JP6833081B2 - Ophthalmic equipment and ophthalmic examination system - Google Patents

Description

The present invention relates to an ophthalmic apparatus and an ophthalmic examination system.

There are known ophthalmic devices that can perform multiple tests and measurements on the eye to be inspected. Examinations and measurements for the eye to be inspected include subjective examinations and objective measurements. A subjective test obtains results based on the response from the subject. Objective measurement is to obtain information about the eye to be examined mainly by using a physical method without referring to the response from the subject.

For example, Patent Document 1 discloses an ophthalmic apparatus capable of performing subjective examination and objective measurement. The ophthalmic apparatus can perform a plurality of examinations and measurements including objective refraction measurement, subjective refraction measurement (distance examination, near vision examination, contrast examination, glare examination), and corneal shape measurement.

JP-A-2015-128482

Optical coherence tomography is very useful as a technique that enables acquisition of an image (tomographic image) showing the internal morphology of an object to be measured such as the fundus. For example, by referring to an image acquired by using optical coherence tomography, it is possible to observe the morphology of the region of interest such as the vicinity of the macula, and the reliability of the subjective test result can be improved. It is considered useful to provide an optical system for performing imaging and measurement using such optical coherence tomography in an ophthalmic apparatus capable of performing a subjective examination.

However, there is a problem that simply adding an optical system for performing imaging using optical coherence tomography to an optical system for performing a subjective examination causes an increase in size of the apparatus.

The present invention has been made to solve the above-mentioned problems, and provides an ophthalmic apparatus and an ophthalmic examination system capable of performing subjective examination and imaging and measurement using optical coherence tomography with a simple configuration. With the goal.

The ophthalmic apparatus according to the embodiment includes an objective lens, a subjective examination optical system, an interference optical system, an objective measurement optical system, and an optical power calculation unit. The subjective test optical system includes an optical element capable of correcting aberrations of the eye to be inspected, and projects an optotype onto the eye to be inspected using visible light via an objective lens and the optical element. The interfering optical system divides the infrared light from the light source into the reference light and the measurement light, irradiates the test eye with the measurement light through the objective lens and the optical element, and emits the interference light between the return light and the reference light. Generate and detect the generated interference light. The objective measurement optical system irradiates the fundus of the eye to be inspected with a ring-shaped measurement pattern using infrared light via an objective lens, and detects the return light from the fundus. The eye refractive power calculation unit obtains the refractive power of the eye to be inspected by analyzing a pattern image based on the return light detected by the objective measurement optical system. The interference optical system includes a first optical path coupling member that is arranged in the optical path of the subjective inspection optical system on the upstream side of the optical element and that couples the optical path of the interference optical system to the optical path of the subjective inspection optical system. The objective measurement optical system includes a second optical path coupling member which is arranged between the objective lens and the optical element and couples the optical path of the objective measurement optical system to the optical path coupled by the first optical path coupling member. The subjective test optical system includes a pupil lens arranged between the optical element and the first optical path coupling member.
Further, the ophthalmic apparatus according to the embodiment includes an objective lens, a subjective examination optical system, an interference optical system, an objective measurement optical system, and an optical power calculation unit. The subjective test optical system includes an optical element capable of correcting aberrations of the eye to be inspected, and projects an optotype onto the eye to be inspected using visible light via an objective lens and the optical element. The interfering optical system divides the infrared light from the light source into the reference light and the measurement light, irradiates the test eye with the measurement light through the objective lens and the optical element, and emits the interference light between the return light and the reference light. Generate and detect the generated interference light. The objective measurement optical system irradiates the fundus of the eye to be inspected with a ring-shaped measurement pattern using infrared light via an objective lens, and detects the return light from the fundus. The eye refractive power calculation unit obtains the refractive power of the eye to be inspected by analyzing a pattern image based on the return light detected by the objective measurement optical system. The interference optical system is arranged in the optical path of the subjective inspection optical system on the upstream side of the optical element, and the first optical path coupling member that couples the optical path of the interference optical system to the optical path of the subjective inspection optical system and the light of the interference optical system. An image rotator that is arranged on the axis and rotatably arranged around the optical axis to deflect the measurement light, an optical fiber that guides the measurement light, and a collimating lens that makes the measurement light emitted from the exit end of the optical fiber a parallel light beam. And, including. The objective measurement optical system includes a second optical path coupling member which is arranged between the objective lens and the optical element and couples the optical path of the objective measurement optical system to the optical path coupled by the first optical path coupling member. The image rotator deflects the measurement light converted into a parallel luminous flux by the collimating lens, and the optical fiber and the collimating lens are arranged so that their optical axes intersect with the optical axis of the image rotator.
The ophthalmologic examination system according to the embodiment includes a left examination unit for inspecting the left eye and a right examination unit for inspecting the right eye, and at least one of the left examination unit and the right examination unit is included. Includes an ophthalmic apparatus according to an embodiment.

According to the ophthalmic apparatus and the ophthalmologic examination system according to the present invention, it is possible to perform subjective examination and imaging and measurement using optical coherence tomography with a simple configuration.

It is the schematic which shows the structural example of the optical system of the ophthalmic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the optical system of the ophthalmic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the optical system of the ophthalmic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the processing system of the ophthalmic apparatus which concerns on embodiment. It is a flow chart of the operation example of the ophthalmic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the optical system of the ophthalmic apparatus which concerns on the 1st modification of embodiment. It is the schematic which shows the structural example of the optical system of the ophthalmic apparatus which concerns on the 1st modification of embodiment. It is the schematic which shows the structural example of the optical system of the ophthalmic apparatus which concerns on the 2nd modification of embodiment. It is the schematic which shows the structural example of the optical system of the ophthalmic apparatus which concerns on the 2nd modification of embodiment. It is the schematic which shows the structural example of the ophthalmic examination system to which the ophthalmologic apparatus which concerns on embodiment is applied.

Examples of embodiments of the ophthalmic apparatus and the ophthalmic examination system according to the present invention will be described in detail with reference to the drawings. It should be noted that the description contents of the documents cited in this specification and arbitrary known techniques can be incorporated into the following embodiments.

<Ophthalmic equipment>
The ophthalmic apparatus according to the embodiment is capable of performing at least one of any subjective tests and any objective measurements. In the subjective test, information (such as a target) is presented to the subject, and the result is acquired based on the subject's response to the information. The subjective test includes a distance test, a near test, a contrast test, a glare test and other subjective refraction measurements, and a visual field test. In objective measurement, light is applied to the eye to be inspected, and information on the eye to be inspected is acquired based on the detection result of the return light. Objective measurement includes measurement for acquiring the characteristics of the eye to be inspected and photographing for acquiring an image of the eye to be inspected. For objective measurement, objective refraction measurement, corneal shape measurement, tonometry, fundus photography, tomography using optical coherence tomography (OCT), and OCT were used. There are measurements etc.

Hereinafter, the ophthalmic apparatus according to the embodiment can perform distance examination, near vision examination, etc. as subjective examination, and can perform objective refraction measurement, corneal shape measurement, OCT imaging, etc. as objective measurement. It shall be a device. However, the configuration of the ophthalmic apparatus according to the embodiment is not limited to this.

Further, a case where the Fourier domain type OCT method is used in OCT imaging will be described. In particular, the ophthalmologic apparatus according to the following embodiment can perform OCT imaging using the technique of swept source OCT. For OCT imaging, a type other than swept source, for example, a method of spectral domain OCT may be used. In addition, the OCT imaging in the following embodiments can also use a time domain type OCT method.

[Constitution]
The ophthalmic apparatus according to the embodiment includes a face receiving portion fixed to the base and a pedestal that can be moved back and forth and left and right with respect to the base. The gantry is provided with a head portion in which an optical system for inspecting (measuring) the eye to be inspected is housed. By operating the operation unit located at the position on the examiner's side, the face receiving unit and the head unit can be moved relative to each other. In addition, the ophthalmic apparatus can automatically move the face receiving portion and the head portion relative to each other by performing the alignment described later.

1 to 3 show a configuration example of the optical system of the ophthalmic apparatus according to the embodiment. The ophthalmic apparatus has Z alignment system 1, XY alignment system 2, kerato measurement system 3, optotype projection system 4, observation system 5, reflex measurement projection system 6, and reflex measurement as optical systems for inspecting the eye E to be inspected. The light receiving system 7 and the OCT optical system 8 are included. In addition, the ophthalmic apparatus includes a processing unit 9.

(Processing unit 9)
The processing unit 9 controls each unit of the ophthalmic apparatus. In addition, the processing unit 9 can execute various arithmetic processes. The processing unit 9 includes a processor. The functions of the processor are, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, a SPLD (Simple Program Program), a programmable logic device (SPLD) , FPGA (Field Programmable Gate Array)) and the like. The processing unit 9 realizes the function according to the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example.

(Observation system 5)
The observation system 5 captures a moving image of the anterior segment of the eye E to be inspected. The light (infrared light) from the anterior segment of the eye E to be inspected passes through the objective lens 51, passes through the dichroic mirror 52, and passes through the aperture of the aperture 53. The light that has passed through the aperture 53 passes through the half mirror 22, passes through the relay lenses 55 and 56, and passes through the half mirror 76. The light transmitted through the half mirror 76 is imaged on the image pickup surface of the image pickup element 59 (area sensor) by the image pickup lens 58. The image sensor 59 performs image pickup and signal output at a predetermined rate. The output (video signal) of the image sensor 59 is input to the processing unit 9. The processing unit 9 displays the anterior segment image E'based on this video signal on the display screen 10a of the display unit 10. The anterior segment image E'is, for example, an infrared moving image. The observation system 5 may include an illumination light source for illuminating the anterior segment of the eye.

(Z alignment system 1)
The Z alignment system 1 irradiates the eye E to be inspected with light (infrared light) for aligning the observation system 5 in the optical axis direction (front-back direction, Z direction). The light output from the Z alignment light source 11 is applied to the cornea K of the eye E to be inspected, reflected by the cornea K, and imaged on the line sensor 13 by the imaging lens 12. When the position of the apex of the cornea changes in the anteroposterior direction, the projected position of light on the line sensor 13 changes. The processing unit 9 obtains the position of the corneal apex of the eye E to be inspected based on the projection position of the light with respect to the line sensor 13, and executes Z alignment based on this.

(XY alignment system 2)
The XY alignment system 2 irradiates the eye E with light (infrared light) for aligning in a direction (horizontal direction (X direction), vertical direction (Y direction)) orthogonal to the optical axis of the observation system 5. .. The XY alignment system 2 includes an XY alignment light source 21 provided in an optical path branched from the observation system 5 by a half mirror 22. The light output from the XY alignment light source 21 is reflected by the half mirror 22 and is irradiated to the eye E to be inspected through the observation system 5. The reflected light from the cornea K is guided to the image sensor 59 through the observation system 5.

This reflected light image (bright spot image) is included in the anterior segment image E'. As shown in FIG. 1, the processing unit 9 displays the anterior segment image E'including the bright spot image Br and the alignment mark AL on the display screen 10a. When the XY alignment is manually performed, the user such as the examiner or the examinee moves the optical system so as to guide the bright spot image Br in the alignment mark AL. When the alignment is performed automatically, the processing unit 9 controls a mechanism for moving the optical system so that the displacement of the bright spot image Br with respect to the alignment mark AL is cancelled.

(Kerato measurement system 3)
The kerato measurement system 3 projects a ring-shaped luminous flux (infrared light) for measuring the shape of the cornea K onto the cornea K. The kerato plate 31 is arranged between the objective lens 51 and the eye E to be inspected. A keratling light source 32 is provided on the back side (objective lens 51 side) of the kerato plate 31. By illuminating the kerato plate 31 with the light from the kerat ring light source 32, a ring-shaped luminous flux is projected onto the cornea K. The reflected light (keratling image) is detected by the image sensor 59 together with the anterior segment image. The processing unit 9 calculates the corneal shape parameter by performing a known calculation based on this keratling image.

(Optimal projection system 4)
The optotype projection system 4 presents various optotypes such as a fixation target and an optotype for a subjective examination to the eye E to be inspected. The liquid crystal panel 41 receives control from the processing unit 9 and displays a pattern representing an optotype. The light (visible light) output from the liquid crystal panel 41 passes through the relay lens 42 and the focusing lens 43, and passes through the dichroic mirror 81. The light transmitted through the dichroic mirror 81 passes through the relay lens 44, the pupil lens 45, and the VCS lens 46, is reflected by the reflection mirror 47, is transmitted through the dichroic mirror 69, and is reflected by the dichroic mirror 52. The light reflected by the dichroic mirror 52 passes through the objective lens 51 and is projected onto the fundus Ef.

The focusing lens 43 can move along the optical axis of the optotype projection system 4. The position of the focusing lens 43 is adjusted so that the liquid crystal panel 41 and the fundus Ef are optically conjugated. The VCS lens 46 can adjust the astigmatism of the eye to be inspected (that is, can correct the aberration of the eye to be inspected). Specifically, the VCS lens 46 is controlled by the processing unit 9 and can change the astigmatic power and the astigmatic axis angle added to the eye E to be inspected, and at least the astigmatic power and the astigmatic axis of the eye aberration of the eye to be inspected. The angle can be corrected. As a result, the astigmatic state of the eye E to be inspected is corrected.

The liquid crystal panel 41 is controlled by the processing unit 9 and can display a pattern representing a fixation target for fixing the eye E to be inspected. By sequentially changing the display position of the pattern representing the fixation target on the liquid crystal panel 41, the fixation position can be moved and the fixation can be induced. Further, the optotype projection system 4 may include a glare inspection optical system for projecting glare light onto the eye E to be inspected together with the above-mentioned optotype.

When performing a subjective test, the processing unit 9 controls the liquid crystal panel 41, the focusing lens 43, and the VCS lens 46 based on the result of the objective measurement. The processing unit 9 causes the liquid crystal panel 41 to display the optotype selected by the examiner or the processing unit 9. As a result, the target is presented to the subject. The subject responds to the optotype. Upon receiving the input of the response content, the processing unit 9 further controls and calculates the subjective test value. For example, in the visual acuity measurement, the processing unit 9 selects and presents the next visual acuity based on the response to the Randold ring or the like, and repeatedly repeats this to determine the visual acuity value.

In objective measurement (objective refraction measurement, etc.), a landscape chart is projected on the fundus Ef. Alignment is performed while the subject is staring at this landscape chart, and the optical power is measured in a cloud-fog state.

(Ref measurement projection system 6 and reflex measurement light receiving system 7)
The reflex measurement projection system 6 and the reflex measurement light receiving system 7 are used for objective refraction measurement (refraction measurement). The reflex measurement projection system 6 projects a ring-shaped luminous flux (infrared light) for objective measurement onto the fundus Ef. In this specification, the ring-shaped luminous flux also includes a luminous flux having a shape in which a part of the ring is interrupted. The reflex measurement light receiving system 7 receives the return light of the ring-shaped luminous flux from the eye E to be inspected.

The light source unit 60 includes a reflex measurement light source 61, a condenser lens 62, a conical prism 63, and a ring aperture plate 64. The light source unit 60 can move along the optical axis of the reflex measurement projection system 6. The reflex measurement light source 61 is arranged at a position optically conjugate with the fundus Ef. The light output from the reflex measurement light source 61 passes through the condenser lens 62, passes through the conical prism 63, passes through the ring-shaped opening of the ring opening plate 64, and becomes a ring-shaped luminous flux. The ring-shaped light flux formed by the ring opening plate 64 passes through the relay lens 65 and the pupil lens 66, is reflected by the reflecting surface of the perforated prism 67, passes through the rotary prism 68, and is reflected by the dichroic mirror 69. The light reflected by the dichroic mirror 69 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the fundus Ef.

The rotary prism 68 is used to average the light amount distribution of the ring-shaped luminous flux with respect to the blood vessels and the diseased part of the fundus Ef.

The return light of the ring-shaped luminous flux projected on the fundus Ef passes through the objective lens 51 and is reflected by the dichroic mirrors 52 and 69. The return light reflected by the dichroic mirror 69 passes through the rotary prism 68, passes through the hole portion of the perforated prism 67, passes through the pupil lens 71, and is reflected by the reflection mirror 72. The light reflected by the reflection mirror 72 passes through the relay lens 73 and the focusing lens 74, and is reflected by the reflection mirror 75. The light reflected by the reflection mirror 75 is reflected by the half mirror 76 and imaged on the image pickup surface of the image pickup device 59 by the image pickup lens 58. The processing unit 9 calculates the spherical power S, astigmatism power C, and astigmatism axis angle A of the eye E to be inspected by performing a known calculation based on the output from the image sensor 59.

Based on the calculated refraction value, the processing unit 9 moves the light source unit 60 and the focusing lens 74 in the optical axis direction to positions where the reflex measurement light source 61, the fundus Ef, and the image sensor 59 are conjugate. .. Further, the processing unit 9 moves the focusing lens 43 in the optical axis direction in conjunction with the movement of the light source unit 60 and the focusing lens 74. Further, the processing unit 9 may move the focusing lens 82 of the OCT optical system 8 in the optical axis direction in conjunction with the movement of the light source unit 60 and the focusing lens 74.

(OCT optical system 8)
The OCT optical system 8 is an optical system for performing OCT imaging. The position of the focusing lens 82 is adjusted so that the end face of the optical fiber f2 is conjugated to the fundus Ef and the optical system based on the result of the reflex measurement performed before the OCT imaging.

The optical path of the OCT optical system 8 is coupled to the optical path of the optotype projection system 4 by the dichroic mirror 81. As a result, the optical axes of the OCT optical system 8 and the optotype projection system 4 can be coaxially coupled.

The OCT optical system 8 includes an OCT unit 90. As shown in FIG. 2, in the OCT unit 90, the OCT light source 91 is a wavelength sweep type (wavelength scanning type) light source capable of sweeping (scanning) the wavelength of emitted light, similarly to a general swept source type OCT device. Consists of including. The wavelength sweep type light source is configured to include a laser light source including a resonator. The OCT light source 91 changes the output wavelength with time in a near-infrared wavelength band that is invisible to the human eye.

The light (infrared light, broadband light) L0 output from the OCT light source 91 is divided into the measurement light LS and the reference light LR by the fiber coupler 92 guided through the optical fiber f1. The measurement light LS is guided to the collimating lens 86 through the optical fiber f2. On the other hand, the reference optical path LR is guided to the reference optical path length changing unit 94 through the optical fiber f4.

The reference optical path length changing unit 94 changes the optical path length of the reference optical path LR. The reference light LR guided to the reference optical path length changing unit 94 is converted into a parallel luminous flux by the collimating lens 95 and guided to the corner cube 96. The corner cube 96 folds back the traveling direction of the reference light LR, which is converted into a parallel luminous flux by the collimating lens 95, in the opposite direction. The optical path of the reference light LR incident on the corner cube 96 and the optical path of the reference light LR emitted from the corner cube 96 are parallel. Further, the corner cube 96 is movable in the direction along the incident optical path and the outgoing optical path of the reference light LR. This movement changes the length of the optical path of the reference light LR. The reference light LR emitted from the corner cube 96 is converted from a parallel luminous flux to a focused luminous flux by the collimating lens 97, enters the optical fiber f5, and is guided to the fiber coupler 93. A delay member or a dispersion compensation member may be provided between the collimating lens 95 and the corner cube 96 or between the corner cube 96 and the collimating lens 97. The delay member is an optical member for matching the optical path length (optical distance) of the reference light LR and the optical path length of the measurement light LS. The dispersion compensating member is an optical member for matching the dispersion characteristics between the reference light LR and the measurement light LS.

The measurement light LS converted into a parallel luminous flux by the collimating lens 86 is one-dimensionally or two-dimensionally deflected by the optical scanner 84. The optical scanner 84 includes a galvano mirror 84X and a galvano mirror 84Y. The galvanometer 84X deflects the measurement light LS so as to scan the fundus Ef in the X direction. The galvano mirror 84Y deflects the measurement light LS deflected by the galvano mirror 84X so as to scan the fundus Ef in the Y direction. Examples of the scanning mode of the measured optical LS by the optical scanner 84 include horizontal scan, vertical scan, cross scan, radial scan, circular scan, concentric circular scan, and spiral scan.

The measurement light LS deflected by the optical scanner 84 is reflected by the dichroic mirror 81 via the reflection mirror 83 and the focusing lens 82. The measurement light LS reflected by the dichroic mirror 81 is guided to the dichroic mirror 52 through the optotype projection system 4 and reflected by the dichroic mirror 52. The light reflected by the dichroic mirror 52 passes through the objective lens 51 and is applied to the eye E to be inspected. The measurement light LS is scattered (including reflection) at various depth positions of the eye E to be inspected. The return light of the measurement light LS including such backscattered light travels in the same path as the outward path in the opposite direction, is guided to the fiber coupler 92, and reaches the fiber coupler 93 via the optical fiber f3.

The fiber coupler 93 generates interference light by synthesizing (interfering with) the measurement light LS incidented through the optical fiber f3 and the reference light LR incidented via the optical fiber f5. The fiber coupler 93 generates a pair of interference light LCs by branching the interference light between the measurement light LS and the reference light LR at a predetermined branching ratio (for example, 1: 1). The pair of interference light LCs emitted from the fiber coupler 93 are guided to the detector 98 by the optical fibers f6 and f7, respectively.

The detector 98 is, for example, a balanced photodiode (BPD) having a pair of photodetectors that detect each pair of interference light LCs and outputting the difference between the detection results. The difference between the detection results output from the detector 98 is sampled based on the clock generated in synchronization with the output timing of each wavelength swept (scanned) within a predetermined wavelength range by the OCT light source 91. This sampling data is sent to the arithmetic processing unit 120 of the processing unit 9. The arithmetic processing unit 120 forms a reflection intensity profile in each A line by, for example, performing a Fourier transform or the like on the spectral distribution based on the sampling data for each series of wavelength scans (for each A line). Further, the arithmetic processing unit 120 forms image data by imaging the reflection intensity profile of each A line.

As described above, the OCT optical system 8 divides the light L0 from the OCT light source 91 into the reference light LR and the measurement light LS, irradiates the eye E to be examined with the measurement light LS, and uses the return light and the reference light LR. Includes an interference optical system that generates the interference light LC of the above and detects the generated interference light. This interference optical system irradiates the eye E to be inspected with the measurement light LS via the objective lens 51 and the VCS lens 46.

Such an OCT optical system 8 is coupled to the optical path of the optotype projection system 4 by a dichroic mirror 81. For example, when the optical path of the OCT optical system 8 is coupled to the optical path of another optical system using a perforated prism, the optical system is configured so that the measurement light passes through the hole of the perforated prism, so that the measurement light or It is necessary to consider the eclipse of the return light. Further, when the OCT optical system 8 is coupled to another optical system (ref measurement projection system 6 and reflex measurement light receiving system 7) that uses light having a wavelength close to the wavelength of the measurement light, the wavelengths are close to each other, which makes separation difficult. , Efficiency is reduced. On the other hand, since the optical path of the OCT optical system 8 is coupled to the optical path of another optical system by using the dichroic mirror 81, the configuration of the optical system can be simplified and the degree of freedom in designing the optical system is improved. Can be made to. In addition, it becomes easy to add another optical system, and the configuration can be expanded.

Further, since the above two optical paths are combined on the light source side (upstream side) of the VCS lens 46, the measurement light LS is irradiated to the fundus Ef through the VCS lens 46, and it is easier to converge to one point at the measurement site. Become. As a result, it becomes possible to acquire an interference signal based on the detection result of the interference light with sufficient intensity with the optimum lateral resolution.

As shown in FIG. 3, the intermediate position between the VCS lens 46 and the pupil lens 45 is arranged at a position optically conjugate with the pupil of the eye E to be inspected (pupil conjugate position Q). Similarly, the intermediate position between the galvano mirror 84X and the galvano mirror 84Y is arranged at a position optically conjugate with the pupil of the eye E to be inspected. Further, the focusing lens 82 is moved in the optical axis direction so that the fundus Ef of the eye E to be inspected and the fiber end face of the optical fiber f2 are optically coupled (fundus conjugate position P). Since the optical path of the OCT optical system 8 and the optical path of the optotype projection system 4 are coupled to each other on the light source side of the pupil lens 45, the fundus conjugate position P can be brought closer to the optotype projection system 4 and the optotype projection system 4. The OCT optical system 8 can be made smaller.

(Processing system configuration)
The processing system of the ophthalmic apparatus according to the embodiment will be described. An example of the functional configuration of the processing system of the ophthalmic apparatus is shown in FIG. FIG. 4 shows an example of a functional block diagram of the processing system of the ophthalmic apparatus according to the embodiment. The processing unit 9 includes a control unit 110 and an arithmetic processing unit 120. Further, the ophthalmic apparatus according to the embodiment includes a display unit 170, an operation unit 180, a communication unit 190, and a moving mechanism 200.

The moving mechanism 200 includes an optical system such as a Z alignment system 1, an XY alignment system 2, a kerato measurement system 3, an optotype projection system 4, an observation system 5, a reflex measurement projection system 6, a reflex measurement light receiving system 7, and an OCT optical system 8. It is a mechanism for moving the head portion in which the is stored in the front-back and left-right directions. For example, the moving mechanism 200 is provided with an actuator that generates a driving force for moving the moving mechanism 200 and a transmission mechanism that transmits the 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 110 (main control unit 111) controls the moving mechanism 200 by sending a control signal to the actuator.

(Control unit 110)
The control unit 110 includes a processor and controls each unit of the ophthalmic apparatus. The control unit 110 includes a main control unit 111 and a storage unit 112. A computer program for controlling the ophthalmic apparatus is stored in the storage unit 112 in advance. The computer program includes a light source control program, a detector control program, an optical scanner control program, an optical system control program, an arithmetic processing program, a user interface program, and the like. When the main control unit 111 operates according to such a computer program, the control unit 110 executes the control process.

The main control unit 111 controls various ophthalmic devices as a measurement control unit. The control for the Z alignment system 1 includes the control of the Z alignment light source 11 and the control of the line sensor 13. The control of the Z alignment light source 11 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. The control of the line sensor 13 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. As a result, the Z alignment light source 11 is switched between lighting and non-lighting, and the amount of light is changed. The main control unit 111 captures the signal detected by the line sensor 13 and specifies the projection position of the light with respect to the line sensor 13 based on the captured signal. The main control unit 111 obtains the position of the corneal apex of the eye E to be inspected based on the specified projection position, and controls the movement mechanism 200 based on this to move the head unit in the front-rear direction (Z alignment).

The control for the XY alignment system 2 includes the control of the XY alignment light source 21 and the like. The control of the XY alignment light source 21 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, the XY alignment light source 21 is switched between lighting and non-lighting, and the amount of light is changed. The main control unit 111 captures the signal detected by the image sensor 59, and determines the position of the bright spot image based on the return light of the light from the XY alignment light source 21 based on the captured signal. The main control unit 111 controls the movement mechanism 200 to move the head unit in the left-right, up-down direction so that the displacement from the position of the bright spot image with respect to a predetermined target position (for example, the center position of the alignment mark) is cancelled. (XY alignment).

The control for the kerato measurement system 3 includes the control of the kerat ring light source 32 and the like. Control of the keratling light source 32 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, the keratling light source 32 is switched between lighting and non-lighting, and the amount of light is changed. The main control unit 111 causes the arithmetic processing unit 120 to perform a known calculation on the keratling image detected by the image sensor 59. As a result, the corneal shape parameter of the eye E to be inspected is obtained.

Controls for the optotype projection system 4 include control of the liquid crystal panel 41, control of the focusing lens 43, control of the VCS lens 46, and the like. The control of the liquid crystal panel 41 includes turning on / off the display of the optotype and the fixation target, switching the display position of the fixation target, and the like. As a result, a target or a fixed target is projected on the fundus Ef of the eye E to be inspected. Control of the focusing lens 43 includes control of movement of the focusing lens 43 in the optical axis direction. For example, the optotype projection system 4 includes a moving mechanism that moves the focusing lens 43 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, and moves the focusing lens 43 in the optical axis direction. As a result, the position of the focusing lens 43 is adjusted so that the liquid crystal panel 41 and the fundus Ef are optically conjugated. Control of the VCS lens 46 includes control of changing the astigmatic power and the astigmatic axis angle. The VCS lens 46 includes a pair of concave-convex cylinder lenses provided so as to be relatively rotatable about its optical axis. The main control unit 111 relatively rotates the pair of cylinder lenses so as to correct the astigmatism state (astigmatism power, astigmatism axis angle) of the eye E to be inspected separately obtained, for example, by ref measurement described later.

Control of the observation system 5 includes control of the image sensor 59 and the like. The control of the image pickup device 59 includes exposure adjustment, gain adjustment, and detection rate adjustment of the image pickup device 59. The main control unit 111 captures the signal detected by the image sensor 59, and causes the arithmetic processing unit 120 to perform processing such as forming an image based on the captured signal. When the observation system 5 includes an illumination light source, the main control unit 111 can control the illumination light source.

Control of the reflex measurement projection system 6 includes control of the light source unit 60, control of the rotary prism 68, and the like. The control of the light source unit 60 includes the control of the reflex measurement light source 61 and the control of the light source unit 60. The control of the ref measurement light source 61 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, the reflex measurement light source 61 is switched between lighting and non-lighting, and the amount of light is changed. Control of the light source unit 60 includes control of movement of the light source unit 60 in the optical axis direction. For example, the reflex measurement projection system 6 includes a moving mechanism that moves the light source unit 60 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, and moves the light source unit 60 in the optical axis direction. Control of the rotary prism 68 includes rotation control of the rotary prism 68 and the like. For example, a rotation mechanism for rotating the rotary prism 68 is provided, and the main control unit 111 rotates the rotary prism 68 by controlling the rotation mechanism.

Control of the reflex measurement light receiving system 7 includes control of the focusing lens 74 and the like. Control of the focusing lens 74 includes control of movement of the focusing lens 74 in the optical axis direction. For example, the reflex measurement light receiving system 7 includes a moving mechanism that moves the focusing lens 74 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, and moves the focusing lens 74 in the optical axis direction. The main control unit 111 optically axes the light source unit 60 and the focusing lens 74 according to the refractive power of the eye E to be inspected, for example, so that the reflex measurement light source 61, the fundus Ef, and the image pickup element 59 are optically coupled. It is possible to move in the direction.

Controls for the OCT optical system 8 include control of the OCT light source 91, control of the optical scanner 84, control of the focusing lens 82, control of the corner cube 96, control of the detector 98, and the like. Control of the OCT light source 91 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. The control of the optical scanner 84 includes control of the scanning position, scanning range and scanning speed by the galvano mirror 84X, control of the scanning position, scanning range and scanning speed by the galvano mirror 84Y and the like. Control of the focusing lens 82 includes control of movement of the focusing lens 82 in the optical axis direction. For example, the OCT optical system 8 includes a moving mechanism that moves the focusing lens 82 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, and moves the focusing lens 82 in the optical axis direction. For example, the main control unit 111 may move the focusing lens 82 in conjunction with the movement of the focusing lens 43, and then move only the focusing lens 82 based on the intensity of the interference signal. Control of the corner cube 96 includes control of movement of the corner cube 96 in the optical axis direction. For example, the OCT optical system 8 includes a moving mechanism that moves the corner cube 96 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, and moves the corner cube 96 in the optical axis direction. As a result, the length of the optical path of the reference light LR is changed. Control of the detector 98 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. The main control unit 111 samples the signal detected by the detector 98, and causes the arithmetic processing unit 120 (image forming unit 122) to perform processing such as forming an image based on the sampled signal.

Further, the main control unit 111 performs a process of writing data to the storage unit 112 and a process of reading data from the storage unit 112.

(Storage unit 112)
The storage unit 112 stores various types of data. The data stored in the storage unit 112 includes, for example, the test result of the subjective test, the measurement result of the objective measurement, the image data of the tomographic image, the image data of the fundus image, and the eye information to be inspected. The eye test information includes information about the subject such as the patient ID and name, and information about the test eye such as left eye / right eye identification information. In addition, various programs and data for operating the ophthalmic apparatus are stored in the storage unit 112.

(Calculation processing unit 120)
The arithmetic processing unit 120 includes an eye refractive power calculation unit 121, an image forming unit 122, and a data processing unit 123.

The eye refractive power calculation unit 121 receives a ring image (pattern image) obtained by the image pickup device 59 receiving the return light of the ring-shaped luminous flux (ring-shaped measurement pattern) projected on the fundus Ef by the reflex measurement projection system 6. ) Is analyzed. For example, the eye refractive power calculation unit 121 obtains the position of the center of gravity of the ring image from the brightness distribution in the image in which the obtained ring image is drawn, and obtains the brightness distribution along a plurality of scanning directions extending radially from the center of gravity position. , The ring image is specified from this brightness distribution. Subsequently, the eye refractive power calculation unit 121 obtains an approximate ellipse of the specified ring image, and substitutes the major axis and the minor axis of the approximate ellipse into a known equation to obtain the spherical power S, the astigmatic power C, and the astigmatic axis angle. Find A. Alternatively, the eye refractive power calculation unit 121 can obtain the parameter of the eye refractive power based on the deformation and displacement of the ring image with respect to the reference pattern.

In addition, the eye refractive power calculation unit 121 calculates the corneal refractive power, the corneal astigmatism degree, and the corneal astigmatism axis angle based on the keratling image acquired by the observation system 5. For example, the optical power calculation unit 121 calculates the radius of curvature of the cornea of the strong main meridian and the weak main meridian on the front surface of the cornea by analyzing the keratling image, and calculates the above parameters based on the radius of curvature of the cornea.

The image forming unit 122 forms the image data of the tomographic image of the fundus Ef based on the signal detected by the detector 98. That is, the image forming unit 122 forms the image data of the eye E to be inspected based on the detection result of the interference light LC by the interference optical system. This process includes processing such as filtering and FFT (Fast Fourier Transform), as in the case of the conventional swept source type OCT. The image data acquired in this way is a data set including a group of image data formed by imaging the reflection intensity profile in a plurality of A lines (paths of each measurement light LS in the eye E to be inspected). is there.

In order to improve the image quality, it is possible to superimpose (add and average) a plurality of data sets collected by repeating scanning with the same pattern a plurality of times.

The data processing unit 123 performs various data processing (image processing) and analysis processing on the tomographic image formed by the image forming unit 122. For example, the data processing unit 123 executes correction processing such as image brightness correction and dispersion correction. In addition, the data processing unit 123 performs various image processing and analysis processing on the image (anterior eye portion image and the like) obtained by using the observation system 5.

The data processing unit 123 can form volume data (voxel data) of the eye E to be inspected by executing known image processing such as interpolation processing for interpolating pixels between tomographic images. When displaying an image based on volume data, the data processing unit 123 performs rendering processing on the volume data to form a pseudo three-dimensional image when viewed from a specific line-of-sight direction.

(Display unit 170, operation unit 180)
As a user interface unit, the display unit 170 displays information under the control of the control unit 110. The display unit 170 includes the display unit 10 shown in FIG. 1 and the like.

The operation unit 180 is used as a user interface unit to operate the ophthalmic apparatus. The operation unit 180 includes various hardware keys (joysticks, buttons, switches, etc.) provided in the ophthalmic apparatus. Further, the operation unit 180 may include various software keys (buttons, icons, menus, etc.) displayed on the touch panel type display screen 10a.

At least a part of the display unit 170 and the operation unit 180 may be integrally configured. A typical example thereof is a touch panel type display screen 10a.

(Communication unit 190)
The communication unit 190 has a function for communicating with an external device (not shown). The communication unit 190 may be provided in, for example, the processing unit 9. The communication unit 190 has a configuration according to a form of communication with an external device.

The VCS lens 46 is an example of the "optical element" according to this embodiment. The optotype projection system 4 is an example of the “awareness test optical system” according to this embodiment. The OCT optical system 8 is an example of the “interference optical system” according to this embodiment. The dichroic mirror 81 is an example of the “first optical path coupling member” according to this embodiment. The focusing lens 43 is an example of the “first focusing lens” according to this embodiment. The focusing lens 82 is an example of the “second focusing lens” according to this embodiment. The reflex measurement projection system 6, the reflex measurement light receiving system 7, and a part of the observation system 5 (half mirror 76, imaging lens 58, and imaging element 59) are examples of the “objective measurement optical system” according to this embodiment. .. The dichroic mirror 69 is an example of the "second optical path coupling member" according to this embodiment.

[Operation example]
An operation example of the ophthalmic apparatus according to this embodiment will be described.

FIG. 5 shows a flow chart of an operation example of the ophthalmic apparatus according to this embodiment.

(S1)
After the face of the subject is fixed by the face receiving portion, the head portion is moved to the inspection position of the eye E to be inspected by the XY alignment by the XY alignment system 2 and the Z alignment by the Z alignment system 1. The examination position is a position where the examination of the eye E to be inspected can be performed. For example, the processing unit 9 (control unit 110) acquires an image pickup signal of the front eye portion image formed on the image pickup surface of the image pickup element 59, and displays the front eye on the display unit 170 (display screen 10a of the display unit 10). Display the part image E'. After that, the head portion is moved to the inspection position of the eye E to be inspected by the above-mentioned XY alignment and Z alignment. The movement of the head unit is executed by the control unit 110 according to the instruction by the control unit 110, but may be executed by the control unit 110 according to an operation or instruction by the user.

Further, the control unit 110 interlocks the reflex measurement light source 61, the focusing lens 74, and the focusing lens 43 to move them to the origin, for example, a position corresponding to 0D along the optical axis.

(S2)
The control unit 110 causes the liquid crystal panel 41 to display the fixation target. As a result, the eye E to be inspected is gazed at a desired fixation position.

(S3)
Next, the control unit 110 executes objective measurement. That is, the control unit 110 projects a ring-shaped light beam onto the fundus Ef of the eye E to be inspected by the reflex measurement projection system 6, and produces a ring image based on the return light detected by the image pickup element 59 through the reflex measurement light receiving system 7 as an ocular refractive force. Let the calculation unit 121 analyze it. The eye refractive power calculation unit 121 obtains the spherical power S, the astigmatic power C, and the astigmatic axis angle A as described above. In the control unit 110, the calculated spherical power S and the like are stored in the storage unit 112.

Further, the control unit 110 can execute the kerato measurement before the reflex measurement or after the reflex measurement. In this case, the control unit 110 turns on the keratling light source 32 and causes the eye refractive power calculation unit 121 to analyze the keratling image detected by the image sensor 59. The eye refractive power calculation unit 121 calculates the corneal radius of curvature by analyzing the keratling image as described above, and calculates the corneal refractive power, the corneal astigmatism degree, and the corneal astigmatism axis angle from the calculated corneal radius of curvature. In the control unit 110, the calculated corneal refractive power and the like are stored in the storage unit 112.

(S4)
Next, the control unit 110 executes a subjective test. First, the control unit 110 controls the focusing lens 43 and the VCS lens 46 so that the spherical power S, the astigmatic power C, and the astigmatic axis angle A obtained in S3 are corrected. Next, the control unit 110 controls the liquid crystal panel 41 based on, for example, a user's instruction to the operation unit 180 to display a desired optotype. The subject responds to the optotype projected on the fundus Ef. For example, in the case of a visual acuity measurement target, the visual acuity value of the eye to be examined is determined by the response of the subject. The selection of the optotype and the response of the subject to it are repeatedly performed at the discretion of the examiner or the control unit 110. The examiner or the control unit 110 determines the visual acuity value or the prescription value (S, C, A) based on the response from the examinee.

(S5)
The control unit 110 determines whether or not to take a tomographic image. For example, the control unit 110 determines whether or not to take a tomographic image based on a user's operation or instruction to the operation unit 180. At this time, the objective measurement result obtained in S3 and the subjective examination result obtained in S4 are displayed on the display unit 170, and information for assisting the user in determining whether or not to take a tomographic image is provided. It is possible. When it is determined that the tomographic image is to be taken (S5: Y), the operation of the ophthalmologic apparatus shifts to S6. When it is determined not to take a tomographic image (S5: N), the operation of the ophthalmologic apparatus ends (end).

Further, the control unit 110 can control the ophthalmic apparatus so as to automatically take a tomographic image based on at least one of the objective measurement result obtained in S3 and the subjective examination result obtained in S4. Is.

(S6)
When it is determined in S5 that the tomographic image is to be taken (S5: Y), the control unit 110 causes the OCT optical system 8 to scan a predetermined portion of the fundus Ef with the measurement light, and causes the arithmetic processing unit 120 to scan the predetermined portion of the fundus Ef with the measurement light. Form a tomographic image. This completes the operation of the ophthalmic device (end).

For example, the portion where the ring-shaped luminous flux is projected in the objective measurement in S3 is scanned with the measurement light, and the obtained tomographic image of the portion is displayed on the display unit 170. As a result, the examiner or the like can observe the tomographic image of the measurement site on which the ring-shaped luminous flux is projected, so that it becomes possible to confirm the reliability of the objective measurement result acquired in S3, and S3. It is possible to improve the accuracy of the objective measurement result in.

For example, the display unit 170 displays a tomographic image of a portion in the vicinity of the macula obtained by scanning the vicinity of the macula of the eye E to be inspected with measurement light. In this case, since the examiner or the like can observe the tomographic image of the portion near the macula, it becomes possible to confirm the reliability of the subjective test result acquired in S4, and the subjective test result in S4. The accuracy can be improved.

<< First modification >>
The configuration of the optical system of the ophthalmic apparatus according to the embodiment is not limited to the configuration described in FIGS. 1 and 2.

6 and 7 show a configuration example of the optical system of the ophthalmic apparatus according to the first modification of the embodiment. In FIG. 6, the same parts as those in FIG. 1 are designated by the same reference numerals, and the description thereof will be omitted as appropriate. In FIG. 7, the same parts as those in FIG. 6 are designated by the same reference numerals, and the description thereof will be omitted as appropriate. Hereinafter, the configuration of the optical system of the ophthalmic apparatus according to the first modification will be described focusing on the differences from the configuration of the optical system of the ophthalmic apparatus according to the embodiment.

The configuration of the optical system of the ophthalmic apparatus according to the first modification of the embodiment is different from the configuration of the optical system of the ophthalmic apparatus according to the embodiment in the configuration of the optical scanner 84 in the OCT optical system 8. Specifically, a reflection mirror 85, relay lenses 87A and 87B are arranged between the galvano mirror 84Y and the galvano mirror 84X. The galvano mirror 84X is arranged at the focal position on the upstream side of the relay lens 87B. The galvano mirror 84Y is arranged at the focal position on the downstream side of the relay lens 87A. The reflection mirror 85 is arranged so as to guide the measurement light LS deflected by the galvano mirror 84X to the galvano mirror 84Y. As shown in FIG. 7, each of the galvano mirror 84Y and the galvano mirror 84X is arranged at a position optically conjugate with the pupil of the eye E to be inspected (pupil conjugate position Q).

The measurement light LS converted into a parallel luminous flux by the collimating lens 86 is deflected by the galvanometer mirror 84X so as to scan the fundus Ef in the X direction. The measurement light LS deflected by the galvano mirror 84X passes through the relay lenses 87B and 87A and is deflected by the reflection mirror 85. The measurement light LS deflected by the reflection mirror 85 is deflected by the galvano mirror 84Y so as to scan the fundus Ef in the Y direction.

Since the operation of the ophthalmic apparatus according to the first modification of the embodiment is the same as the operation of the ophthalmic apparatus according to the embodiment, the description thereof will be omitted.

According to the first modification, since both the galvanometer mirrors 84X and 84Y are arranged at the pupil conjugate position Q, it is possible to detect the interference light with a higher lateral resolution than that of the embodiment. Further, since the galvanometer mirrors 84X and 84Y are arranged at optically conjugate positions, the intensity of the interference signal is increased while maintaining the conjugate relationship even when the focusing lens 82 is moved, and a higher image quality tomographic image is obtained. Can be obtained.

<< Second modification >>
In the optical system of the ophthalmic apparatus according to the embodiment or the first modification thereof, the case where the measurement light LS is deflected by the galvanometer mirrors 84X and 84Y has been described, but the configuration of the ophthalmic apparatus according to the embodiment is not limited to this. Absent.

8 and 9 show a configuration example of the optical system of the ophthalmic apparatus according to the second modification of the embodiment. In FIG. 8, the same parts as those in FIG. 1 are designated by the same reference numerals, and the description thereof will be omitted as appropriate. In FIG. 9, the same parts as those in FIG. 8 are designated by the same reference numerals, and the description thereof will be omitted as appropriate. Hereinafter, the configuration of the optical system of the ophthalmic apparatus according to the second modification of the embodiment will be described focusing on the difference from the configuration of the optical system of the ophthalmic apparatus according to the embodiment.

The configuration of the optical system of the ophthalmic apparatus according to the second modification of the embodiment is different from the configuration of the optical system of the ophthalmic apparatus according to the embodiment in that an image rotator 89 is provided instead of the optical scanner 84. .. The image rotator 89 is arranged on the optical axis of the OCT optical system 8 and is rotatably provided about the optical axis. The optical axes of the optical fiber f2 and the collimating lens 86 are arranged so as to intersect the optical axes of the image rotator 89. As shown in FIG. 9, the focusing lens 82 is moved so that the fiber end face of the optical fiber f2 is arranged at a position optically conjugate with the fundus Ef of the eye E to be inspected (fundus conjugate position P). The image rotator 89 is arranged at a position optically conjugate with the pupil of the eye E to be inspected (pupil conjugate position Q).

The image rotator 89 is rotated about the optical axis of the OCT optical system 8 by a rotation mechanism (not shown). This rotation mechanism receives control from the processing unit 9 and rotates the image rotator 89. The measurement light LS converted into a parallel luminous flux by the collimating lens 86 is deflected in a circle by the rotated image rotator 89. The measurement light LS deflected by the image rotator 89 is deflected toward the focusing lens 82 by the reflection mirror 83.

For example, by tilting the optical fiber f2 or the like so as to have the same magnitude as the ring-shaped luminous flux projected on the fundus Ef, the projection position of the ring-shaped luminous flux on the fundus Ef can be scanned by the measurement light LS. .. Thereby, a tomographic image at the projection position of the ring-shaped luminous flux on the fundus Ef can be acquired. A mechanism for changing the tilt angle of the optical fiber f2 or the like with respect to the optical axis of the image rotator 89 may be provided, and the tilt angle of the optical fiber f2 or the like may be adjusted by control from the processing unit 9.

In the processing system of the ophthalmic apparatus according to the second modification, the rotation control for the image rotator 89 is possible as described above. For example, the main control unit 111 rotates the image rotator 89 by controlling the rotation mechanism.

According to the second modification, the fundus Ef of the eye E to be inspected can be scanned in a circle with the measurement light LS with a simple configuration. As a result, it is possible to acquire a tomographic image of the measurement site on which the ring-shaped luminous flux is projected in objective measurement with a simple configuration, so it is possible to confirm the reliability of the objective measurement result and the accuracy of the objective measurement result. Can be improved.

<Ophthalmic examination system>
The ophthalmologic apparatus according to the embodiment or a modification thereof can be applied to an ophthalmologic examination system capable of examining both eyes.

FIG. 10 is a block diagram of a configuration example of an ophthalmic examination system to which an ophthalmic apparatus according to an embodiment or a modified example thereof is applied.

The ophthalmologic examination system includes a measuring head 300. The measurement head 300 is suspended from above by a holding portion 350 supported by a support member (not shown). The measuring head 300 includes a moving mechanism 310, a left inspection unit 320L, and a right inspection unit 320R. Each of the left inspection unit 320L and the right inspection unit 320R is formed with an optometry window (not shown). The left eye of the subject (the left eye to be examined) is examined through an optometry window provided in the left examination unit 320L. The right eye of the subject (right eye to be examined) is examined through an eye examination window provided in the right examination unit 320R.

The left inspection unit 320L and the right inspection unit 320R are three-dimensionally moved by the moving mechanism 310 independently or in conjunction with each other. At least one of the left inspection unit 320L and the right inspection unit 320R is provided with an ophthalmic apparatus according to an embodiment or a modification thereof.

The moving mechanism 310 includes a horizontal moving mechanism 311L, 311R, a rotating mechanism 312L, 312R, and a vertical moving mechanism 313L, 313R.

The horizontal movement mechanism 311L moves the rotation mechanism 312L, the vertical movement mechanism 313L, and the left inspection unit 320L in the horizontal direction (horizontal direction (X direction), front-back direction (Z direction)). Thereby, the horizontal position of the optometry window can be adjusted according to the arrangement position of the left optometry. The horizontal motion mechanism 311L has a known configuration using, for example, a driving means or a driving force transmitting means for transmitting a driving force generated by the driving means, and receives a control signal from a control device (not shown) to be a rotating mechanism. Move 312L or the like in the horizontal direction. The horizontal movement mechanism 311L can be operated by an operator to manually move the rotation mechanism 312L and the like in the horizontal direction.

The horizontal movement mechanism 311R moves the rotation mechanism 312R, the vertical movement mechanism 313R, and the right inspection unit 320R in the horizontal direction. Thereby, the horizontal position of the optometry window can be adjusted according to the arrangement position of the right optometry. The horizontal movement mechanism 311R has the same configuration as the horizontal movement mechanism 311L, and moves the rotation mechanism 312R and the like in the horizontal direction in response to a control signal from a control device (not shown). The horizontal movement mechanism 311R can be operated by an operator to manually move the rotation mechanism 312R and the like in the horizontal direction.

The rotation mechanism 312L rotates the vertical movement mechanism 313L and the left inspection unit 320L around a rotation shaft (left rotation shaft) for the left eye extending in the vertical direction (substantially vertical direction). The angle formed by the rotating shaft and the horizontal plane can be changed. The rotating mechanism 312L has a known configuration using, for example, a driving means or a driving force transmitting means for transmitting a driving force generated by the driving means, and receives a control signal from a control device (not shown) to rotate the rotating mechanism 312L. The left inspection unit 320L or the like is rotated around the shaft. The rotation mechanism 312L can also be operated by an operator to manually rotate the left inspection unit 320L or the like around the rotation shaft.

The rotation mechanism 312R rotates the vertical movement mechanism 313R and the right inspection unit 320R around a rotation shaft (right rotation shaft) for the right eye extending in the vertical direction. The angle formed by the rotating shaft and the horizontal plane can be changed. The rotation shaft for the right eye is a shaft arranged at a position separated by a predetermined distance from the rotation shaft for the left eye. The distance between the rotation axis for the left eye and the rotation axis for the right eye is adjustable. The rotation mechanism 312R has the same configuration as the rotation mechanism 312L, and rotates the right inspection unit 320R or the like around the rotation axis in response to a control signal from a control device (not shown). The rotation mechanism 312R can also be operated by an operator to manually rotate the right inspection unit 320R or the like around the rotation shaft.

By rotating the left inspection unit 320L and the right inspection unit 320R by the rotation mechanism 312L and 312R, the orientations of the left inspection unit 320L and the right inspection unit 320R can be relatively changed. For example, the left inspection unit 320L and the right inspection unit 320R are rotated in opposite directions around the eye rotation points of the left and right eyes of the subject. As a result, the eye to be inspected can be congested.

The vertical movement mechanism 313L moves the left inspection unit 320L in the vertical direction (vertical direction, Y direction). Thereby, the position of the optometry window in the height direction can be adjusted according to the arrangement position of the optometry. The vertical movement mechanism 313L has a known configuration using, for example, a driving means or a driving force transmitting means for transmitting the driving force generated by the driving means, and receives a control signal from a control device (not shown) to receive a left inspection unit. Move 320L in the vertical direction. The vertical movement mechanism 313L can also be operated by the operator to manually move the left inspection unit 320L in the vertical direction.

The vertical movement mechanism 313R moves the right inspection unit 320R in the vertical direction. Thereby, the position of the optometry window in the height direction can be adjusted according to the arrangement position of the optometry. The vertical movement mechanism 313R may move the right inspection unit 320R in conjunction with the movement by the vertical movement mechanism 313L, or may move the right inspection unit 320R independently of the movement by the vertical movement mechanism 313L. The vertical movement mechanism 313R has the same configuration as the vertical movement mechanism 313L, and moves the right inspection unit 320R in the vertical direction in response to a control signal from a control device (not shown). The vertical movement mechanism 313R can also be operated by the operator to manually move the right inspection unit 320R in the vertical direction.

The left inspection unit 320L and the right inspection unit 320R can operate individually.

According to such an ophthalmologic examination system, subjective examinations and objective measurements can be easily performed on both eyes.

(Action / effect)
The operation and effect of the ophthalmic apparatus and the ophthalmic examination system according to the embodiment will be described.

The ophthalmic apparatus according to the embodiment includes an objective lens (objective lens 51), a subjective examination optical system (objective projection system 4), and an interference optical system (OCT optical system 8). The subjective test optical system includes an optical element (VCC lens 46) capable of correcting aberrations of the eye to be inspected, and projects an optotype onto the eye to be inspected (eye to be inspected E) via an objective lens and an optical element. The interference optical system divides the light (light L0) from the light source (OCT light source 91) into a reference light (reference light LR) and a measurement light (measurement light LS), and provides the eye to be inspected via an objective lens and an optical element. The measurement light is irradiated, interference light (interference light LC) between the return light and the reference light is generated, and the generated interference light is detected.

According to such a configuration, the measurement light can be irradiated to the eye to be inspected through the objective lens common to the subjective examination optical system, and the return light can be detected. Therefore, the subjective examination and the optical coherence tomography can be performed with a simple configuration. It enables photography and measurement using graphics. In particular, since the measurement light can be applied to the eye to be inspected through an optical element capable of correcting the aberration of the eye to be inspected, the optical element can be controlled so as to correct the astigmatic state of the eye to be inspected separately acquired. It is possible. As a result, the measurement light irradiated to the eye to be inspected through the optical element can be more easily converged to one point at the measurement site, and the interference signal based on the detection result of the interference light can be acquired with sufficient intensity with the optimum lateral resolution. Become.

Further, in the ophthalmic apparatus according to the embodiment, the interference optical system is arranged in the optical path of the awareness inspection optical system on the upstream side of the optical element, and the first optical path that couples the optical path of the interference optical system with the optical path of the awareness inspection optical system. A coupling member (dycroic mirror 81) may be included.

According to such a configuration, since the optical path of the interference optical system is coupled to the optical path of the subjective inspection optical system by the first optical path coupling member, the configuration of the optical system is simplified as compared with the case where a perforated prism is used. It is possible to improve the degree of freedom in the design of the optical system. In addition, it becomes easy to add another optical system, and the configuration can be expanded.

Further, in the ophthalmic apparatus according to the embodiment, the subjective examination optical system may include a pupil lens (pupil lens 45) arranged between the optical element and the first optical path coupling member.

According to such a configuration, since the optical path of the interference optical system and the optical path of the subjective examination optical system are coupled on the upstream side of the pupil lens 45, it is possible to bring the position conjugate to the fundus close to the fundus. , The interference optical system and the subjective inspection optical system can be made smaller.

Further, in the ophthalmic apparatus according to the embodiment, the subjective examination optical system includes a first focusing lens (focusing lens 43) that changes the focal position of the subjective examination optical system, and the first optical path coupling member is a pupil lens. It may be arranged between the first focusing lens and the first focusing lens.

According to such a configuration, the focal position of the subjective inspection optical system can be changed regardless of the interference optical system.

Further, in the ophthalmic apparatus according to the embodiment, the interference optical system is arranged between the first optical path coupling member and the light source, and the second focusing lens (focusing lens 82) that changes the focal position of the interference optical system. May include.

According to such a configuration, the focal position of the interference optical system can be changed regardless of the subjective inspection optical system. Thereby, the focal position can be changed to the optimum position for each of the subjective inspection optical system and the interference optical system. For example, while changing the focal position of the subjective examination optical system with the first focusing lens, the focal position of the interfering optical system can be adjusted to an arbitrary part such as the anterior segment of the eye to be inspected or the choroid with the second focusing lens. it can.

Further, the ophthalmic apparatus according to the embodiment may include an objective measurement optical system and an ocular refractive force calculation unit. The objective measurement optical system irradiates the fundus (fundus Ef) of the eye to be inspected with a ring-shaped measurement pattern via an objective lens, and detects the return light from the fundus. The eye refractive power calculation unit obtains the refractive power of the eye to be inspected by analyzing a pattern image based on the return light detected by the objective measurement optical system. The objective measurement optical system is arranged between the objective lens and the optical element, and includes a second optical path coupling member (dichroic mirror 69) that connects the optical path of the objective measurement optical system to the optical path of the subjective inspection optical system.

According to such a configuration, objective measurement is performed through an objective lens common to the subjective inspection optical system, so that the subjective inspection, imaging and measurement using optical coherence tomography and objective measurement are performed with a simple configuration. Measurement becomes possible.

Further, in the ophthalmic apparatus according to the embodiment, the interference optical system includes an image rotator (image rotator 89) which is arranged on the optical axis of the interference optical system and is rotatably arranged around the optical axis to deflect the measurement light. It may be.

According to such a configuration, the measurement light can be deflected with a simple configuration and control.

Further, in the ophthalmic apparatus according to the embodiment, the interfering optical system includes an optical fiber (optical fiber f2) that guides the measurement light and a collimating lens (collimating lens 86) that converts the measurement light emitted from the exit end of the optical fiber into a parallel light beam. The image rotator may deflect the measurement light as a parallel light beam by the collimating lens, and the optical fiber and the collimating lens may be arranged so that their optical axes intersect the optical axis of the image rotator.

According to such a configuration, it is possible to scan the site of the eye to be inspected on which the ring-shaped measurement pattern is projected in a circle shape with the measurement light with a simple configuration, and acquire a tomographic image of the site. .. Thereby, the reliability of the objective measurement result can be improved.

The ophthalmologic examination system according to the embodiment includes a left examination unit (left examination unit 320L) for inspecting the left eye to be inspected and a right examination unit (right examination unit 320R) for inspecting the right eye to be inspected. At least one of the left and right optometry units includes the ophthalmic apparatus described in any of the above.

According to such a configuration, it is possible to provide an ophthalmologic examination system capable of performing subjective examination and imaging and measurement using optical coherence tomography for both eyes with a simple configuration.

(Other variants)
The embodiments shown above are merely examples for carrying out the present invention. A person who intends to carry out the present invention can make arbitrary modifications, omissions, additions, etc. within the scope of the gist of the present invention.

In the above embodiment or a modification thereof, the dichroic mirror 81 is arranged between the relay lens 44 and the focusing lens 43 in the optotype projection system 4, but the dichroic mirror 81 is the focusing lens 43 and the relay lens 42. It may be arranged between and. In this case, after the focal position of the optotype projection system 4 and the OCT optical system 8 is changed by the focusing lens 43, the focal position of the OCT optical system 8 can be finely adjusted by the focusing lens 82.

In the above embodiment or a modification thereof, an image rotator that can rotate about the optical axis of the OCT optical system 8 may be provided instead of the galvanometer mirror 84Y.

In the above embodiment or a modification thereof, the interference optical system has been described as performing OCT imaging, but measurement may be performed by OCT. For example, the interference optical system may measure the axial length, corneal pressure, anterior chamber depth, lens thickness, and the like by OCT.

The above-described embodiment for an apparatus having an arbitrary function that can be used in the ophthalmic field, such as an intraocular pressure measurement function, a fundus photography function, an anterior ocular segment imaging function, an optical coherence tomography (OCT) function, and an ultrasonic examination function. It is possible to apply the invention according to. The intraocular pressure measurement function is realized by a tonometer or the like, the fundus photography function is realized by a fundus camera or a scanning ophthalmoscope (SLO) or the like, the anterior ocular segment imaging function is realized by a slit lamp or the like, and the OCT function is optical. It is realized by an interference tomometer or the like, and the ultrasonic inspection function is realized by an ultrasonic diagnostic apparatus or the like. It is also possible to apply the present invention to a device (multifunction device) having two or more of such functions.

4 Objective projection system 5 Observation system 6 Ref measurement projection system 7 Ref measurement Light receiving system 8 OCT optical system 46 VCS lens 51 Objective lens 81 Dichroic mirror

Claims (6)

With the objective lens
A subjective test optical system that includes an optical element capable of correcting aberrations of the eye to be inspected and projects an optotype onto the eye to be inspected using visible light through the objective lens and the optical element.
The infrared light from the light source is divided into a reference light and a measurement light, the measurement light is irradiated to the eye to be inspected through the objective lens and the optical element, and the return light and the interference light between the reference light are emitted. An interfering optical system that is generated and detects the generated interfering light,
An objective measurement optical system that irradiates the fundus of the eye to be inspected with a ring-shaped measurement pattern using infrared light through the objective lens and detects return light from the fundus.
An optical power calculation unit that obtains the refractive power of the eye to be inspected by analyzing a pattern image based on the return light detected by the objective measurement optical system.
Including
The interference optical system includes a first optical path coupling member that is arranged in the optical path of the awareness inspection optical system on the upstream side of the optical element and that couples the optical path of the interference optical system to the optical path of the awareness inspection optical system.
The objective measurement optical system is arranged between the objective lens and the optical element, and is a second optical path coupling member that couples the optical path of the objective measurement optical system to the optical path coupled by the first optical path coupling member. only including,
The subjective examination optical system including a pupil lens disposed between the optical element and the first optical path coupling member, ophthalmic devices. The subjective inspection optical system includes a first focusing lens that changes the focal position of the subjective inspection optical system.
The ophthalmic apparatus according to claim 1 , wherein the first optical path coupling member is arranged between the pupil lens and the first focusing lens. The second aspect of claim 2 , wherein the interference optical system includes a second focusing lens which is arranged between the first optical path coupling member and the light source and changes the focal position of the interference optical system. Ophthalmic device. Claims 1 to 3 include an image rotator that is arranged on the optical axis of the interference optical system, is rotatably arranged around the optical axis, and deflects the measurement light. The ophthalmic apparatus according to any one of the above. With the objective lens
A subjective test optical system that includes an optical element capable of correcting aberrations of the eye to be inspected and projects an optotype onto the eye to be inspected using visible light through the objective lens and the optical element.
The infrared light from the light source is divided into a reference light and a measurement light, the measurement light is irradiated to the eye to be inspected through the objective lens and the optical element, and the return light and the interference light between the reference light are emitted. An interfering optical system that is generated and detects the generated interfering light,
An objective measurement optical system that irradiates the fundus of the eye to be inspected with a ring-shaped measurement pattern using infrared light through the objective lens and detects return light from the fundus.
An optical power calculation unit that obtains the refractive power of the eye to be inspected by analyzing a pattern image based on the return light detected by the objective measurement optical system.
Including
The interference optical system is
A first optical path coupling member arranged in the optical path of the subjective inspection optical system on the upstream side of the optical element and coupling the optical path of the interference optical system to the optical path of the subjective inspection optical system.
An image rotator arranged on the optical axis of the interference optical system, rotatably arranged around the optical axis, and deflecting the measurement light.
An optical fiber that guides the measurement light and
A collimating lens that converts the measurement light emitted from the emission end of the optical fiber into a parallel luminous flux, and
Including
The objective measurement optical system is arranged between the objective lens and the optical element, and is a second optical path coupling member that couples the optical path of the objective measurement optical system to the optical path coupled by the first optical path coupling member. Including
The image rotator deflects the measurement light, which is converted into a parallel luminous flux by the collimating lens.
The optical fiber and the collimating lens, the optical axis is arranged to intersect with the optical axis of the image rotator, ophthalmic devices. A left inspection unit for inspecting the left eye and
The right inspection unit for inspecting the right eye,
Including
An ophthalmologic examination system comprising the ophthalmic apparatus according to any one of claims 1 to 5 , wherein at least one of the left examination unit and the right examination unit includes the ophthalmic apparatus according to any one of claims 1 to 5.

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