figure 19, the measurement optical axis OL deflected by the reflective mirror ML1 becomes the measurement optical axis OL', and the measurement optical axis OR becomes the measurement optical axis OR', thereby changing the convergence angle.

[0271] In some embodiments, the reflective 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 functions of the convergence angle adjustment unit are realized by the control unit and the moving mechanism (not shown). In some embodiments, the reflective mirrors ML1 and MR1 are rotated manually by a moving mechanism (rotating mechanism) not shown. In this case, the functions of the convergence angle adjustment unit are realized by the moving mechanism (not shown).

[0272] Figure 20 shows an example configuration of the measurement optical system 300a according to the second embodiment. Similar to Figure 6, Figure 20 schematically represents an example configuration of the measurement optical system 300a viewed from the side (X direction). In Figure 20, the same reference numerals are used for parts that are the same as in Figure 6 or Figure 16, and explanations are omitted as appropriate.

[0273] The difference between the configuration of the measurement optical system 300a and the configuration of the measurement optical system 300 is that a dichroic mirror 83, a reflective mirror 84, and a fixation projection system 4 are provided between the relay lens 82 and the relay lens 85, and the optical path of the fixation projection system 4 is coaxially coupled to the optical path of the OCT optical system 8 by the dichroic mirror 83.

[0274] 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 positioned in the transmission direction of the dichroic mirror 83, and the OCT optical system 8 is positioned in the reflection direction of the dichroic mirror 83. Specifically, the dichroic mirror 83 is positioned between the relay lens 82 and the fixation projection system 4, and the reflection mirror 84 is positioned between the dichroic mirror 83 and the OCT optical system 8.

[0275] The fixation projection system 4 projects a fixation beam onto the fundus ELf of the left eye EL or the fundus ERf of the right eye ER, thereby presenting a fixation target to the left eye EL or the right eye ER. The fixation projection system 4 includes a fixation unit 40 and relay lenses 43 and 44. The fixation unit 40 includes a liquid crystal panel 41 and a relay lens 42. The liquid crystal panel 41 receives control from the control unit and displays a pattern representing the fixation target. By changing the display position of the pattern on the screen of the liquid crystal panel 41, the fixation position of the left eye EL or the right eye ER can be changed. The fixation unit 40 is also movable in the optical axis direction under control from the control unit.

[0276] Light from the liquid crystal panel 41 passes through relay lenses 42, 43, and 44, then through the dichroic mirror 83, and is projected onto the eye under examination via the same path as the measurement light LS from the OCT optical system 8.

[0277] In some embodiments, the fixation unit 40 is movable in the optical axis direction independently of the relay lenses 43, 44.

[0278] Furthermore, in the second embodiment, the optical axis of the OCT optical system 8 can be adjusted in the same way as in the first embodiment. For example, by using a reflective mirror 84 as the deflection member DF1 and a dichroic mirror 83 as the deflection member DF2, the optical axis of the OCT optical system 8 can be adjusted as shown in the first adjustment example in Figure 11A. Also, in the second embodiment, the optical axis of the OCT optical system 8 can be adjusted as shown in the second adjustment example in Figure 11B or the third adjustment example in Figure 11C. In the fourth adjustment example, in which the deflection direction of the optical axis of the OCT optical system 8 is changed by optical members in the path of the measurement light, examples of optical members that can be used include the reflective mirror 81, dichroic mirror 52, dichroic mirror 83, reflective mirror 84, and reflective mirrors not shown in Figure 20.

[0279] The fixation projection system 4 is an example of the "fixation optical system" according to the embodiment. The dichroic mirror 83 is an example of the "optical path coupling member" according to the embodiment. The deflection surface M1 of the prism mirror PR is an example of the "first deflection member" according to the embodiment. The reflection mirror ML1 is an example of the "first reflection member" according to the embodiment. The deflection surface M2 of the prism mirror PR is an example of the "second deflection member" according to the embodiment. The reflection mirror MR1 is an example of the "second reflection member" according to the embodiment. The convergence angle adjustment unit is an example of the "first adjustment unit" according to the embodiment. The movement mechanism that rotates the deflection surface M1 of the prism mirror PR or the reflection mirror RML, the deflection surface M2 of the prism mirror PR or the reflection mirror RMR, the deflection surface of the reflection mirror ML1, and the deflection surface of the reflection mirror MR1 is an example of the "second adjustment unit" according to the embodiment.

[0280] FIG. 21 shows a functional configuration example of the processing system of the ophthalmic device 1a according to the second embodiment. FIG. 21 shows an example of a functional block diagram of the processing system of the ophthalmic device 1a. In FIG. 21, the same parts as those in FIG. 12 or FIG. 20 are denoted by the same reference numerals, and the description thereof will be omitted as appropriate.

[0281] The differences between the configuration of the processing system of the ophthalmic device 1a and the configuration of the processing system of the ophthalmic device 1 shown in FIG. 12 are that the fixation projection system 4 is provided instead of the fixation projection systems 4L and 4R, and the processing unit 9a is provided instead of the processing unit 9.

[0282] The difference between the configuration of the processing unit 9a and the configuration of the processing unit 9 shown in FIG. 12 is that the 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 it performs control on the fixation projection system 4 instead of the control on 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 processes for executing control on the fixation projection systems 4L and 4R.

[0283] The operation of the ophthalmic device 1a according to the second embodiment is substantially the same as the operation of the ophthalmic device 1 according to the first embodiment shown in Figures 14 and 15, except for the control of the fixation projection system 4.

[0284] In the second embodiment, the same fixation target is presented to both eyes during refractometry, keratometry, and OCT measurement. That is, with both eyes open and the same fixation target presented to both eyes, refractometry and keratometry can be performed simultaneously on both eyes. Furthermore, with both eyes open and the same fixation target presented to both eyes, OCT measurements can be performed sequentially on one eye at a time.

[0285] Specifically, instead of the main control unit 211 controlling the fixation projection system 4L and 4R to independently present fixation targets to the left eye EL and the right eye ER, the main control unit 211a controls the fixation projection system 4 to present the same fixation target to the left eye EL and the right eye ER.

[0286] For example, in step S7 of Figure 14, when the examination is performed in the distance viewing state, the main control unit 211a presents the fixation target to both eyes from a position corresponding to the more positive (distance viewing) provisional spherical power S and provisional astigmatism power C (or equivalent spherical power) of the left eye EL and the right eye ER, which were determined in step S5 of Figure 14.

[0287] For example, in step S7 of Figure 14, when the examination is performed in a near-vision state, the main control unit 211a presents the fixation target to both eyes from the same position as when the examination is performed in a far-vision state. In some embodiments, if the subject is monovision, the main control unit 211a presents the fixation target to both eyes from a position corresponding to the more negative (near-vision) provisional spherical power S and provisional astigmatism power C (or equivalent spherical power) of the provisional spherical power S and provisional astigmatism power C (or equivalent spherical power) of the left eye EL and the right eye ER, which were determined in step S5 of Figure 14. At this time, the main control unit 211a can adjust the convergence angle by controlling the reflective mirrors ML1 and ML2 as needed.

[0288] Furthermore, similar to step S22 in Figure 15, the main control unit 211a can determine whether the alignment direction of the left eye EL and the right eye ER is parallel to the X direction (i.e., whether the heights of the two eyes are misaligned) based on the pupil positions of both eyes identified in step S21. In this case, the main control unit 211a, as a second adjustment unit, can adjust the alignment direction of the measurement optical axis OL and the measurement optical axis OR by changing the deflection direction of the reflective mirror ML1, the deflection direction of the reflective mirror MR1, the orientation of the reflective surface of the prism mirror PR or deflection surface M1, and the orientation of the reflective surface of the prism mirror PR or deflection surface M2, based on the pupil positions of both eyes identified in step S21.

[0289] In some embodiments, in the configuration according to the second embodiment, a holopter may be provided in front of both eyes, or trial lenses may be placed.

[0290] As described above, the second embodiment, like the first embodiment, provides an ophthalmic device that can measure the characteristics of both eyes with high precision at low cost and in a space-saving manner. In particular, it is possible to miniaturize and reduce the cost of the optical system of an ophthalmic device that can perform OCT measurements on both eyes. Furthermore, by performing refractive power measurement through objective lenses through which the measurement optical axes OL and OR pass, it is also possible to perform refractive power measurement simultaneously with both eyes open.

[0291] [Third Embodiment] In the first embodiment, a case was described in which fixation projection systems 4L and 4R are provided in the transmission direction of the dichroic mirrors ML and MR, but the configuration of the ophthalmic device according to the embodiment is not limited thereto. For example, a common target presentation unit for both eyes may be arranged in the transmission direction of the dichroic mirrors ML and MR.

[0292] The following describes the ophthalmic device according to the third embodiment, focusing on the differences from the ophthalmic device 1 according to the first embodiment.

[0293] Figure 22 shows an example of the optical system configuration of the ophthalmic device according to the third embodiment. Similar to Figure 1, Figure 22 schematically represents the optical system configuration of the ophthalmic device according to the third embodiment as viewed from above.

[0294] The difference between the optical system configuration of the ophthalmic device 1b according to the third embodiment and the optical system configuration of the ophthalmic device 1 according to the first embodiment is that a target presentation unit 400 is provided in place of the fixation projection systems 4L and 4R.

[0295] The target presentation unit 400 includes a target chart. For example, the target chart is a transmissive chart on which fixation targets are displayed, and is placed between the illumination light source and the eye under examination. In some embodiments, the target chart is a transmissive film on which fixation targets are printed. Examples of fixation targets include landscape charts and dot targets.

[0296] The control unit turns on the illumination light source when performing a refraction measurement, 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 eye EL and the right eye ER.

[0297] The deflection surface M1 of the prism mirror PR is an example of the "first deflection member" according to the embodiment. The dichroic mirror ML is an example of the "first optical path coupling member" according to the embodiment. The deflection surface M2 of the prism mirror PR is an example of the "second deflection member" according to the embodiment. The dichroic mirror MR is an example of the "second optical path coupling member" according to the embodiment.

[0298] Figure 23 shows an example of the functional configuration of the processing system of the ophthalmic device 1b according to the third embodiment. Figure 23 shows an example of a functional block diagram of the processing system of the ophthalmic device 1b. In Figure 23, the same reference numerals are used for parts that are the same as those in Figure 12 or Figure 22, and their descriptions are omitted as appropriate.

[0299] The difference between the processing system configuration of ophthalmic device 1b and the processing system configuration of ophthalmic device 1 shown in Figure 12 is that the fixation projection systems 4L and 4R are omitted, and a processing unit 9b is provided in place of processing unit 9.

[0300] The difference between the configuration of the processing unit 9b and the configuration of the processing unit 9 shown in Figure 12 is that the control unit 210b is replaced by a control unit 210b. 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 program as the storage unit 212, except that it stores the processing that executes the control of the fixation projection systems 4L and 4R.

[0301] The operation of the ophthalmic device 1b according to the third embodiment is substantially the same as the operation of the ophthalmic device 1 according to the first embodiment shown in Figures 14 and 15, except that control of the fixation projection systems 4L and 4R is omitted.

[0302] In the third embodiment, the same fixation target is presented to both eyes during refractometry, keratometry, and OCT measurement. That is, with both eyes open and the same fixation target presented to both eyes, refractometry and keratometry can be performed simultaneously on both eyes. Furthermore, with both eyes open and the same fixation target presented to both eyes, OCT measurements can be performed sequentially on one eye at a time.

[0303] In some embodiments, the target presentation unit 400 presents the target based on the examiner's operation. In some embodiments, the target presentation unit 400 presents the target under control from the main control unit 211b. In this case, the main control unit 211b controls the target presentation unit 400 in the same manner as the control of the fixation projection system 4 according to the second embodiment.

[0304] In some embodiments, in the configuration according to the third embodiment, a holopter may be provided in front of both eyes, or trial lenses may be placed.

[0305] As described above, the third embodiment, like the first embodiment, provides an ophthalmic device that can measure the characteristics of both eyes with high precision at low cost and in a space-saving manner. In particular, it is possible to miniaturize and reduce the cost of the optical system of an ophthalmic device that can perform OCT measurements on both eyes. Furthermore, by performing refractive power measurement through objective lenses through which the measurement optical axes OL and OR pass, it is also possible to perform refractive power measurement simultaneously with both eyes open.

[0306] [Effect] An ophthalmic device according to an embodiment will be described.

[0307] The first embodiment is an ophthalmic device (1, 1a, 1b) including an objective lens (51), an OCT optical system (8), an optical axis adjustment unit (a member and mechanism for adjusting the optical axis of the OCT optical system 8 as shown in any of Figures 11A to 11C), a control unit (210, 210a, 210b, main control units 211, 211a, 211b), and an intraocular parameter calculation unit (data processing unit 223). A first measurement optical axis (measurement optical axis OL) and a second measurement optical axis (measurement optical axis OR), which are spaced apart from each other, pass through the objective lens. The OCT optical system splits light (L0) from a light source (light source unit 101) into measurement light (LS) and reference light (LR). The measurement light is projected via an objective lens onto the left eye (EL) positioned on the first measurement optical axis or the right eye (ER) positioned on the second measurement optical axis, and interference light (LC) is detected between the return light of the measurement light from the left or right eye and the reference light that has passed through the reference optical path. The optical axis adjustment unit adjusts the optical axis of the OCT optical system. The control unit controls the optical axis adjustment unit so that it substantially coincides with either the first measurement optical axis or the second measurement optical axis. The intraocular parameter calculation unit calculates the intraocular parameters (e.g., axial length) of the left eye based on the detection result of interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the first measurement optical axis, and calculates the intraocular parameters (e.g., axial length) of the right eye based on the detection result of interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the second measurement optical axis.

[0308] In this embodiment, the optical axis of the OCT optical system for performing OCT measurement via an objective lens through which the first and second measurement optical axes, which are arranged spaced apart from each other, pass is adjusted to substantially coincide with either the first or second measurement optical axis. This allows for sequential OCT measurement of both eyes with both eyes open. Therefore, it becomes possible to provide an ophthalmic device that can measure the characteristics of both eyes with high precision at low cost and in a space-saving manner.

[0309] In a second embodiment, before performing an OCT measurement using the measurement light on one of the left and right eyes under examination, the control unit controls the OCT optical system to adjust the optical path length of the reference light path based on the axial length and refractive power of the other eye under examination.

[0310] In this configuration, the measurement environment can be estimated from the measurement environment of the other eye before performing OCT measurement on one eye, thereby shortening the time required for OCT measurement.

[0311] A third aspect of the embodiment includes, in the first or second embodiment, a first fixation optical system (fixation projection system 4L) for projecting a first fixation beam, a first deflection member (prism mirror PR or reflective mirror RML) for deflecting the optical path of the measurement light, a first optical path coupling member (dichroic mirror ML) for optically coupling the optical path of the measurement light deflected by the first deflection member to the optical path of the first fixation beam, a second fixation optical system (fixation projection system 4R) for projecting a second fixation beam, a second deflection member (prism mirror PR or reflective mirror RMR) for deflecting the optical path of the measurement light, and a second optical path coupling member (dichroic mirror MR) for optically coupling the optical path of the measurement light deflected by the second deflection member to the optical path of the second fixation beam.

[0312] This configuration allows for OCT measurements to be performed with both eyes open, while independently presenting fixation targets to the left and right eyes under examination, using a simple setup.

[0313] A fourth aspect of the embodiment includes, in the first or second embodiment, a fixation optical system (4) that projects a fixation beam; an optical path coupling member (dichroic mirror 83) that optically couples the optical path of the fixation beam to the optical path of the measurement light and guides the fixation beam to the objective lens; a first deflection member (deflection surface M1 of prism mirror PR) that deflects the optical path of the measurement light; a first reflecting member (reflection mirror ML1) that deflects the optical path of the measurement light deflected by the first deflection member toward the left eye under examination; a second deflection member (deflection surface M2 of prism mirror PR) that deflects the optical path of the measurement light; and a second reflecting member (reflection mirror MR1) that deflects the optical path of the measurement light deflected by the second deflection member toward the right eye under examination.

[0314] This configuration allows for OCT measurements to be performed with both eyes open, while presenting the same fixation target to both eyes using a common fixation projection system.

[0315] A fifth aspect of the embodiment includes, in the first or second embodiment, a first deflection member (deflection surface M1 of a prism mirror PR) that deflects the optical path of the measurement light, a first optical path coupling member (dichroic mirror ML) that deflects the optical path of the measurement light deflected by the first deflection member toward the left eye under examination and transmits a first fixation beam from the transmission direction to guide it toward the left eye under examination, a second deflection member (deflection surface M2 of a prism mirror PR) that deflects the optical path of the measurement light deflected by the second deflection member toward the right eye under examination and transmits a second fixation beam from the transmission direction to guide it toward the right eye under examination.

[0316] According to this configuration, a common fixation projection system for both eyes is placed outside the device, allowing OCT measurements to be performed with both eyes open while presenting the same fixation target to both eyes.

[0317] A sixth aspect of the embodiment includes a first adjustment unit (convergence angle adjustment unit, a moving mechanism for rotating dichroic mirrors ML and MR) that changes the orientation of the first and second measuring optical axes by changing the orientation of the optical path coupling surface of the first optical path coupling member and the optical path coupling surface of the second optical path coupling member, in accordance with the third or fifth embodiment.

[0318] This configuration allows for OCT measurements to be performed with a simple setup, while adjusting the convergence angle, and with both eyes open.

[0319] A seventh aspect of the embodiment includes a second adjustment unit (height adjustment unit, deflection surface M1 of prism mirror PR or reflective mirror RML, deflection surface M2 of prism mirror PR or reflective mirror RMR, deflection surface (optical path coupling surface) of dichroic mirror ML, and deflection surface of dichroic mirror MR) that adjusts the alignment direction of the first and second measuring optical axes by changing the deflection direction of the first deflection member, the deflection direction of the second deflection member, the orientation of the optical path coupling surface of the first optical path coupling member, and the orientation of the optical path coupling surface of the second optical path coupling member, as in the third, fifth, or sixth aspect.

[0320] According to this embodiment, when the alignment directions of the first and second measuring optical axes are not parallel to the alignment directions of the left and right eyes being examined, the alignment directions of the first and second measuring optical axes can be aligned with the alignment directions of the left and right eyes being examined with a simple configuration.

[0321] An eighth aspect of the embodiment includes, in the fourth embodiment, a first adjustment unit (convergence angle adjustment unit, moving mechanism for rotating reflective mirrors ML1 and MR1) that changes the orientation of the first measuring optical axis and the orientation of the second measuring optical axis by changing the orientation of the reflective surface of the first reflecting member and the reflective surface of the second reflecting member.

[0322] This configuration allows for OCT measurements to be performed with a simple setup, while adjusting the convergence angle, and with both eyes open.

[0323] A ninth aspect of the embodiment includes a second adjustment unit (height adjustment unit, a moving mechanism for rotating the deflection surface M1 of the prism mirror PR or reflective mirror RML, the deflection surface M2 of the prism mirror PR or reflective mirror RMR, the deflection surface of the reflective mirror ML1, and the deflection surface of the reflective mirror MR1) which adjusts the alignment direction of the first measuring optical axis and the second measuring optical axis by changing the deflection direction of the first deflection member, the deflection direction of the second deflection member, the orientation of the reflective surface of the first reflecting member, and the orientation of the reflective surface of the second reflecting member, in accordance with the fourth or eighth aspect.

[0324] According to this embodiment, when the alignment directions of the first and second measuring optical axes are not parallel to the alignment directions of the left and right eyes being examined, the alignment directions of the first and second measuring optical axes can be aligned with the alignment directions of the left and right eyes being examined with a simple configuration.

[0325] A tenth embodiment of the embodiment includes a third adjustment unit (interpupillary distance adjustment unit, moving mechanism 310) that changes the distance between the first measuring optical axis and the second measuring optical axis by moving the first deflection member and the second deflection member along the first measuring optical axis or the second measuring optical axis, in any of the third to ninth embodiments.

[0326] According to this configuration, the first and second measurement optical axes can be aligned with the interpupillary distance of the subject with a simple setup.

[0327] An eleventh embodiment of the embodiment includes a prism mirror (PR) having a first deflection surface (deflection surface M1) as a first deflection member and a second deflection surface (deflection surface M2) as a second deflection member, in any of the third to tenth embodiments.

[0328] In this embodiment, with a simple configuration, the first and second measurement optical axes are directed into the left and right eyes under examination, respectively, and OCT measurements can be performed on both eyes with both eyes open.

[0329] In the twelfth embodiment, in any of the third to eleventh embodiments, the optical axis adjustment unit adjusts the optical axis of the OCT optical system by moving the first deflection member and the second deflection member along the first measurement optical axis or the second measurement optical axis.

[0330] According to this embodiment, the optical axis of the OCT optical system can be made to substantially coincide with the first measurement optical axis or the second measurement optical axis with a simple configuration and control.

[0331] A thirteenth embodiment of the embodiment includes, in any of the first to twelfth embodiments, two or more imaging units (anterior segment cameras 15LA, 15LB, 15RA, 15RB) that image the anterior segment of the left eye and the anterior segment of the right eye from different directions, and a movement mechanism (200) that moves at least the OCT optical system in three dimensions. Based on two or more images obtained by the two or more imaging units, the control unit changes the relative position of the OCT optical system with respect to the left eye and the right eye, and changes the orientation of the first measurement optical axis, the orientation of 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.

[0332] This configuration allows for the alignment of an ophthalmic device that enables OCT measurement with both eyes open, using a simple configuration and a wide dynamic range.

[0333] In the 14th embodiment, as in the 13th embodiment, the two or more imaging units include a first imaging unit (anterior segment camera 15LA) for imaging the anterior segment of the left eye under examination, a second imaging unit (anterior segment camera 15LR) for imaging the anterior segment of both the left and right eyes under examination, and a third imaging unit (anterior segment camera 15RA) for imaging the anterior segment of the right eye under examination.

[0334] This configuration reduces the number of anterior segment cameras, enabling bilateral OCT measurements with both eyes open at a lower cost.

[0335] In the 15th embodiment, in any of the 1st to 14th embodiments, the OCT optical system includes optical members (reflection mirror 81, dichroic mirror 52, dichroic mirror 83, reflection mirror 84, reflection mirror not shown) that deflect the optical axis of the OCT optical system. The optical axis adjustment unit adjusts the optical axis of the OCT optical system by changing the deflection direction of the optical axis deflected by the optical members based on the interpupillary distance of the subject.

[0336] According to this embodiment, the optical axis of the OCT optical system can be made to substantially coincide with the first measurement optical axis or the second measurement optical axis with a simple configuration and control.

[0337] In the sixteenth embodiment, in any of the first to fifteenth embodiments, the optical axis adjustment unit adjusts the optical axis of the OCT optical system by moving the position of the optical axis of the OCT optical system based on the interpupillary distance of the subject.

[0338] According to this embodiment, the optical axis of the OCT optical system can be made to substantially coincide with the first measurement optical axis or the second measurement optical axis with a simple configuration and control.

[0339] A 17th embodiment of the embodiment includes, in any of the 1st to 16th embodiments, a refractive power measurement optical system (refractive measurement projection system 6L, 6R, and refractive 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 along the first measurement optical axis via an objective lens and a second measurement pattern light beam onto the right eye along the second measurement optical axis, and receives the reflected light of the first measurement pattern light beam from the left eye and the reflected light of the second measurement pattern light beam from the right eye. The eye refractive power calculation unit calculates the refractive power of the left eye based on the reception result of the reflected light of the first measurement pattern light beam and calculates the refractive power of the right eye based on the reception result of the reflected light of the second measurement pattern light beam.

[0340] This configuration allows for simultaneous refractive power measurement of both eyes while both eyes are open.

[0341] In the 18th embodiment, as in the 17th embodiment, the refractive power measuring optical system projects a first measurement pattern beam and a second measurement pattern beam such that the focal position is at a position corresponding to the intermediate power between the refractive power of the left eye under examination and the refractive power of the right eye under examination.

[0342] According to this configuration, even when the refractive powers of the two eyes are different, refractive power measurements can be performed simultaneously for both eyes.

[0343] In the 19th embodiment, in the 17th or 18th embodiment, the refractive power measuring optical system includes a first projection system (refractive measurement projection system 6L) that projects a first measurement pattern light beam onto the left eye under examination, a second projection system (refractive measurement projection system 6R) that projects a second measurement pattern light beam onto the right eye under examination, and a light receiving system (refractive measurement light receiving system) that receives the reflected light of the first measurement pattern light beam and the reflected light of the second measurement pattern light beam.

[0344] This configuration makes it possible to perform highly accurate refractive power measurements for both eyes while minimizing the increase in size of the refractive power measurement optical system.

[0345] <Other> The embodiments described above are merely examples of how to carry out this invention. Anyone intending to carry out this invention may make any modifications, omissions, additions, etc., within the scope of the gist of this invention.

[0346] Furthermore, although the above embodiment described a case in which an ophthalmic device performs OCT on the fundus, the configuration of the ophthalmic device according to the embodiment is not limited to this. For example, the present invention can be applied to an ophthalmic device that performs OCT on both the fundus and the anterior segment of the eye.

[0347] Furthermore, in the above embodiment, the prism mirror PR folded the optical axis in the XZ plane, but the configuration of the embodiment is not limited to this. For example, the prism mirror PR may be configured to fold 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]

[0348] 1, 1a, 1b Ophthalmic equipment 2 XY Alignment System 3. Keratometry System 4, 4L, 4R fixation projection system 5 Anterior segment observation system 6L, 6R Ref Measurement Projection System 7. Ref measurement light receiving system 8 OCT optical system 9, 9a, 9b Processing Units 40, 40L, 40R Fixation Unit 41, 41L, 41R LCD panel 42, 43, 44, 42L, 43L, 44L, 42R, 43R, 44R Relay Lens 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 under examination ELf, ERf fundus ER right eye M1, M2 deflection surface ML, MR Dichroic Mirror ML1, MR1 Reflective Mirrors OL, OR measurement optical axis PR Prism Mirror

Claims

1. An objective lens through which a first measuring optical axis and a second measuring optical axis, which are arranged at a distance from each other, An OCT optical system that splits light from a light source into measurement light and reference light, projects the measurement light onto the left eye to be examined, positioned on the first measurement optical axis, or the right eye to be examined, positioned on the second measurement optical axis, via the objective lens, and detects interference light between the return light of the measurement light from the left eye or the right eye to be examined and the reference light that has passed through the reference optical path, An optical axis adjustment unit for adjusting the optical axis of the OCT optical system, A control unit controls the optical axis adjustment unit so that the optical axis of the OCT optical system substantially coincides with either the first measurement optical axis or the second measurement optical axis. An intraocular parameter calculation unit calculates intraocular parameters of the left eye under examination based on the detection results of the interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the first measurement optical axis, and calculates intraocular parameters of the right eye under examination based on the detection results of the interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the second measurement optical axis. Includes, Before performing an 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 light path based on the axial length and refractive power of the other eye, the left eye and the right eye, in an ophthalmic device.

2. A first fixation optical system that projects the first fixation beam, A first deflection member that deflects the optical path of the measurement light, A first optical path coupling member that optically couples the optical path of the measurement light deflected by the first deflection member to the optical path of the first fixed-view light beam, A second fixation optical system that projects a second fixation beam, A second deflecting member that deflects the optical path of the measurement light, A second optical path coupling member that optically couples the optical path of the measurement light deflected by the second deflection member to the optical path of the second fixation beam, including The ophthalmic device according to feature 1.

3. A fixation optical system that projects a fixation beam, An optical path coupling member that optically couples the optical path of the fixed-view light beam to the optical path of the measurement light and guides the fixed-view light beam to the objective lens, A first deflection member that deflects the optical path of the measurement light, A first reflecting member that deflects the optical path of the measurement light deflected by the first deflecting member toward the left eye under examination, A second deflecting member that deflects the optical path of the measurement light, A second reflecting member that deflects the optical path of the measurement light deflected by the second deflecting member toward the right eye under examination, including The ophthalmic device according to feature 1.

4. A first deflection member that 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 first deflection member toward the left eye to be examined, and also transmits the first fixation light beam from the transmission direction and guides it toward the left eye to be examined, A second deflecting member that deflects the optical path of the measurement light, A second optical path coupling member deflects the optical path of the measurement light deflected by the second deflection member toward the right eye under examination, and also transmits the second fixation light beam from the transmission direction to guide it toward the right eye under examination, including The ophthalmic device according to feature 1.

5. The system includes a first adjustment unit that changes the orientation of the first and second measuring optical axes by changing the orientation of the optical path coupling surface of the first optical path coupling member and the optical path coupling surface of the second optical path coupling member. The ophthalmic apparatus according to claim 2 or 4.

6. The system includes a second adjustment unit that adjusts the alignment direction of the first and second measuring optical axes by changing the deflection direction of the first deflection member, the deflection direction of the second deflection member, the orientation of the optical path coupling surface of the first optical path coupling member, and the orientation of the optical path coupling surface of the second optical path coupling member. The ophthalmic apparatus according to claim 2, claim 4, or claim 5.

7. The system includes a first adjustment unit that changes the orientation of the first measuring optical axis and the orientation of the second measuring optical axis by changing the orientation of the reflective surface of the first reflective member and the reflective surface of the second reflective member. The ophthalmic apparatus according to feature 3.

8. The system includes a second adjustment unit that adjusts the alignment direction of the first and second measuring optical axes by changing the deflection direction of the first deflection member, the deflection direction of the second deflection member, the orientation of the reflective surface of the first reflector member, and the orientation of the reflective surface of the second reflector member. The ophthalmic apparatus according to claim 3 or 7.

9. The system includes a third adjustment unit that changes the distance between the first and second measuring optical axes by moving the first and second deflection members along the first or second measuring optical axis. The ophthalmic apparatus according to any one of claims 2 to 8.

10. The prism mirror includes a first deflection surface as the first deflection member and a second deflection surface as the second deflection member. The ophthalmic apparatus according to any one of claims 2 to 9.

11. The optical axis adjustment unit adjusts the optical axis of the OCT optical system by moving the first deflection member and the second deflection member along the first measurement optical axis or the second measurement optical axis. An ophthalmic device according to any one of claims 2 to 10, characterized by the features described herein.

12. Two or more imaging units, including at least one imaging unit arranged to photograph the anterior segment of the left eye under examination from different directions, and at least one imaging unit arranged to photograph the anterior segment of the right eye under examination from different directions, A moving mechanism that moves the OCT optical system in three dimensions, Includes, 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 orientation of the first measurement optical axis, the orientation of the second measurement optical axis, and the distance between the first and second measurement optical axes so that the first measurement optical axis coincides with the visual axis of the left eye and the second measurement optical axis coincides with the visual axis of the right eye. An ophthalmic device according to any one of claims 1 to 11, characterized by the features described herein.

13. An objective lens through which a first measuring optical axis and a second measuring optical axis, which are arranged to be spaced apart from each other, An OCT optical system that splits light from a light source into measurement light and reference light, projects the measurement light onto the left eye to be examined, positioned on the first measurement optical axis, or the right eye to be examined, positioned on the second measurement optical axis, via the objective lens, and detects interference light between the return light of the measurement light from the left eye or the right eye to be examined and the reference light that has passed through the reference optical path, An optical axis adjustment unit for adjusting the optical axis of the OCT optical system, A control unit controls the optical axis adjustment unit so that the optical axis of the OCT optical system substantially coincides with either the first measurement optical axis or the second measurement optical axis. An intraocular parameter calculation unit calculates intraocular parameters of the left eye under examination based on the detection results of the interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the first measurement optical axis, and calculates intraocular parameters of the right eye under examination based on the detection results of the interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the second measurement optical axis. Two or more imaging units, including at least one imaging unit arranged to photograph the anterior segment of the left eye under examination from different directions, and at least one imaging unit arranged to photograph the anterior segment of the right eye under examination from different directions, A moving mechanism that moves the OCT optical system in three dimensions, Includes, The two or more imaging units described above are: A first imaging unit for photographing the anterior segment of the left eye under examination, A second imaging unit for photographing the anterior segment of the left eye and the anterior segment of the right eye, A third imaging unit for photographing the anterior segment of the right eye under examination, Includes, An ophthalmic device in which 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 changes the orientation of the first measuring optical axis, the orientation of the second measuring optical axis, and the distance between the first measuring optical axis and the second measuring optical axis so that the first measuring optical axis coincides with the visual axis of the left eye and the second measuring optical axis coincides with the visual axis of the right eye.

14. The OCT optical system includes an optical member that deflects the optical axis of the OCT optical system, The optical axis adjustment unit adjusts the optical axis of the OCT optical system by changing the direction of deflection of the optical axis, which is deflected by the optical element based on the interpupillary distance of the subject. An ophthalmic device according to any one of claims 1 to 13.

15. The optical axis adjustment unit adjusts the optical axis of the OCT optical system by moving the position of the optical axis of the OCT optical system based on the interpupillary distance of the subject. An ophthalmic device according to any one of claims 1 to 14.

16. A refractive power measuring optical system that projects a first measurement pattern beam onto the left eye under examination along the first measurement optical axis via the objective lens, and projects a second measurement pattern beam onto the right eye under examination along the second measurement optical axis, and receives the reflected light of the first measurement pattern beam from the left eye under examination and the reflected light of the second measurement pattern beam from the right eye under examination, An eye refractive power calculation unit calculates the refractive power of the left eye under examination based on the reception result of the reflected light of the first measurement pattern light beam, and calculates the refractive power of the right eye under examination based on the reception result of the reflected light of the second measurement pattern light beam, include An ophthalmic device according to any one of claims 1 to 15, characterized by the features described herein.

17. An objective lens through which a first measuring optical axis and a second measuring optical axis, which are arranged to be spaced apart from each other, An OCT optical system that splits light from a light source into measurement light and reference light, projects the measurement light onto the left eye to be examined, positioned on the first measurement optical axis, or the right eye to be examined, positioned on the second measurement optical axis, via the objective lens, and detects interference light between the return light of the measurement light from the left eye or the right eye to be examined and the reference light that has passed through the reference optical path, An optical axis adjustment unit for adjusting the optical axis of the OCT optical system, A control unit controls the optical axis adjustment unit so that the optical axis of the OCT optical system substantially coincides with either the first measurement optical axis or the second measurement optical axis. An intraocular parameter calculation unit calculates intraocular parameters of the left eye under examination based on the detection results of the interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the first measurement optical axis, and calculates intraocular parameters of the right eye under examination based on the detection results of the interference light obtained when the optical axis of the OCT optical system is adjusted to substantially coincide with the second measurement optical axis. A refractive power measuring optical system that projects a first measurement pattern beam onto the left eye under examination along the first measurement optical axis via the objective lens, and projects a second measurement pattern beam onto the right eye under examination along the second measurement optical axis, and receives the reflected light of the first measurement pattern beam from the left eye under examination and the reflected light of the second measurement pattern beam from the right eye under examination, An eye refractive power calculation unit calculates the refractive power of the left eye under examination based on the reception result of the reflected light of the first measurement pattern light beam, and calculates the refractive power of the right eye under examination based on the reception result of the reflected light of the second measurement pattern light beam, Includes, The refractive power measuring optical system is an ophthalmic device that projects the first measurement pattern light beam and the second measurement pattern light beam such that the focal position is at a position corresponding to the intermediate power between the refractive power of the left eye under examination and the refractive power of the right eye under examination.

18. The refractive power measuring optical system is A first projection system that projects the first measurement pattern light beam onto the left eye under examination, A second projection system that projects the second measurement pattern light beam onto the right eye under examination, A light receiving system that receives the reflected light of the first measurement pattern light beam and the reflected light of the second measurement pattern light beam, including The ophthalmic apparatus according to claim 16 or 17.

Images