Ophthalmic device and method of controlling an ophthalmic device

Abstract

An ophthalmic apparatus and a control method of an ophthalmic apparatus are disclosed. The ophthalmic apparatus includes a refractive power measuring optical system, a fixation projection system, an examination optical system, and a control section. The refractive power measuring optical system includes a first focusing element whose focal position is changeable, and projects first light toward a subject eye, and detects return light of the first light from the subject eye by means of the first focusing element. The fixation projection system projects a fixation target toward the subject eye. The examination optical system includes a second focusing element whose focal position is changeable in conjunction with the first focusing element, and is used to perform a prescribed examination of projecting second light toward at least the subject eye by means of the second focusing element. The control section controls the first focusing element and the second focusing element in accordance with a detection result of the return light, and after performing the prescribed examination based on the examination optical system, controls the fixation projection system to perform a refractive power measurement using the first light in a state of inducing fogging of the subject eye.

Description

[0001] This application is a divisional application of application number 201980012843.4 filed on January 10, 2019, entitled "Ophthalmic Device and Control Method for Ophthalmic Device". Technical Field

[0002] This invention relates to an ophthalmic device and a method for controlling the ophthalmic device. Background Technology

[0003] Ophthalmic devices capable of performing multiple examinations and measurements on the examined eye are known. These examinations and measurements include subjective and objective measurements. Subjective examinations are based on results obtained from the examinee's responses. Objective measurements, on the other hand, primarily use physical methods to obtain information relevant to the examined eye, without referring to the examinee's responses.

[0004] For example, Patent Document 1 discloses an ophthalmic device capable of performing measurements using subjective examination, refractive power measurement of the examined eye, and optical coherence tomography. In this ophthalmic device, whenever an examination, measurement, or determination is performed, the optical system is controlled to determine the focusing position of the light used in the examination, and the examination is performed at the determined focusing position. In such an ophthalmic device, focusing control is achieved by causing multiple focusing lenses in each optical system to operate in conjunction, thereby achieving miniaturization and simplified control.

[0005] Existing technical documents

[0006] Patent documents

[0007] Patent Document 1: Japanese Patent Application Publication No. 2017-136215 Summary of the Invention

[0008] However, refractive power measurement is performed while the eye being examined is in a fogged state. Therefore, if an examination using another optical system (e.g., using optical coherence tomography) is performed after the refractive power measurement, it is necessary to restore the focusing state of that other optical system to the state before the refractive power measurement. As a result, the examination time is increased, which can be burdensome for the examinee.

[0009] The present invention was made in view of this problem, and its object is to provide an ophthalmic device and a method for controlling the ophthalmic device that can reduce the burden on the examinee while performing multiple examinations, including refractive power measurement, with a simple structure and control.

[0010] Some embodiments provide an ophthalmic device comprising: a refractive power measuring optical system including a first focusing element with a changeable focal position, projecting first light onto an eye to be examined, and detecting, by means of the first focusing element, the return light of the first light from the eye to be examined; a fixation projection system for projecting a fixed optotype onto the eye to be examined; an examination optical system including a second focusing element with a changeable focal position in conjunction with the first focusing element, and for performing a designated examination by projecting second light onto the eye to be examined by means of the second focusing element; and a control unit that controls the first focusing element and the second focusing element based on the detection result of the return light of the first light obtained by using the refractive power measuring optical system in a state where the fixed optotype is projected onto the eye to be examined, and after performing the designated examination based on the examination optical system, controls the fixation projection system to perform refractive power measurement using the first light in a state that causes the eye to be examined to fog up.

[0011] Some embodiments provide a method for controlling an ophthalmic device, the ophthalmic device comprising: a power-measuring optical system including a first focusing element with a changeable focal position, projecting first light onto an eye to be examined, and detecting a return light of the first light from the eye to be examined by means of the first focusing element; a fixation projection system for projecting a fixed optotype onto the eye to be examined; and an examination optical system including a second focusing element with a changeable focal position in conjunction with the first focusing element, and for performing a specified examination by projecting second light onto the eye to be examined by means of the second focusing element, the method for controlling the ophthalmic device comprising: a focus control step, controlling the first focusing element and the second focusing element based on a detection result of the return light of the first light predicted by using the power-measuring optical system while the fixed optotype is projected onto the eye to be examined; an examination step, after the focus control step, controlling the examination optical system to perform the specified examination; and a power-measuring step, after the examination step, controlling the fixation projection system to perform a power measurement of the first light while causing the eye to fog up.

[0012] A first embodiment of some implementations is an ophthalmic device comprising: a refractive power measuring optical system including a first focusing element with a changeable focal position, projecting first light onto an eye to be examined, and detecting a return light from the first light from the eye to be examined by means of the first focusing element; a fixation projection system for projecting a fixed optotype onto the eye to be examined; an examination optical system including a second focusing element with a changeable focal position in conjunction with the first focusing element, and for performing a designated examination by means of the second focusing element to project second light onto at least the eye to be examined; and a control unit that controls the first focusing element and the second focusing element based on the detection result of the return light, and after performing the designated examination based on the examination optical system, controls the fixation projection system to perform a refractive power measurement using the first light in a state that causes the eye to be examined to be fogged.

[0013] According to the first embodiment, a second aspect of some implementations of the ophthalmic device includes: a holding member for holding the first focusing element and the second focusing element; and a driving unit for driving the holding member, wherein the control unit controls the movement of the first focusing element and the second focusing element by controlling the driving unit.

[0014] In some implementations, a third approach is based on the first or second approach, wherein the control unit causes the examined eye to fog up by moving the focal position of the image of the fixed target from a position determined based on the detection result of the returned light along the optical axis of the fixed projection system.

[0015] According to the third embodiment, in some implementations, the fourth aspect of the fixed projection system includes a display unit that displays the fixed target, and the control unit changes the focal position of the image of the fixed target by moving the display unit along the optical axis of the fixed projection system.

[0016] A fifth embodiment of some implementations is based on any one of the first to fourth embodiments, wherein the examination optical system includes an OCT optical system that projects a measurement light, which is the second light, onto the eye being examined and detects the return light of the measurement light and the interference light of the reference light from the eye being examined.

[0017] A sixth embodiment of some implementations is a method for controlling an ophthalmic device, the ophthalmic device comprising: a refractive power measuring optical system including a first focusing element with a changeable focal position, projecting first light onto an eye to be examined, and detecting a return light from the first light from the eye to be examined by means of the first focusing element; a fixation projection system for projecting a fixed optotype onto the eye to be examined; and an examination optical system including a second focusing element with a changeable focal position in conjunction with the first focusing element, for performing a designated examination by means of the second focusing element projecting second light onto at least the eye to be examined. The control method of the ophthalmic device includes: a focus control step, controlling the first focusing element and the second focusing element based on the detection result of the return light; an examination step, after the focus control step, controlling the examination optical system to perform the designated examination; and a refractive power measuring step, after the examination step, controlling the fixation projection system to perform a refractive power measurement using the first light in a state that causes the eye to be examined to fog up.

[0018] A seventh embodiment of some implementations, according to the sixth embodiment, wherein, in the focusing control step, the first focusing element is moved along the optical axis of the refractive power measuring optical system, and the second focusing element is moved along the optical axis of the inspection optical system.

[0019] An eighth embodiment of some implementations, based on the sixth or seventh embodiment, wherein, in the refractive power measurement step, the examined eye is caused to fog up by moving the focal position of the image of the fixed target from a position determined based on the detection result of the returned light along the optical axis of the fixation projection system.

[0020] According to the eighth embodiment, in the ninth aspect of some implementations, the focal position of the image of the fixed target is changed by moving the display section displaying the fixed target along the optical axis of the fixed projection system during the refractive power measurement step.

[0021] In some embodiments, a tenth method is based on any one of the sixth to ninth methods, wherein the inspection step involves projecting the measurement light, which is the second light, onto the eye under examination to perform an OCT measurement that detects the return light of the measurement light and the interference light of the reference light from the eye under examination.

[0022] According to the present invention, an ophthalmic device and a method for controlling the ophthalmic device are provided, which can reduce the burden on the examinee with a simple structure and control, while performing multiple examinations including refractive power measurement. Attached Figure Description

[0023] Figure 1 This is a schematic diagram illustrating a structural example of the optical system of an ophthalmic device according to an embodiment.

[0024] Figure 2 This is a schematic diagram illustrating a structural example of the optical system of an ophthalmic device according to an embodiment.

[0025] Figure 3 This is a schematic diagram illustrating a structural example of the processing system of an ophthalmic device according to an embodiment.

[0026] Figure 4 This is a schematic diagram illustrating the operation of an ophthalmic device according to an embodiment.

[0027] Figure 5 This is a schematic diagram illustrating the operation of an ophthalmic device according to an embodiment.

[0028] Figure 6 This is a schematic diagram illustrating the operation of an ophthalmic device according to an embodiment.

[0029] (Explanation of reference numerals in the attached diagram)

[0030] 1: Z alignment system; 2: XY alignment system; 3: Corneal measurement system; 4: Fixation projection system; 5: Anterior eye observation system; 6: Reflection measurement projection system; 7: Reflection measurement light receiving system; 8: OCT optical system; 9: Processing unit; 210: Control unit; 211: Main control unit; 1000: Ophthalmic device. Detailed Implementation

[0031] Referring to the accompanying drawings, examples of embodiments of the ophthalmic device and its control method according to the present invention will be described in detail. Furthermore, the contents of the documents cited in this specification and any prior art can be applied to the following embodiments.

[0032] The ophthalmic device described in this embodiment can perform multiple examinations (measurements), including the measurement of the refractive power of the examined eye. In addition to the refractive power measurement, there are objective measurements and subjective examinations.

[0033] Objective measurements are methods that primarily use physical methods to obtain information about the examined eye without referencing responses from the subject. Objective measurements include measurements to obtain characteristics of the examined eye and imaging of the examined eye. In addition to refractive power measurement, objective measurements also include corneal shape measurement, intraocular pressure measurement, fundus photography, and optical coherence measurement.

[0034] Subjective examination is a measurement method that uses responses from the examinee to obtain information. Subjective examinations include subjective refractive measurements such as farsightedness testing, nearsightedness testing, contrast testing, and glare testing, as well as visual field testing.

[0035] The ophthalmic apparatus of the embodiment includes a refractive power measuring optical system for performing refractive power measurement, an examination optical system for performing examinations other than refractive power measurement, and a fixation projection system for projecting a fixed target onto the examined eye. The refractive power measuring optical system includes a first focusing element with a changeable focal position, projects first light onto the examined eye, and detects the return light from the first light from the examined eye using the first focusing element. The examination optical system includes a second focusing element with a changeable focal position in conjunction with the first focusing element, for performing a designated examination in which second light is projected onto at least the examined eye using the second focusing element.

[0036] In this configuration, the ophthalmic device can perform an examination based on the examination optics system during the interval of refractive power measurement. Specifically, the ophthalmic device controls the first and second focusing elements based on the refractive power of the examined eye calculated from the detection result of the returned light based on the first light, performs the specified examination based on the examination optics system, and then performs a refractive power measurement using the refractive power measuring optics system. The refractive power measurement is performed while a fixed target is projected onto the examined eye through a fixation projection system, and the examined eye is fogged up.

[0037] In the following embodiments, the examination optical system is described as an OCT optical system used to perform optical coherence tomography (OCT) on the examined eye. Furthermore, below, the fundus conjugate position refers to a position optically conjugate to the fundus of the examined eye in the fully aligned state, meaning a position optically conjugate to or near the fundus of the examined eye. Similarly, the pupil conjugate position refers to a position optically conjugate to the pupil of the examined eye in the fully aligned state, meaning a position optically conjugate to or near the pupil of the examined eye.

[0038] <Structure of an Optical System>

[0039] Figure 1 An example of the structure of the optical system of the ophthalmic device according to the embodiment is shown. The ophthalmic device 1000 of the embodiment includes an optical system for observing the examined eye E, an optical system for examining the examined eye E, and a dichroic mirror for wavelength separation of the optical paths of these optical systems. As the optical system for observing the examined eye E, an anterior ocular observation system 5 is provided. As the optical system for examining the examined eye E, an OCT optical system and a reflectance measurement optical system (refractive power measurement optical system) are provided.

[0040] The ophthalmic device 1000 includes a Z-alignment system 1, an XY-alignment system 2, a corneal measurement system 3, a fixation projection system 4, an anterior eye observation system 5, a reflectivity measurement projection system 6, a reflectivity measurement light receiving system 7, and an OCT optical system 8. For example, the anterior eye observation system 5 uses light from 940 nm to 1000 nm, the reflectivity measurement optical system (reflectivity measurement projection system 6 and reflectivity measurement light receiving system 7) uses light from 830 nm to 880 nm, the fixation projection system 4 uses light from 400 nm to 700 nm, and the OCT optical system 8 uses light from 1000 nm to 1100 nm.

[0041] (Anterior Eye Observation System 5)

[0042] The anterior eye observation system 5 dynamically captures images of the anterior eye of the examined eye E. In the optical system of the anterior eye observation system 5, the imaging surface of the imaging element 59 is positioned at the pupil conjugate position. An anterior eye illumination source 50 illuminates the anterior eye of the examined eye E with illumination light (e.g., infrared light). Light reflected from the anterior eye of the examined eye E passes through the objective lens 51, through the dichroic mirror 52, through the aperture formed in the aperture (telecentric aperture) 53, through the semi-reflective mirror 23, through the relay lenses 55 and 56, and through the dichroic mirror 76. The dichroic mirror 52 combines (separates) the optical paths of the reflection measurement optical system and the anterior eye observation system 5. The dichroic mirror 52 is arranged such that the optical path combining surface is tilted relative to the optical axis of the objective lens 51. Light transmitted through the dichroic mirror 76 is imaged by the imaging lens 58 onto the imaging surface of the imaging element 59 (area sensor). The imaging element 59 performs imaging and signal output at a predetermined rate. The output (image signal) of the imaging element 59 is input to the processing unit 9, which will be described later. The processing unit 9 displays the fore-eye image E' based on the image signal on the display screen 10a of the display unit 10, which will be described later. The fore-eye image E' is, for example, an infrared dynamic image.

[0043] (Z-alignment system 1)

[0044] The Z-alignment system 1 projects light (infrared light) for alignment along the optical axis (anteroposterior direction, Z direction) of the anterior eye observation system 5 onto the examined eye E. Light output from the Z-alignment light source 11 is projected onto the cornea Cr of the examined eye E, reflected by the cornea Cr, and imaged through the imaging lens 12 onto the sensing surface of the online sensor 13. When the position of the corneal apex changes along the optical axis of the anterior eye observation system 5, the projection position of the light onto the sensing surface of the online sensor 13 changes. The processing unit 9 determines the position of the corneal apex of the examined eye E based on the projection position of the light onto the sensing surface of the sensor 13, and performs Z-alignment by controlling the mechanism that moves the optical system accordingly.

[0045] (XY Alignment System 2)

[0046] The XY alignment system 2 illuminates the examined eye E with light (infrared light) used for alignment in a direction orthogonal to the optical axis of the anterior eye observation system 5 (left-right direction (X direction) and up-down direction (Y direction)). The XY alignment system 2 includes an XY alignment light source 21 and a collimating lens 22 disposed on the optical path branching from the anterior eye observation system 5 via a semi-reflecting mirror 23. Light output from the XY alignment light source 21 passes through the collimating lens 22, is reflected by the semi-reflecting mirror 23, and is projected onto the examined eye E through the anterior eye observation system 5. The reflected light generated by the cornea Cr of the examined eye E is guided to the imaging element 59 through the anterior eye observation system 5.

[0047] The image (bright spot image) Br based on the reflected light is included in the forearm image E'. The processing unit 9 displays the forearm image E' including the bright spot image Br and the alignment mark AL on the display screen. In the case of manual XY alignment, the user moves the optical system to guide the bright spot image Br within the alignment mark AL. In the case of automatic XY alignment, the processing unit 9 controls the mechanism that moves the optical system to cancel the displacement of the bright spot image Br relative to the alignment mark AL.

[0048] (Corneal Measurement System 3)

[0049] The corneal measurement system 3 projects a ring-shaped beam (infrared light) onto the cornea Cr, which is used to measure the shape of the cornea Cr of the examined eye E. A corneal plate 31 is arranged between the objective lens 51 and the examined eye E. A corneal ring light source 32 is provided on the back side (objective lens 51 side) of the corneal plate 31. By illuminating the corneal plate 31 with light from the corneal ring light source 32, the ring-shaped beam is projected onto the cornea Cr of the examined eye E. The reflected light from the cornea Cr of the examined eye E (corneal ring image) is detected by the imaging element 59 along with the anterior eye image E'. The processing unit 9 calculates corneal shape parameters that display the shape of the cornea Cr by performing known calculations based on the corneal ring image.

[0050] (Reflection measurement projection system 6, reflection measurement light receiving system 7)

[0051] The reflectance measurement optical system includes a reflectance measurement projection system 6 and a reflectance measurement receiving system 7 used in refractive power measurement. The reflectance measurement projection system 6 projects a beam of light (e.g., a ring beam) (infrared light) for refractive power measurement onto the fundus Ef. The reflectance measurement receiving system 7 receives the reflected light from the examined eye E. The reflectance measurement projection system 6 is positioned on the optical path branched by an aperture prism 65 disposed in the optical path of the reflectance measurement receiving system 7. The aperture formed in the aperture prism 65 is arranged at a position conjugate to the pupil. In the optical system via the reflectance measurement receiving system 7, the imaging surface of the imaging element 59 is positioned at a position conjugate to the fundus.

[0052] In some embodiments, the reflectance measurement light source 61 is a super luminescent diode (SLD) light source, which is a high-brightness light source. The reflectance measurement light source 61 is movable in the optical axis direction. The reflectance measurement light source 61 is arranged at the conjugate position of the fundus. The light output from the reflectance measurement light source 61 is incident on the conical surface of the conical prism 63 through the relay lens 62. The light incident on the conical surface is deflected and exits from the bottom surface of the conical prism 63. The light exiting from the bottom surface of the conical prism 63 passes through a ring-shaped light-transmitting portion formed on the annular aperture 64. The light (ring-shaped beam) passing through the light-transmitting portion of the annular aperture 64 is reflected by the reflective surface formed around the aperture of the aperture prism 65, and is reflected by the dichroic mirror 67 after passing through the rotating prism 66. 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 eye being examined, E. The rotating prism 66 is used to average the light distribution of the annular beam on the blood vessels and diseased areas of the fundus Ef and to reduce the light spot noise caused by the light source.

[0053] The returning light from the annular beam projected onto the fundus Ef passes through objective lens 51 and is reflected by dichroic mirrors 52 and 67. The returning light reflected by dichroic mirror 67 passes through rotating prism 66, through the aperture of open prism 65, through relay lens 71, is reflected by reflecting mirror 72, and then through relay lens 73 and focusing lens 74. Focusing lens 74 is movable along the optical axis of the reflective light receiving system 7. The light passing through focusing lens 74 is reflected by reflecting mirror 75 and dichroic mirror 76, and then imaged on the imaging surface of imaging element 59 by imaging lens 58. Processing unit 9 calculates the refractive power of the examined eye E by performing known calculations based on the output from imaging element 59. In some embodiments, the refractive power includes spherical power, astigmatic power, and astigmatic axis angle. In some embodiments, the refractive power includes equivalent spherical power.

[0054] (Fixed projection system 4)

[0055] The OCT optical system 8, described later, is positioned on the optical path through which the wavelength of the light path of the reflective measurement optical system is separated by the dichroic mirror 67. The fixed projection system 4 is positioned on the optical path through which the light path of the OCT optical system 8 branches off from the optical path of the dichroic mirror 83.

[0056] The fixation projection system 4 presents a fixed target to the eye being examined, E. A liquid crystal panel 41, controlled by the processing unit 9, displays the pattern of the fixed target. By changing the display position of the pattern on the screen of the liquid crystal panel 41, the fixation position of the eye being examined, E, can be changed. Possible fixation positions for the eye being examined, such as positions for acquiring an image centered on the macula of the fundus Ef, positions for acquiring an image centered on the optic nerve head, and positions for acquiring an image centered on the center of the fundus between the macula and the optic nerve head, etc. The display position of the pattern of the fixed target can be arbitrarily changed. Alternatively, instead of the liquid crystal panel 41, an illumination light source can be provided that displays a transmissive target image and an illuminated target image printed on a thin film or the like.

[0057] Light from the liquid crystal panel 41 passes through the relay lens 42, then through the dichroic mirror 83, and is reflected by the reflecting mirror 81. It then passes through the dichroic mirror 67 and is reflected by the dichroic mirror 52. The light reflected by the dichroic mirror 52 is projected onto the fundus Ef through the objective lens 51. The liquid crystal panel 41 (or the liquid crystal panel 41 and the relay lens 42) can move along the optical axis.

[0058] (OCT Optical System 8)

[0059] The OCT optical system 8 is an optical system used for performing OCT measurements. Based on the reflection measurement results performed prior to the OCT measurement, the position of the focusing lens 87 is adjusted so that the end face of the fiber f1 is conjugate with the fundus Ef and the optical system.

[0060] The OCT optical system 8 is positioned on the optical path separated from the wavelength of the reflective optical system by the dichroic mirror 67. The optical path of the fixed projection system 4 is combined with the optical path of the OCT optical system 8 by the dichroic mirror 83. Thus, the optical axes of the OCT optical system 8 and the fixed projection system 4 can be coaxially aligned.

[0061] The OCT optical system 8 includes an OCT unit 100. For example... Figure 2 As shown, in the OCT unit 100, similar to a typical swept-frequency light source type OCT device, the OCT light source 101 is configured as a wavelength swept-frequency (wavelength scanning) light source capable of sweeping (scanning) the wavelength of the emitted light. The wavelength swept-frequency light source is configured to include a laser light source, which includes a resonator. The OCT light source 101 outputs a wavelength that varies over time in the near-infrared band, which is imperceptible to the human eye.

[0062] like Figure 2As shown, the OCT unit 100 is equipped with an optical system for performing frequency-sweeping light source OCT. This optical system includes an interference optical system. This interference optical system has the functions of splitting light from a wavelength-variable light source (wavelength-sweeping type light source) into measurement light and reference light, generating interference light by coinciding the return light from the measured light from the examined eye E and the reference light via the reference optical path, and detecting the interference light. The detection result (detection signal) of the interference light obtained by the interference optical system is a signal displaying the spectrum of the interference light and is sent to the processing unit 9.

[0063] OCT light source 101 includes, for example, a near-infrared wavelength-variable laser that rapidly changes the wavelength of the emitted light (in the wavelength range of 1000 nm to 1100 nm). The light L0 output from OCT light source 101 is guided by optical fiber 102 to polarization controller 103 to adjust its polarization state. The polarization-adjusted light L0 is then guided by optical fiber 104 to fiber coupler 105 to split into measurement light LS and reference light LR.

[0064] The reference light LR is guided by fiber optic cable 110 to collimator 111 and converted into a parallel beam. It is then guided to corner cube 114 via optical path length correction member 112 and dispersion compensation member 113. Optical path length correction member 112 ensures that the optical path length of the reference light LR matches that of the measurement light LS. Dispersion compensation member 113 integrates the dispersion characteristics of the reference light LR and the measurement light LS. Corner cube 114 can move along the incident direction of the reference light LR, thereby changing the optical path length of the reference light LR.

[0065] The reference light LR, passing through the corner bevel prism 114, is converted from a parallel beam to a focused beam by the collimator 116 via the dispersion compensation component 113 and the optical path length correction component 112, and then incident on the optical fiber 117. The reference light LR incident on the optical fiber 117 is guided to the polarization controller 118 to adjust its polarization state, guided to the attenuator 120 via the optical fiber 119 to adjust the light intensity, and guided to the optical fiber coupler 122 via the optical fiber 121.

[0066] On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the fiber f1 and converted into a parallel beam by the collimating lens unit 89. It is then reflected by the dichroic mirror 83 via the optical scanner 88, the focusing lens 87, the relay lens 85, and the reflector 84.

[0067] The optical scanner 88 deflects the measurement light LS in one or two dimensions. The optical scanner 88 includes, for example, a first current mirror and a second current mirror. The first current mirror deflects the measurement light LS to scan the fundus Ef in a horizontal direction orthogonal to the optical axis of the OCT optical system 8. The second current mirror deflects the measurement light LS deflected by the first current mirror to scan the fundus Ef in a vertical direction orthogonal to the optical axis of the OCT optical system 8. Examples of scanning shapes for the measurement light LS based on this optical scanner 88 include horizontal scanning, vertical scanning, cross scanning, radial scanning, circular scanning, concentric circle scanning, and spiral scanning.

[0068] The measurement light LS, reflected by dichroic mirror 83, passes through relay lens 82, is reflected by mirror 81, passes through dichroic mirror 67, is reflected by dichroic mirror 52, and is refracted by objective lens 51 before entering the eye being examined, E. The measurement light LS is scattered and reflected at various depth positions of the eye being examined, E. The return light of the measurement light LS from the eye being examined, E, travels in the opposite direction along the same path as its outgoing journey and is guided to fiber optic coupler 105, then reaches fiber optic coupler 122 via fiber optic cable 128.

[0069] Fiber optic coupler 122 combines the measurement light LS incident via fiber 128 and the reference light LR incident via fiber 121 (causing them to interfere) to generate interference light. Fiber optic coupler 122 branches the interference light at a predetermined branching ratio (e.g., 1:1), thereby generating a pair of interference lights LC. The pair of interference lights LC are guided to detector 125 via fibers 123 and 124, respectively.

[0070] Detector 125 is, for example, a balanced photodiode. The balanced photodiode includes a pair of photodetectors that detect a pair of interfering light LCs respectively, and outputs the difference between the pair of detection results obtained through these photodetectors. Detector 125 sends this output (detection signal) to DAQ (Data Acquisition System) 130.

[0071] A clock KC is supplied from the OCT light source 101 to the DAQ 130. The clock KC is generated synchronously in the OCT light source 101 with the output timing of each wavelength scanned within a predetermined wavelength range by a wavelength-variable light source. For example, the OCT light source 101 generates the clock KC based on the detection of one branch of the two branched light obtained by branching the light L0 of each output wavelength, after optical delay. The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC. The DAQ 130 sends the sampling result of the detection signal from the detector 125 to the arithmetic processing unit 220 of the processing unit 9. The arithmetic processing unit 220 performs a Fourier transform on the spectral distribution based on the sampled data, for example, according to a series of wavelength scans (along the A-line), thereby forming the reflection intensity status of each A-line. Furthermore, the arithmetic processing unit 220 forms image data by imagerizing the reflection intensity status of each A-line.

[0072] In this example, although a corner prism 114 is provided for changing the length of the optical path (reference optical path, reference arm) of the reference light LR, other optical components can also be used to change the difference between the length of the measuring optical path and the length of the reference optical path.

[0073] The processing unit 9 calculates the refractive power value from the measurement results obtained using the reflectance measurement optical system. Based on the calculated refractive power value, it moves the reflectance measurement light source 61 and the focusing lens 74 in the optical axis direction at positions conjugate to the fundus Ef, the reflectance measurement light source 61, and the imaging element 59. In some embodiments, the processing unit 9 moves the focusing lens 87 of the OCT optical system 8 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 41 in the optical axis direction in conjunction with the movement of the reflectance measurement light source 61 and the focusing lens 74.

[0074] <Structure of the Processing System>

[0075] The structure of the processing system of the ophthalmic device 1000 will be described. An example of the functional structure of the processing system of the ophthalmic device 1000 is provided below. Figure 3 As shown in the image. Figure 3 An example of a functional block diagram of the processing system of the ophthalmic device 1000 is shown.

[0076] The processing unit 9 controls various parts of the ophthalmic device 1000. Furthermore, the processing unit 9 is capable of performing various arithmetic operations. The processing unit 9 includes a processor. The functions of the processor are implemented, for example, by circuits such as a CPU (Central Processing Unit), GPU (Graphics Processing Unit), ASIC (Application Specific Integrated Circuit), or programmable logic device (e.g., SPLD (Simple Programmable Logic Device), CPLD (Complex Programmable Logic Device), FPGA (Field Programmable Gate Array)). The processing unit 9 implements the functions of the embodiment, for example, by reading and executing a program stored in a storage circuit or storage device.

[0077] The processing unit 9 includes a control unit 210 and an arithmetic processing unit 220. The processing unit 9 includes one or more processors that implement the functions of the control unit 210 and the arithmetic processing unit 220. For example, the processing unit 9 includes a control processor that implements the functions of the control unit 210 and an arithmetic processing processor that implements the functions of the arithmetic processing unit 220. Additionally, the ophthalmic device 1000 includes a movement mechanism 200, a display unit 270, an operation unit 280, and a communication unit 290.

[0078] The moving mechanism 200 is used to move a head housing optical systems such as the Z-alignment system 1, XY-alignment system 2, corneal measurement system 3, fixation projection system 4, anterior eye observation system 5, reflectance measurement projection system 6, reflectance measurement light receiving system 7, and OCT optical system 8 in the front-back and left-right directions. For example, the moving mechanism 200 includes an actuator that generates a driving force for moving the head and a transmission mechanism that transmits this driving force. The actuator is, for example, a pulse motor. The transmission mechanism is, for example, a gear assembly or a rack and pinion. The control unit 210 (main control unit 211) controls the moving mechanism 200 by sending control signals to the actuator.

[0079] (Control Unit 210)

[0080] The control unit 210 includes a processor and controls various parts of the ophthalmic device. The control unit 210 includes a main control unit 211 and a storage unit 212. The storage unit 212 stores pre-stored computer programs for controlling the ophthalmic device. These computer programs include programs for controlling the light source, detectors, optical scanners, optical systems, computational processing, and user interfaces. The main control unit 211 operates according to these computer programs, thereby enabling the control unit 210 to perform control processing.

[0081] The main control unit 211, acting as the measurement control unit, performs various controls on the ophthalmic device. Control of the Z-alignment system 1 includes the control of the Z-alignment light source 11 and the line sensor 13. Control of the Z-alignment light source 11 includes turning the light source on and off, adjusting the light intensity, and adjusting the aperture. Control of the line sensor 13 includes adjusting the exposure, gain, and detection rate of the detection element. This allows switching the Z-alignment light source 11 between being on and off, or changing its brightness. The main control unit 211 reads the signal detected by the line sensor 13 and specifies the projection position of the light onto the line sensor 13 based on the read signal. Based on the specified projection position, the main control unit 211 determines the position of the corneal apex of the examined eye E, and based on this, controls the movement mechanism 200 to move the head in the forward-backward direction (Z-alignment).

[0082] The control of the XY alignment system 2 includes the control of the XY alignment light source 21. The 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 switching the XY alignment light source 21 between being on and off, or changing its brightness. The main control unit 211 reads the signal detected by the imaging element 59 and, based on the read signal, specifies the position of the bright spot image based on the return light from the XY alignment light source 21. The main control unit 211 controls the moving mechanism 200 to move the head in the up, down, left, and right directions to cancel the displacement (XY alignment) between the bright spot image Br and the predetermined target position (e.g., the center position of the alignment mark AL).

[0083] The control of the corneal measurement system 3 includes the control of the corneal ring light source 32. The control of the corneal ring light source 32 includes turning the light source on and off, adjusting the light intensity, and adjusting the aperture. This allows switching between on and off states of the corneal ring light source 32, or changing its brightness. The main control unit 211 causes the arithmetic processing unit 220 to perform known calculations on the corneal ring image detected by the imaging element 59. This calculates the corneal shape parameters of the examined eye E.

[0084] The fixed projection system 4 is controlled by the liquid crystal panel 41, etc. The control of the liquid crystal panel 41 includes turning the display of the fixed target on / off and switching the display position of the fixed target. This projects the fixed target onto the fundus Ef of the examined eye E. For example, the fixed projection system 4 includes a moving mechanism that moves the liquid crystal panel 41 (or the liquid crystal panel 41 and the relay lens 42) along the optical axis. Similar to the moving mechanism 200, this moving mechanism includes an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending control signals to the actuator, at least moving the liquid crystal panel 41 along the optical axis. This adjusts the position of the liquid crystal panel 41 so that the liquid crystal panel 41 and the fundus Ef are optically conjugate.

[0085] The control of the anterior eye observation system 5 includes the control of the anterior eye illumination source 50 and the camera element 59. The control of the anterior eye illumination source 50 includes turning the light source on and off, adjusting the light intensity, and adjusting the aperture. This allows switching between on and off states of the anterior eye illumination source 50, or changing the light intensity. The control of the camera element 59 includes adjusting the exposure, gain, and detection rate of the camera element 59. The main control unit 211 reads the signal detected by the camera element 59, and the arithmetic processing unit 220 performs image formation and other processing based on the read signal.

[0086] The control of the reflectivity measurement projection system 6 includes the control of the reflectivity measurement light source 61 and the control of the rotating prism 66. The control of the reflectivity measurement light source 61 includes turning the light source on and off, adjusting the light intensity, and adjusting the aperture. This allows switching between on and off states of the reflectivity measurement light source 61, or changing the light intensity. For example, the reflectivity measurement projection system 6 includes a moving mechanism that moves the reflectivity measurement light source 61 along the optical axis. Similar to the moving mechanism 200, this moving mechanism includes 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, causing the reflectivity measurement light source 61 to move along the optical axis. The control of the rotating prism 66 includes the rotation control of the rotating prism 66. For example, a rotating mechanism is provided to rotate the rotating prism 66, and the main control unit 211 controls this rotating mechanism to rotate the rotating prism 66.

[0087] The control of the reflectivity measurement light-receiving system 7 includes the control of the focusing lens 74. The control of the focusing lens 74 includes the control of its movement along the optical axis. For example, the reflectivity measurement light-receiving system 7 includes a moving mechanism for moving the focusing lens 74 along the optical axis. Similar to the moving mechanism 200, this moving mechanism includes an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, causing the focusing lens 74 to move along the optical axis. For example, the main control unit 211 can move the reflectivity measurement light source 61 and the focusing lens 74 along the optical axis according to the refractive power of the examined eye E, so that the reflectivity measurement light source 61, the fundus Ef, and the imaging element 59 are optically conjugated.

[0088] The control of the OCT optical system 8 includes the control of the OCT light source 101, the optical scanner 88, the focusing lens 87, the corner cube prism 114, the detector 125, and the DAQ 130. The control of the OCT light source 101 includes turning the light source on and off, adjusting the light intensity, and adjusting the aperture. The control of the optical scanner 88 includes controlling the scanning position, scanning range, and scanning speed of the first current mirror, and the scanning position, scanning range, and scanning speed of the second current mirror. The control of the focusing lens 87 includes controlling the movement of the focusing lens 87 along the optical axis. For example, the OCT optical system 8 includes a moving mechanism for moving the focusing lens 87 along the optical axis. Similar to the moving mechanism 200, this moving mechanism includes an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending control signals to the actuator, causing the focusing lens 87 to move along the optical axis. In some embodiments, the ophthalmic device includes a holding member for holding the focusing lens 74 and the focusing lens 87, and a driving unit for driving the holding member. The main control unit 211 controls the movement of the focusing lens 74 and the focusing lens 87 by controlling the driving unit. For example, the main control unit 211 may move the focusing lens 87 only based on the intensity of the interference signal after moving it in conjunction with the movement of the focusing lens 74. The control of the corner cube prism 114 includes movement control of the corner cube prism 114 along the optical path. For example, the OCT optical system 8 includes a moving mechanism for moving the corner cube prism 114 in the direction along the optical path. Similar to the moving mechanism 200, this moving mechanism includes an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, causing the corner cube prism 114 to move in the direction along the optical path. The control of the detector 125 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. The main control unit 211 samples the signal detected by the detector 125 through the DAQ 130, and causes the arithmetic processing unit 220 (image forming unit 222) to perform image forming and other processing based on the sampled signal.

[0089] In addition, the main control unit 211 performs the processing of writing data to the storage unit 212 and the processing of reading data from the storage unit 212.

[0090] (Storage Department 212)

[0091] Storage unit 212 stores various types of data. Data stored in storage unit 212 includes, for example, objective measurement results, tomographic image data, fundus image data, and information about the examined eye. The examined eye information includes information about the examinee, such as patient ID and name, and information about the examined eye, such as identification information for the left and right eyes. Additionally, storage unit 212 stores various programs and data used to operate the ophthalmic device.

[0092] (Computational Processing Unit 220)

[0093] The arithmetic processing unit 220 includes an ocular refractive power calculation unit 221, an image forming unit 222, and a data processing unit 223. The arithmetic processing unit 220 includes one or more processors that implement the functions of the ocular refractive power calculation unit 221, the image forming unit 222, and the data processing unit 223. For example, the arithmetic processing unit 220 includes a processor that implements the functions of the ocular refractive power calculation unit 221, an image forming processor that implements the functions of the image forming unit 222, and a data processing processor that implements the functions of the data processing unit 223.

[0094] The ocular refractive power calculation unit 221 analyzes the annular image (pattern image), which is obtained by receiving the reflected light from the annular beam (annular measurement pattern) projected onto the fundus Ef by the reflective measurement projection system 6 via the imaging element 59. For example, the ocular refractive power calculation unit 221 determines the centroid position of the annular image based on the brightness distribution in the image scanned from the obtained annular image, determines the brightness distribution along multiple scanning directions extending radially based on the centroid position, and specifies the annular image based on the brightness distribution. Next, the ocular refractive power calculation unit 221 determines the approximate ellipse of the specified annular image, and calculates the spherical power, astigmatism power, and astigmatic axis angle by substituting the major and minor axes of the approximate ellipse into known formulas. Alternatively, the ocular refractive power calculation unit 221 can calculate the parameters of the ocular refractive power based on the deformation and displacement of the annular image of the reference pattern.

[0095] Furthermore, the ocular refractive power calculation unit 221 calculates the corneal refractive power, corneal astigmatism, and corneal astigmatic axis angle based on the corneal ring image acquired through the anterior eye observation system 5. For example, the ocular refractive power calculation unit 221 calculates the corneal curvature radii of the strong and weak principal meridians in front of the cornea by analyzing the corneal ring image, and calculates the above parameters based on the corneal curvature radii.

[0096] The image forming unit 222 forms image data of a tomographic image of the fundus Ef based on the signal detected by the detector 125. That is, the image forming unit 222 forms image data of the examined eye E based on the detection result of the interference light LC of the interference optical system. Similar to existing spectral domain OCT, this processing includes filtering, FFT (Fast Fourier Transform), and other processing. The image data thus acquired is a data set consisting of a group of image data formed by imagering the reflection intensity conditions on multiple A-lines (the paths of each measurement light LS within the examined eye E).

[0097] To improve image quality, multiple data sets collected by repeatedly scanning the same pattern can be superimposed (and averaged).

[0098] The data processing unit 223 performs various data processing (image processing) and analysis processing on the tomographic image formed by the image forming unit 222. For example, the data processing unit 223 performs correction processing such as brightness correction and dispersion correction on the image. In addition, the data processing unit 223 performs various image processing and analysis processing on the image (fore-eye image, etc.) obtained using the anterior eye observation system 5.

[0099] The data processing unit 223 can generate volume data (voxel data) of the examined eye E by performing known image processing such as interpolation processing for pixel interpolation between tomographic images. In the case of an image based on volume data display, the data processing unit 223 performs rendering processing on the volume data to generate a similar three-dimensional image when viewed from a specified viewing direction.

[0100] (Display unit 270, Operation unit 280)

[0101] The display unit 270 serves as a user interface unit, receiving control from the control unit 210 to display information. The display unit 270 includes... Figure 1 The display unit 10 shown in the figure.

[0102] The operation unit 280 serves as a user interface unit for operating the ophthalmic device. The operation unit 280 includes various hardware keys (joysticks, buttons, switches, etc.) provided on the ophthalmic device. Additionally, the operation unit 280 may also include various software keys (buttons, icons, menus, etc.) displayed on a touch panel-type display screen 10a.

[0103] Alternatively, at least a portion of the display unit 270 and the operation unit 280 may be integrated into one unit. As a typical example, there is a touch panel-type display screen 10a.

[0104] (Communication Department 290)

[0105] The communication unit 290 has the function of communicating with an external device (not shown). The communication unit 290 has a communication interface corresponding to the connection method of the external device. An example of an external device is a spectacle lens measuring device for measuring the optical characteristics of a lens. The spectacle lens measuring device measures the power of the spectacle lens worn by the examinee, and inputs this measurement data to the ophthalmic device 1000. Alternatively, the external device can be any ophthalmic device, a device for reading information from a recording medium (reader), or a device for writing information to a recording medium (writer), etc. Furthermore, the external device can also be a hospital information system (HIS) server, a DICOM (Digital Imaging and Communications in Medicine) server, a doctor's terminal, a mobile terminal, a personal terminal, a cloud server, etc. The communication unit 290 can also be provided in, for example, the processing unit 9.

[0106] The focusing lens 74 is an example of a "first focusing element with a changeable focal position" in the embodiment. The light output from the reflectance measuring light source 61 is an example of a "first light" in the embodiment. The reflectance measuring optical system or OCT optical system 8 is an example of a "refractive power measuring optical system" in the embodiment. The focusing lens 87 is an example of a "second focusing element with a changeable focal position in conjunction with the first focusing element" in the embodiment. The measuring light LS is an example of a "second light" in the embodiment. The OCT optical system 8 is an example of an "inspection optical system" in the embodiment. The liquid crystal panel 41 is an example of a "display unit" in the embodiment.

[0107] <Action Examples>

[0108] The operation of the ophthalmic device 1000 according to the embodiment will be explained.

[0109] Figures 4-6 The image shows an example of the operation of the ophthalmic device 1000. Figure 4 A flowchart showing an example of the operation of the ophthalmic device 1000. Figure 5 show Figure 4 The flowchart for step S3 is shown. Figure 6 show Figure 4 The flowchart shows an example of the action of step S4. The storage unit 212 stores information for implementing... Figures 4-6 The computer program for processing is shown in the figure. The main control unit 211 executes the operation according to the computer program. Figures 4-6 The processing is shown in the figure.

[0110] (S1: Align)

[0111] With the subject's face fixed to the face receiving unit (not shown), the subject performs a predetermined operation on the operation unit 280, thereby aligning the ophthalmic device 1000.

[0112] Specifically, the main control unit 211 illuminates the Z-aligned light source 11 and the XY-aligned light source 21. Additionally, the main control unit 211 illuminates the front eye illumination source 50. The processing unit 9 acquires the imaging signal of the front eye image on the imaging surface of the imaging element 59 and displays the front eye image on the display unit 270. Afterwards, Figure 1 The optical system shown is moved to the examination position of the eye being examined, E. The examination position is one where the examination of the eye being examined, E, can be performed with sufficient accuracy. Using the alignment described above (based on the alignment of the Z-alignment system 1, XY-alignment system 2, and anterior eye observation system 5), the eye being examined, E, is positioned at the examination position. The movement of the optical system is executed by the control unit 210 according to the user's operation, instructions, or commands from the control unit 210. That is, the movement of the optical system to the examination position of the eye being examined and preparation for objective measurement are performed.

[0113] In addition, the main control unit 211 moves the reflectance measuring light source 61, the focusing lens 74 and the liquid crystal panel 41 along their respective optical axes to the initial point position (for example, the position corresponding to 0D).

[0114] (S2: Corneal Analysis)

[0115] Next, the main control unit 211 causes the liquid crystal panel 41 to display the pattern of the fixed target at a display position corresponding to the desired fixation position. As a result, the examined eye E fixates on the desired fixation position.

[0116] Subsequently, the main control unit 211 illuminates the corneal ring light source 32. If light is output from the corneal ring light source 32, a ring-shaped beam for measuring the corneal shape is projected onto the cornea Cr of the examined eye E. The ocular refractive power calculation unit 221 performs computational processing on the image acquired by the imaging element 59 to calculate the corneal radius of curvature, and calculates the corneal refractive power, corneal astigmatism, and corneal astigmatic axis angle based on the calculated corneal radius of curvature. The control unit 210 stores the calculated corneal refractive power, etc., in the storage unit 212. Based on instructions from the main control unit 211, or user operations or instructions to the operation unit 280, the operation of the ophthalmic device 1000 proceeds to step S3. Furthermore, this corneal analysis can be performed simultaneously or continuously during the formal measurement in step S5.

[0117] (S3: Prediction)

[0118] Next, the main control unit 211 controls the liquid crystal panel 41 to project a fixed target onto the eye being examined, E, and begins the reflectivity measurement. In this embodiment, the reflectivity measurement includes a prediction setting and a formal measurement. In the prediction setting, the focusing state in the reflectivity measurement optical system is changed according to the refractive power of the eye being examined, E. In the formal measurement, the eye being examined, E, is fogged up based on the focusing state changed by the prediction setting, while the refractive power of the eye being examined, E, is acquired.

[0119] In step S3, the reflectance measuring light source 61, focusing lens 74, and focusing lens 87 are moved along the optical axis and positioned to correspond to the refractive power of the examined eye E. Details of step S3 will be described later.

[0120] (S4: OCT measurement)

[0121] Next, the main control unit 211, with the focusing lens 87 moved in step S3, moves the corner bevel prism 114 to correct the optical path length and obtain the desired OCT image of the eye. OCT measurement is then performed by controlling the OCT optical system 8. That is, OCT measurement is performed during the interval of reflection measurement. Therefore, OCT measurement is performed before the examined eye E becomes fogged, eliminating the need for focusing control for OCT measurement and shortening the measurement time. Furthermore, the optical path length correction by moving the corner bevel prism 114 can also be performed in parallel by automatically adjusting the position of the OCT image in step S3. Details of step S4 will be described later.

[0122] The operation of the ophthalmic device 1000 is transferred to step S5 by instruction from the main control unit 211 or by the user's operation or instruction to the operation unit 280.

[0123] (S5: Formal Measurement)

[0124] In step S5, the main control unit 211 moves the liquid crystal panel 41 from the position determined in the prediction to the atomization position, thereby causing the examined eye E to atomize. Then, with the reflectivity measurement light source 61 off, the main control unit 211 illuminates the reflectivity measurement light source 61. Additionally, with the rotation of the rotating prism 66 stopped, the main control unit 211 starts the rotation of the rotating prism 66. Next, similar to the prediction, the main control unit 211 controls the reflectivity measurement projection system 6 and the reflectivity measurement receiving system 7 to acquire the annular image again. The main control unit 211 causes the eye refractive power calculation unit 221 to calculate the spherical power, astigmatism power, and astigmatic axis angle based on the resolution of the annular image and the movement of the focusing lens 74. The calculated spherical power, astigmatism power, and astigmatic axis angle are stored in the storage unit 212.

[0125] (S6: Obtain the OCT image?)

[0126] Next, the main control unit 211 determines whether to acquire an OCT image. The main control unit 211 determines whether to acquire an OCT image based on instructions from itself or user operations or instructions to the operation unit 280. For example, if the time required for OCT measurements such as 3D scanning is longer, acquiring an OCT image after step S5 can reduce the burden on the subject.

[0127] When it is determined that an OCT image needs to be acquired (S6: Yes), the operation of the ophthalmic device 1000 proceeds to step S7. When it is determined that an OCT image does not need to be acquired (S6: No), the operation of the ophthalmic device 1000 ends (terminates).

[0128] (S7: Acquire OCT image)

[0129] When it is determined in step S6 that an OCT image needs to be acquired (S6: Yes), the main control unit 211 causes the liquid crystal panel 41, which was moved to the atomization position in step S5, to return to the focus position determined in the prediction step S3. Then, the main control unit 211 controls the liquid crystal panel 41 to project the fixed target onto the examined eye E, and performs an OCT measurement.

[0130] The main control unit 211 illuminates the OCT light source 101 and controls the optical scanner 88 to scan a designated area of ​​the fundus Ef using the measurement light LS. The detection signal obtained by the 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 Ef based on the obtained detection signal. The operation of the ophthalmic device 1000 then ends.

[0131] Prediction in step S3 Figure 5 Perform as shown.

[0132] (S11: Turn on the reflective measurement light source and start rotating the prism)

[0133] First, the main control unit 211 illuminates the reflectance measuring light source 61 and starts the rotation of the rotating prism 66.

[0134] (S12: Analyzing the circular image)

[0135] Next, the main control unit 211 projects a ring-shaped measurement pattern beam onto the examined eye E. A ring-shaped image based on the return light from the measurement pattern beam of the examined eye E is imaged on the imaging surface of the imaging element 59. The main control unit 211 determines whether a ring-shaped image based on the return light from the fundus Ef detected by the imaging element 59 has been acquired. For example, the main control unit 211 detects the edge position (pixel) of the image based on the return light detected by the imaging element 59 and determines whether the image width (difference between outer and inner diameters) is above a predetermined value. Alternatively, the main control unit 211 may determine whether a ring-shaped image has been acquired by determining whether a ring can be formed based on points (images) of a predetermined height (ring diameter).

[0136] When it is determined that a ring image has been obtained, the ocular refractive power calculation unit 221 analyzes the ring image based on the return light of the measurement pattern beam projected onto the tested eye E using a known method, and calculates the temporary spherical power S and the temporary astigmatism power C.

[0137] (S13: Moving the focusing lens)

[0138] The main control unit 211 moves the reflectance measuring light source 61, the focusing lens 74, and the liquid crystal panel 41 to the position of the equivalent spherical degree (S+C / 2) based on the temporary spherical degree S and astigmatism degree C obtained in step S12.

[0139] (S14: Analyzing the Circular Image)

[0140] Next, similar to step S12, the main control unit 211 projects the annular measurement pattern beam onto the examined eye E. An annular image based on the return light from the measurement pattern beam of the examined eye E is imaged on the imaging surface of the imaging element 59. The main control unit 211 determines whether an annular image based on the return light from the fundus Ef detected by the imaging element 59 has been acquired.

[0141] When it is determined that a ring image has been obtained, the ocular refractive power calculation unit 221 analyzes the ring image based on the return light of the measurement pattern beam projected onto the tested eye E using a known method, and calculates the temporary spherical power S and the temporary astigmatism power C.

[0142] (S15: Moving the focusing lens)

[0143] Based on the temporary spherical power S and astigmatism C obtained in step S14, the main control unit 211 moves the reflectance measuring light source 61, the focusing lens 74, and the liquid crystal panel 41 to a position equivalent to the spherical power (S+C / 2). The position moved in step S15 is equivalent to the position of the temporary far point.

[0144] (S16: Turn off the reflective measuring light source and stop the rotation of the rotating prism)

[0145] Next, the main control unit 211 turns off the reflectivity measuring light source 61 and stops the rotation of the rotating prism 66. That concludes... Figure 4 Step S3 ends (terminates).

[0146] Figure 4 Step S4 is as follows Figure 6 Perform as shown.

[0147] (S21: Turn on the OCT light source and start the light scanner operation)

[0148] First, the main control unit 211 illuminates the OCT light source 101 and starts the operation of the light scanner 88. Thereby, the measuring light LS scans a designated area (anterior eye, fundus, or both) of the examined eye E. Furthermore, alignment can be performed using known methods in step S21. Additionally, tracking can also be initiated.

[0149] (S22: Obtain tomographic images)

[0150] Next, the main control unit 211 sends the detection signal obtained by scanning the measurement light LS to the image forming unit 222. The image forming unit 222 forms a tomographic image of the examined eye E based on the obtained detection signal. If the tomographic image is not formed in the proper position, the position of the tomographic image can be adjusted by adjusting the corner bevel prism 114.

[0151] (S23: Calculate intraocular parameters)

[0152] The main control unit 211 instructs the data processing unit 223 to calculate intraocular parameters based on the tomographic image obtained in step S22 or the detection signal obtained through scanning. The intraocular parameters include at least one of the following: axial length, corneal thickness, anterior chamber depth, lens thickness, radius of curvature of the strong principal meridian in front of the cornea, radius of curvature of the weak principal meridian in front of the cornea, radius of curvature of the strong principal meridian in back of the cornea, radius of curvature of the weak principal meridian in back of the cornea, radius of curvature of the strong principal meridian in front of the lens, radius of curvature of the weak principal meridian in front of the lens, radius of curvature of the strong principal meridian in back of the lens, and radius of curvature of the weak principal meridian in back of the lens.

[0153] (S24: Turn off the OCT light source and stop the operation of the light scanner)

[0154] Next, the main control unit 211 turns off the OCT light source 101 and stops the operation of the light scanner 88. That concludes... Figure 3 Step S4 ends (terminates).

[0155] Furthermore, if it is determined that a ring image cannot be acquired in step S12 or S14, the main control unit 211 considers that the eye may have an intensity refractive error and moves the reflectance measurement light source 61 and the focusing lens 74 in a pre-set sequence toward the negative diopter side (e.g., -10D) and the positive diopter side (e.g., +10D). The main control unit 211 controls the reflectance measurement light receiving system 7 to detect the ring image at various positions. If it is still determined that a ring image cannot be acquired even after this, the main control unit 211 executes a predetermined measurement error handling procedure.

[0156] In the above embodiments, at least one function of the relay lens 42, focusing lens 74, and focusing lens 87 can also be achieved by a liquid crystal lens or a liquid lens.

[0157] [Functions and Effects]

[0158] The function and effect of the ophthalmic device and the control method of the ophthalmic device described in the embodiments are explained.

[0159] Some embodiments of the ophthalmic device 1000 include a refractive power measuring optical system (reflection measuring optical system), a fixation projection system 4, an examination optical system (OCT optical system 8), and a control unit 210 (main control unit 211). The refractive power measuring optical system includes a first focusing element (focusing lens 74) with a changeable focal position, which projects a first light onto the examined eye E and detects the return light from the first light from the examined eye using the first focusing element. The fixation projection system projects a fixed optotype onto the examined eye. The examination optical system includes a second focusing element (focusing lens 87) with a changeable focal position linked to the first focusing element, for performing a designated examination (OCT measurement) in which a second light (measuring light LS) is projected onto at least the examined eye using the second focusing element. The control unit controls the first and second focusing elements based on the detection result of the return light, performs the designated examination based on the examination optical system, and then controls the fixation projection system to perform a refractive power measurement using the first light in a state that causes the examined eye to fog up.

[0160] Based on this structure, the first focusing element is controlled according to the detection result of the return light of the first light obtained through the refractive power measuring optical system. Corresponding to the control of the first focusing element, the second focusing element is also controlled according to the above detection result. This simplifies the focusing control used for refractive power measurement and specified examinations, thus enabling a simplification of both the structure and control of the ophthalmic device.

[0161] Afterwards, following an inspection using the second light via the inspection optical system, a refractive power measurement using the first light is performed via the refractive power measuring optical system. That is, the specified inspection is performed during the intervals of the refractive power measurement. Therefore, control of the second focusing element for inspections based on the inspection optical system is eliminated, reducing measurement time and lessening the burden on the examinee.

[0162] Some embodiments of the ophthalmic device include a holding member for holding a first focusing element and a second focusing element, and a driving unit for driving the holding member, wherein a control unit controls the movement of the first focusing element and the second focusing element by controlling the driving unit.

[0163] Based on this structure, by moving the first focusing element and the second focusing element with a single drive unit, the focal positions of the first focusing element and the second focusing element can be changed, thus greatly simplifying the structure and control of the ophthalmic device.

[0164] In some implementations of ophthalmic devices, the control unit causes the examined eye to fog up by moving the focal position of the image of the fixed target from a position determined based on the detection results of the returned light (equivalent to the position of the temporary far point) along the optical axis of the fixation projection system.

[0165] Based on this structure, the examined eye can be atomized without controlling the first focusing element and the second focusing element.

[0166] In some embodiments of ophthalmic devices, the fixation projection system includes a display unit (liquid crystal panel 41) that displays a fixed target, and a control unit changes the focal position of the image of the fixed target by moving the display unit along the optical axis of the fixation projection system.

[0167] Based on this structure, the examined eye can be atomized or returned to its original position (the position determined by the detection result of the returned light) with a simple structure.

[0168] In some embodiments of the ophthalmic device, the examination optical system includes an OCT optical system 8 that projects a measurement light, which serves as a second light, onto the eye being examined and detects the interference light LC of the return light from the measurement light and the reference light LR from the eye being examined.

[0169] Based on this structure, it is possible to provide an ophthalmic device that can perform refractive power measurement and OCT measurement with a simple structure and control that can reduce the burden on the subject.

[0170] Some embodiments are control methods for an ophthalmic device comprising a refractive power measuring optical system (reflection measuring optical system), a fixation projection system 4, and an examination optical system (OCT optical system 8). The refractive power measuring optical system includes a first focusing element (focusing lens 74) with a changeable focal position, projects first light onto the examined eye E, and detects the return light from the first light from the examined eye using the first focusing element. The fixation projection system projects a fixed optotype onto the examined eye. The examination optical system includes a second focusing element (focusing lens 87) with a changeable focal position linked to the first focusing element, for performing a designated examination by projecting a second light (measuring light) onto at least the examined eye using the second focusing element. The control method for the ophthalmic device includes: a focusing control step of controlling the first focusing element and the second focusing element based on the detection result of the return light; and, after the focusing control step, controlling the examination optical system to perform an examination step of performing the designated examination; and, after the examination step, controlling the fixation projection system to perform a refractive power measuring step using the first light in a fogged state for the examined eye.

[0171] Based on this structure, the first focusing element is controlled according to the detection result of the return light of the first light obtained through the refractive power measuring optical system. Corresponding to the control of the first focusing element, the second focusing element is also controlled according to the above detection result. This simplifies the focusing control used for refractive power measurement and specified examinations, thus enabling a simplification of both the structure and control of the ophthalmic device.

[0172] Afterwards, following an inspection using the second light via the inspection optical system, a refractive power measurement using the first light is performed via the refractive power measuring optical system. That is, the specified inspection is performed during the intervals of the refractive power measurement. Therefore, control of the second focusing element for inspections based on the inspection optical system is eliminated, reducing measurement time and lessening the burden on the examinee.

[0173] In some embodiments of the ophthalmic device, the control method involves moving a first focusing element along the optical axis of the refractive power measuring optical system and moving a second focusing element along the optical axis of the examination optical system during the focusing control step.

[0174] Based on this structure, the focal positions of the first and second focusing elements can be changed by moving them with a single drive control, thus greatly simplifying the structure and control of the ophthalmic device.

[0175] In some implementations of ophthalmic devices, the control method involves moving the focal position of the image of the fixed target from a position determined based on the detection results of the returning light (equivalent to the position of the temporary far point) along the optical axis of the fixation projection system, thereby causing the examined eye to fog up.

[0176] Based on this structure, the examined eye can be atomized without controlling the first focusing element and the second focusing element.

[0177] In some embodiments of the ophthalmic device, the control method changes the focal position of the image of the fixed target by moving the display unit (liquid crystal panel 41) displaying the fixed target along the optical axis of the fixation projection system during the refractive power measurement step.

[0178] Based on this structure, the examined eye can be atomized or returned to its original position (the position determined by the detection result of the returned light) with a simple structure.

[0179] In the control method of an ophthalmic device in some embodiments, the examination step involves performing an OCT measurement that projects a measurement light, which serves as a second light, onto the eye being examined and detects the return light of the measurement light from the eye being examined and the interference light LS of the reference light LR.

[0180] Based on this structure, a control method can be provided for an ophthalmic device that performs refractive power measurement and OCT measurement with a simple structure and control that reduces the burden on the subject.

[0181] <Other>

[0182] The embodiments shown above are merely examples for implementing the present invention. Those wishing to implement the present invention can make any modifications, omissions, additions, etc., within the scope of the spirit of the present invention.

[0183] In some embodiments, a program is provided for causing a computer to execute the control method of the ophthalmic device described above. Such a program can be stored on any computer-readable storage medium. Examples of such storage media include semiconductor memory, optical discs, optical disks (CD-ROM / DVD-RAM / DVD-ROM / MO, etc.), and magnetic storage media (hard disk / floppy disk / ZIP, etc.). Furthermore, the program can be transmitted and received via networks such as the Internet or a LAN.

Claims

1. An ophthalmic device comprising: A refractive power measuring optical system includes a first focusing element with a changeable focal position, which projects first light onto the eye being examined and detects the return light of the first light from the eye being examined by means of the first focusing element; A fixation projection system projects a fixed visual target onto the examined eye. An inspection optical system includes a second focusing element whose focal position is changeable in conjunction with the first focusing element, and is used to perform a specified examination by projecting second light onto the examined eye via the second focusing element; and The control unit controls the first focusing element and the second focusing element based on the detection result of the return light of the first light obtained by using the refractive power measuring optical system in the state of projecting the fixed target onto the examined eye. After performing the specified examination based on the examination optical system, the control unit controls the fixation projection system to perform the refractive power measurement of the first light in the state of causing the examined eye to fog up.

2. The ophthalmic device according to claim 1, characterized in that, The ophthalmic device includes: Holding component, holding the first focusing element and the second focusing element; and The drive unit drives the retaining component. The control unit controls the movement of the first focusing element and the second focusing element by controlling the drive unit.

3. The ophthalmic device according to claim 1 or 2, characterized in that, The control unit causes the examined eye to fog up by moving the focal position of the image of the fixed target from the position determined based on the detection result of the return light of the first light along the optical axis of the fixed projection system.

4. The ophthalmic device according to claim 3, characterized in that, The fixed projection system includes a display unit that displays the fixed target. The control unit changes the focal position of the image of the fixed target by moving the display unit along the optical axis of the fixed projection system.

5. The ophthalmic device according to claim 1 or 2, characterized in that, The examination optical system includes an OCT optical system that projects a measurement light, which serves as the second light, onto the eye under examination and detects the return light of the measurement light and the interference light of the reference light from the eye under examination.

6. A method for controlling an ophthalmic device, the ophthalmic device comprising: A refractive power measuring optical system includes a first focusing element with a changeable focal position, which projects first light onto the eye being examined and detects the return light of the first light from the eye being examined by means of the first focusing element; A fixation projection system projects a fixed visual target onto the examined eye. as well as The optical system is inspected, including a second focusing element whose focal position is changeable in conjunction with the first focusing element, and is used to perform a specified examination by projecting second light onto the eye being examined via the second focusing element. The control method for the ophthalmic device includes: The focusing control step controls the first focusing element and the second focusing element based on the detection result of the return light of the first light obtained by using the refractive power measuring optical system in the state of the fixed target being projected onto the examined eye; Following the inspection step and the focusing control step, the inspection optical system is controlled to perform the specified inspection; and Following the examination step, the fixation projection system is controlled to perform a refractive power measurement using the first light while the examined eye is in a state of fogging.

7. The control method for the ophthalmic device according to claim 6, characterized in that, In the focusing control step, the first focusing element is moved along the optical axis of the refractive power measuring optical system, and the second focusing element is moved along the optical axis of the inspection optical system.

8. The control method for the ophthalmic device according to claim 6 or 7, characterized in that, In the refractive power measurement step, the eye under examination is fogged by moving the focal position of the image of the fixed target from the position determined based on the detection result of the return light of the first light along the optical axis of the fixation projection system.

9. The control method for the ophthalmic device according to claim 8, characterized in that, In the refractive power measurement step, the focal position of the image of the fixed target is changed by moving the display section displaying the fixed target along the optical axis of the fixed projection system.

10. The control method for the ophthalmic device according to claim 6 or 7, characterized in that, The inspection step involves projecting the measurement light, which is the second light, onto the eye under examination to perform an OCT measurement that detects the return light of the measurement light and the interference light of the reference light from the eye under examination.

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