WO2023054612A1

WO2023054612A1 - Ophthalmic device

Info

Publication number: WO2023054612A1
Application number: PCT/JP2022/036514
Authority: WO
Inventors: 健志中村; 浩二濱口; 城久小林; 祐輝小嶋; 健治青木
Original assignee: 株式会社ニデック
Priority date: 2021-09-30
Filing date: 2022-09-29
Publication date: 2023-04-06

Abstract

The present invention addresses the technical problem of providing an ophthalmic device that is capable of efficiently measuring ocular refractive power, intraocular pressure, and ocular axial length. The present disclosure relates to an ophthalmic device that examines an eye, said ophthalmic device being characterized by comprising: an ocular refractive power measurement means for measuring the ocular refractive power of the eye being examined; an intraocular pressure measurement means for measuring the intraocular pressure of the eye being examined; and an ocular axial length measurement means for measuring the ocular axial length of the eye being examined. Thus, it is possible to provide an ophthalmic device that is capable of efficiently measuring ocular refractive power, intraocular pressure, and ocular axial length.

Description

ophthalmic equipment

The present disclosure relates to an ophthalmic apparatus for examining an eye to be examined.

Known conventional ophthalmic devices include an ophthalmic device that measures eye refractive power and intraocular pressure, and an ophthalmic device that measures eye refractive power and eye axial length. An ophthalmic device that measures eye refractive power and intraocular pressure is used for screening such as health checkups.

JP-A-2008-99968

In general, the results of measuring the axial length of the eye are often used to calculate the IOL power during cataract surgery. Measurements of ocular refractive power and axial length are increasingly being performed.

However, in the conventional ophthalmologic apparatus, a device for measuring eye refractive power and intraocular pressure and a device for measuring eye refractive power and eye axial length exist separately. could not be measured effectively.

In view of the above circumstances, the technical problem of the present disclosure is to provide an ophthalmologic apparatus capable of efficiently measuring eye refractive power, intraocular pressure, and axial length.

(1) An ophthalmologic apparatus for examining an eye to be inspected, comprising eye refractive power measuring means for measuring the eye refractive power of the eye to be inspected, intraocular pressure measuring means for measuring the intraocular pressure of the eye to be inspected, and an axial length measuring means for measuring the axial length of the eye to be examined.

1 is an external view of an ophthalmologic apparatus; FIG. 3 is a block diagram showing a control system; FIG. It is a schematic diagram showing the optical system of the first measurement unit. It is a schematic diagram showing an internal configuration of a second measurement unit. It is a schematic diagram showing the optical system of the second measurement unit. 4 is a flow chart showing the control operation of the ophthalmologic apparatus; It is a schematic diagram showing the optical system of the first measurement unit in the second embodiment. 9 is a flow chart showing the control operation of the ophthalmologic apparatus in the second embodiment; It is a figure which shows an example of an anterior-segment cross-sectional image. It is a schematic diagram for demonstrating the derivation|leading-out method of eye axial length.

<Embodiment>
Embodiments of the present disclosure will be described. An ophthalmologic apparatus (for example, an ophthalmologic apparatus 1) of this embodiment is an apparatus for examining an eye to be examined. The ophthalmologic apparatus includes, for example, an eye refractive power measurement unit (e.g., first measurement optical system 100), an intraocular pressure measurement unit (e.g., fluid ejection unit 200, deformation detection optical system 350, etc.), and an eye axial length measurement unit ( For example, an axial length measuring optical system 310) is provided. The eye refractive power measuring unit measures the eye refractive power of the subject's eye. The intraocular pressure measurement unit measures the intraocular pressure of the subject's eye. The axial length measuring unit measures the axial length of the eye to be examined. The ophthalmologic apparatus of this embodiment can efficiently measure the refractive power of the eye, the intraocular pressure, and the axial length of the eye by providing the configuration described above.

Note that the intraocular pressure measurement unit and the axial length measurement unit may share a part of the optical system. For example, the tonometry section and the axial length measurement section may share an observation optical system (for example, the second observation optical system 340) for observing the anterior segment. As a result, the size and cost of the apparatus can be reduced compared to the case where an optical system such as an observation optical system is provided in each of the intraocular pressure measurement unit and the axial length measurement unit.

The working distances of the intraocular pressure measuring unit and the axial length measuring unit may be different. For example, the working distance of the axial length measuring unit may be longer than the working distance of the tonometry unit. That is, the working distance of the intraocular pressure measuring unit may be shorter than the working distance of the axial length measuring unit. As a result, it is possible to reduce the feeling of fear or oppression given to the subject when performing eye axial length measurement and intraocular pressure measurement in succession.

The ophthalmologic apparatus may further include a drive section (eg, drive section 5) and a control section (eg, control section 70). The drive unit three-dimensionally drives the intraocular pressure measurement unit and the axial length measurement unit. The control section controls driving of the driving section. For example, when measuring the intraocular pressure after performing the axial length measurement, the control unit moves the second measuring unit to the eye to be examined so that the working distance of the intraocular pressure measuring unit is reached after the axial length measurement is completed. The driving unit may be controlled so that the intraocular pressure measurement is performed after approaching in the working distance direction. As a result, it is possible to reduce the feeling of fear or oppression given to the subject when performing eye axial length measurement and intraocular pressure measurement in succession.

Note that the control unit may measure the axial length of the eye by the axial length measurement unit after measuring the eye refractive power by the eye refractive power measurement unit. That is, measurements may be performed in order of eye refractive power measurement, eye axial length measurement, and intraocular pressure measurement. As a result, eye refractive power, axial length, and intraocular pressure can be measured more efficiently by performing eye refractive power measurement and eye axial length measurement before intraocular pressure measurement, which tends to cause misalignment due to movement of the subject after measurement. can be measured.

The ophthalmologic apparatus may include a corneal shape measuring unit (eg, first observation optical system 150, first target optical system 160, etc.) that measures the corneal shape of the subject's eye. As a result, in addition to eye refractive power measurement, intraocular pressure measurement, and eye axial length measurement, corneal shape measurement of the subject's eye can also be efficiently performed.

<Example>
[exterior]
An embodiment of the present disclosure will be described. An ophthalmologic apparatus 1 of this embodiment is an apparatus for measuring an eye to be examined. As shown in FIG. 1, the ophthalmologic apparatus 1 includes, for example, a measurement unit 3 that measures an eye to be examined. The measurement unit 3 includes a first measurement unit 3a and a second measurement unit 3b.

The first measuring unit 3a functions, for example, as eye refractive power measuring means for measuring the eye refractive power of the subject's eye. The second measuring unit 3b functions, for example, as an axial length measuring device for measuring the axial length of the subject's eye and an intraocular pressure measuring device for measuring the intraocular pressure of the subject's eye. In the second measurement unit 3b, the optical system for measuring the axial length and the optical system for measuring the intraocular pressure are partly shared (shared). Note that the first measurement unit 3a may include corneal shape measurement means. In this case, the measurement result of the corneal shape measured by the corneal shape measuring means of the first measuring unit 3a may be used for the eye axial length measurement by the second measuring unit 3b.

In addition, the ophthalmologic apparatus 1 includes a base 2, a drive section 5, a face support section 4, a display section 75, an operation section 76, a control section 70, and the like. The base 2 supports each part of the ophthalmologic apparatus 1 . The drive unit 5 integrally drives the first measurement unit 3a and the second measurement unit 3b. For example, the driving unit 5 moves the first measuring unit 3a and the second measuring unit 3b in three-dimensional directions, up, down, left, right, front and back, with respect to the base. The face support section 4 is used to fix the subject's face in front of the measurement section 3 . The face support part 4 is fixed to the base 2 and supports the subject's face.

The display unit 75 is controlled by the control unit 70 and displays measurement results and the like. For example, the display unit 75 displays the ocular refractive power of the subject's eye, the front image of the anterior segment, the axial length of the eye, the intraocular pressure, and the like on the screen.

The operation unit 76 accepts the operations of the examiner. In addition, when the display unit 75 has a touch panel, the display unit 75 may function as the operation unit 76 .

A control unit (also called a processor) 70 controls various controls of the ophthalmologic apparatus 1 . It also processes various measurement results obtained by the measurement unit 3 . The control unit 70 includes, for example, a general CPU (Central Processing Unit) 71, ROM 72, RAM 73, etc., as shown in FIG. For example, the ROM 72 stores an ophthalmologic apparatus control program for controlling the ophthalmologic apparatus 1, initial values, and the like. For example, the RAM 73 temporarily stores various information. The control unit 70 is connected to each unit of the ophthalmologic apparatus 1 such as the first measurement unit 3a, the second measurement unit 3b, the drive unit 5, the display unit 75, the operation unit 76, the storage unit (for example, nonvolatile memory) 74, and the like. there is The storage unit 74 is, for example, a non-transitory storage medium that can retain stored content even when power supply is interrupted. For example, a hard disk drive, a detachable USB flash memory, or the like may be used as the storage unit 74 .

[First measurement part]
The first measurement unit 3 a includes a first measurement optical system 100 , a first fixation target optical system 130 , a first observation optical system 150 , a first index optical system 160 and a first index optical system 170 . It also has half mirrors 501 and 502, an objective lens 505, etc. for branching and combining the optical paths of the respective optical systems.

(First measurement optical system)
The first measurement optical system 100 objectively measures the eye refractive power of the eye E to be examined. The first measurement optical system 100 has a light projecting optical system 100a and a light receiving optical system 100b.

The projection optical system 100a has a measurement light source 111, and projects a spot-shaped measurement light onto the fundus of the eye E to be examined via the center of the pupil or the apex of the cornea of the eye E to be examined. The measurement light source 111 may be an SLD light source, an LED light source, or other light sources. In this embodiment, infrared light is used as the measurement light. For example, near-infrared light with a peak wavelength between 800 nm and 900 nm may be used. As an example, near-infrared light with a peak wavelength of 870 nm may be used. Of course, light of other wavelengths may be used.

In this embodiment, a prism 115 is arranged on the common path of the light projecting optical system 100a and the light receiving optical system 100b. By rotating the prism 115 around the optical axis, the projection light flux on the pupil is eccentrically rotated at high speed. As an example, in this embodiment, the projection light flux is eccentrically rotated in a region of φ2 mm to φ4 mm on the pupil. This area is the eye refractive power measurement area in this embodiment.

The light receiving optical system 100b has at least a ring lens 123 and an imaging element 124. The light-receiving optical system 100b takes out the reflected light flux of the measurement light flux reflected from the fundus in a ring shape through the periphery of the pupil. The ring lens 123 is arranged at a pupil conjugate position, and the imaging element 124 is arranged at a fundus conjugate position. By analyzing the ring image formed on the image sensor 124 via the ring lens 123, the eye refractive power is derived.

As described above, in this embodiment, the measurement light is eccentrically rotated at high speed on the pupil. Analysis processing is performed on an added image of image data that is sequentially output, and an eye refractive power is derived. In this embodiment, values such as SPH: spherical power, CYL: cylindrical power, and AXIS: astigmatic axis angle are obtained as a result of analysis processing.

It should be noted that the first measurement optical system 100 may have optical elements such as lenses and diaphragms in addition to the measurement light source 111, the prism 115, the ring lens 123, and the imaging element 124. The measurement light flux from the measurement light source 111 passes through the hole portion of the hole mirror 114 and the prism 115, is reflected by the half mirror 116 and the half mirror 117 respectively, becomes coaxial with the optical axis L11, and further passes through the objective lens 118. and reach the fundus. The reflected light flux, which is the measurement light flux reflected by the fundus, passes through the optical path through which the measurement light flux has passed, is reflected by the mirror portion of the hole mirror 114 , and reaches the imaging device 124 via the ring lens 123 .

(First fixation target optical system)
The first fixation target optical system 130 presents the eye E to be examined with a fixation target. The first fixation target optical system 130 causes the subject's eye to fixate, and applies fog and accommodation load to the subject's eye. For example, the first fixation target optical system 130 includes at least a light source 131 and a fixation target plate 132 . The fixation target plate 132 may be placed at a fundus conjugate position. A fixation light beam from the light source 131 passes through the fixation target plate 132 on the optical axis L12, the lens 133, the lens 134, and the half mirror 116, and is reflected by the half mirror 117 to be coaxial with the optical axis L11. . The fixation luminous flux further passes through the objective lens 118 and reaches the fundus.

Note that the measurement light source 111, the ring lens 123, and the imaging element 124 in the first measurement optical system 100, and the light source 131 and the fixation target plate 132 in the first fixation target optical system 130 are the drive unit 140, and the drive unit 141 can move integrally along the optical axis. For example, the focal length within the drive unit 140 in the first measurement optical system 100 and the focal length within the drive unit 140 in the first fixation target optical system 130 are in a predetermined relationship. For example, by moving the drive unit according to the eye refractive power of the eye E to be examined, the presentation distance of the fixation target plate 132 with respect to the eye E to be examined (that is, the presentation position of the fixation target) can be changed. 111 and the imaging device 124 are optically conjugated to the fundus. At this time, regardless of the movement of the driving unit, the hole mirror 114 and the ring lens 123 are pupil conjugate at a constant magnification.

(First observation optical system)
The first observation optical system 150 captures a front image of the anterior segment of the eye E to be examined. For example, the first observation optical system 150 includes an imaging device 151 and the like. The imaging device 151 may be arranged at a pupil conjugate position. The front image is used for alignment and the like. Also, a target image (point image) projected onto the cornea from the first target optical system 160 and a target image (Meyerling image) are captured by the first observation optical system 150 .

(First index optical system)
The first index optical system 160 projects an index onto the subject's eye. The first target optical system 160 is used, for example, for measurement of the corneal shape of the subject's eye, alignment with the subject's eye E, and the like. The first target optical system 160 has a plurality of point light sources 161 and a light source 162 . The point light source 161 projects an infinity index by irradiating the cornea with parallel light. The point light source 161 emits infrared light. However, it may be visible light. The point light sources 161 are arranged vertically and horizontally symmetrically about the optical axis L11. For example, in this embodiment, two point light sources are provided on each side. This projects four point image indices onto the cornea. Note that the shape of the index is not limited to this, and a linear index or the like may be included. Also, the number of indices is not limited to this, and may be composed of three or more point image indices.

The light source 162 projects a finite distance index by irradiating the cornea with diffused light. Light source 162 emits infrared light. However, it may be visible light. The light source 162 is arranged in a ring shape around the optical axis L11. Thereby, in this embodiment, a ring index (so-called Mayer ring) is projected onto the cornea.

In this embodiment, the working distance is adjusted by moving the measurement unit 3 in the front-rear direction so that the Purkinje image by the point light source 161 and the ring index by the light source 162 are photographed at a predetermined ratio.

[Second measurement unit]
As shown in FIG. 4, the second measurement section 3b includes a fluid ejection section 200 and a second measurement optical system 300. As shown in FIG. The fluid ejection unit 200 generates compressed air for measuring intraocular pressure. The second measurement optical system 300 includes an optical system for measuring intraocular pressure and axial length.

{Fluid discharge part}
The fluid ejector 200 ejects fluid onto the cornea of the eye E to be examined. The fluid ejection unit 200 includes, for example, a cylinder 201, a piston 202, a solenoid actuator (hereinafter also referred to as a solenoid) 203, a nozzle 206, a vent pipe 220, a glass plate 208, a glass plate 209, a pressure sensor 212, and the like.

The cylinder 201 and the piston 202 are used as a fluid compression mechanism for compressing fluid such as air to be discharged to the eye to be examined. The cylinder 201 is cylindrical, for example, and is divided into a compression chamber 234 and an intake chamber 235 inside. An intake port 213 is provided on a side surface of the intake chamber 235 . The piston 202 slides along the axial direction (longitudinal direction) of the cylinder 201 . Piston 202 compresses air in compression chamber 234 within cylinder 201 .

The solenoid 203 is, for example, a linear solenoid and operates linearly. The solenoid 203 has a movable body 204 and a coil 205 . A magnetic body such as a permanent magnet is used for the movable body 204, for example. When the coil 205 is energized, a magnetic field is generated inside the coil 205 . The movable body 204 is axially moved by the electromagnetic force received from the magnetic field. Since the piston 202 is fixed to the movable body 204 , it moves axially with the movable body 204 .

Also, by changing the direction of the current flowing through the coil 205, the moving direction of the movable body 204 can be changed. For example, when the current is passed through the coil 205 in the forward direction, the movable body 204 moves in the compression direction (forward direction, direction A in FIG. 4). , direction B in FIG. 4). Therefore, by switching the direction of the current flowing through the coil 205, the moving direction of the piston 202 that moves together with the movable body 204 can be changed. For example, a forward current is applied to the coil 205 to move the piston 202 in the A direction to compress the fluid in the compression chamber 234, and then a reverse current is applied to the coil 205 to move the piston 202 in the B direction. can be returned to the initial position. Note that the solenoid 203 is not limited to a linear solenoid, and may be a rotary solenoid or other drive source.

The nozzle 206 discharges compressed air to the outside of the device. The glass plate 208 is transparent, holds the nozzle 206, and transmits observation light and alignment light. The glass plate 209 constitutes the rear wall of the airtight chamber 221 and transmits observation light and alignment light. The pressure sensor 212 detects the pressure in the airtight chamber 221, for example.

The fluid compressed in the compression chamber 234 in the cylinder 201 by the movement of the piston 202 passes through the vent tube 220 connected to the tip of the cylinder 201 and the airtight chamber 221 that stores the compressed fluid, and flows out from the nozzle 206 to the eye to be examined. E is discharged toward the cornea of E.

{Second measurement optical system}
The second measurement optical system 300 measures the axial length and intraocular pressure of the subject's eye. For example, the second measurement optical system 300 includes an axial length measurement optical system 310, a second fixation target optical system 330, a second observation optical system 340, a second target optical system 390, a deformation detection optical system 350, and a corneal thickness measurement system. An optical system 370 and the like are provided.

(Axial length measurement optical system)
The axial length measuring optical system 310 measures, for example, the axial length of the subject's eye. The axial length measurement optical system 310 of this embodiment is, for example, a time domain type interference optical system. Of course, not only Time-domain OCT (TD-OCT), but also Fourier domain interference optical systems such as Spectral-domain OCT (SD-OCT) and Swept-source OCT (SS-OCT) may be used.

The axial length measurement optical system 310 includes, for example, a light source 311 (eg, SLD), a collimator lens 312, a beam splitter 313, a first triangular prism (corner cube) 314, a second triangular prism 315, and a polarizing beam splitter 316. , a quarter-wave plate 317, a condenser lens 318, a light-receiving element 319, a driving section 320, and the like.

The light source 311 may emit low coherence light, for example. The collimator lens 312 converts the light flux emitted from the light source 311 into a parallel light flux. The beam splitter 313 splits the light emitted from the light source 311 into first split light and second split light. The first triangular prism 314 is arranged in the transmission direction of the beam splitter 313 . A second triangular prism 315 is arranged in the reflection direction of the beam splitter 313 . The condensing lens 318 condenses the measurement light from the subject's eye onto the light receiving element. The light receiving element 319 synthesizes and receives, for example, the first split light reflected by the fundus of the subject's eye and the second split light. The axial length of the subject's eye is measured based on the light receiving signal output from the light receiving element 319 .

The first triangular prism 314 is used as an optical path length changing member for changing the optical path length, and is linearly moved in the optical axis direction with respect to the beam splitter 313 by driving the driving section 320 (for example, motor). The drive position of the first triangular prism 314 is detected by a position detection sensor (eg, potentiometer, encoder, etc.).

The light (linearly polarized light) emitted from the light source 311 is collimated by the collimator lens 312 and then split by the beam splitter 313 into the first measurement light (reference light) and the second measurement light. Then, the first measurement light (second split light) is reflected by the first triangular prism 314, and the second measurement light (first split light) is reflected by the second triangular prism 315, and after being folded back , are combined by the beam splitter 313 . The combined light is reflected by the polarizing beam splitter 316 and converted into circularly polarized light by the quarter-wave plate 317 , and then irradiated at least to the cornea and fundus of the subject's eye through the objective lens 302 . At this time, when the measurement light flux is reflected by the cornea and the fundus of the eye to be examined, the phase is converted by 1/2 wavelength.

The cornea-reflected light and fundus-reflected light are converted into linearly polarized light by the quarter-wave plate 317 via the objective lens 302 . After that, the reflected light transmitted through the polarizing beam splitter 316 is condensed by the condensing lens 318 and then received by the light receiving element 319 .

In addition, as shown in FIG. 4, the second measurement optical system 300 is provided under the piston 202. As a result, even with the time domain type axial length measurement optical system 310 as shown in FIG. 5, it is possible to secure a driving space for the moving first triangular prism 314, and the axial length can be disturbed in the same way as with a single device. can be measured without Further, when the second measuring optical system 300 is arranged below the piston 202, the height of the optical axis L21 of the second measuring unit 3b is aligned with the optical axis L11 of the first measuring unit 3a. can get closer. Therefore, the vertical stroke can be made smaller.

(Second fixation target optical system)
The second fixation target optical system 330 presents the fixation target to the subject's eye E from the front direction. The second fixation target optical system 330 has, for example, a visible light source (fixation lamp) 331, a projection lens 332, and a dichroic mirror 333. project to A light source such as an LED or a laser is used for the light source 331 . For the light source 331, for example, a pattern light source such as a point light source, a slit light source, a ring light source, or a two-dimensional display such as a liquid crystal display is used.

The visible light emitted from the light source 331 passes through the projection lens 332, is reflected by the dichroic mirror 333, passes through the objective lens 302, and is projected onto the fundus of the eye E to be examined. As a result, the subject's eye E is fixated on the fixation point in the front direction, and the line-of-sight direction is fixed. The visible light emitted from the light source 331 passes through the projection lens 332 and the objective lens 302 and is converted into a parallel light flux.

(Second observation optical system)
The second observation optical system 340 is arranged to image the anterior segment of the subject's eye. A second observation optical system 340 is provided in the reflection direction of the dichroic mirror 333 and the beam splitter 341 . The dichroic mirror 333 has a characteristic of transmitting the light emitted from the light source 311 and reflecting the infrared light emitted from the light source 381 for illuminating the anterior segment. The second observation optical system 340 includes an imaging lens 342 , a filter 343 and an imaging device (such as a CCD) 344 . The imaging lens 342 converges the reflected light from the subject's eye onto the imaging device 344 . The filter 343 has characteristics of, for example, transmitting light from the

light sources

381 and 391 and not transmitting light from a light source 351 for corneal deformation detection and visible light, which will be described later. The imaging device 344 receives reflected light from the subject's eye. The imaging element 344 outputs the acquired light receiving signal to the control section 70 .

The illumination light from the light source 381 reflected by the eye to be examined passes through the nozzle 206, passes through the objective lens 302, is reflected by the dichroic mirror 333 and the beam splitter 341, and is focused on the imaging device 344 via the imaging lens 342 and filter 343. image. In this way, since the axial length measurement optical system 310 and the second observation optical system 340 are coaxial with the nozzle 206 of the fluid ejection unit, the observation optical system for measuring the axial length and the observation optical system for measuring the intraocular pressure A common system can be used. As a result, the size of the apparatus can be reduced more than when an observation optical system is provided separately.

(Second index optical system)
A second target optical system 390 projects a target onto the eye to be inspected. The second index optical system 390 includes a light source 391, a projection lens 392, and a beam splitter 393, for example. Infrared light projected from a light source 391 through a projection lens 392 is reflected by a beam splitter 393 and projected onto the subject's eye from the front. A corneal bright spot formed at the corneal vertex by the light source 391 forms an image on the imaging device 344 of the second observation optical system 340 and is used for alignment detection in the vertical and horizontal directions.

(Deformation detection optical system)
The deformation detection optical system 350 includes a light projection optical system 350a and a light reception optical system 350b, and is used to detect the deformation state of the cornea Ec.

The light projecting optical system 350a has an optical axis L23 as a light projecting optical axis, and irradiates the cornea Ec of the eye E with illumination light from an oblique direction. The projection optical system 350a has a light source 351, a collimator lens 352, and a beam splitter 353, for example. The light receiving optical system 350b has a photodetector 357 and receives the reflected light of the illumination light from the cornea Ec of the eye E. FIG. The light receiving optical system 350b is arranged substantially symmetrically with the light projecting optical system 350a with respect to the optical axis L21. The light receiving optical system 350b has, for example, a lens 354, a beam splitter 355, a pinhole plate 356, and a photodetector 357, and forms an optical axis L22 as a light receiving optical axis.

Light (for example, infrared light) emitted from the light source 351 is collimated by the collimator lens 352 and reflected by the beam splitter 353. After being reflected by the beam splitter 353, it becomes coaxial (matches) with the optical axis L23 of the light receiving optical system 370b, which will be described later. The light is projected onto the cornea Ec of the eye to be examined. The light reflected by the cornea Ec becomes coaxial (matches) with the optical axis L22 of the projection optical system 370a, which will be described later. Received at 357 . The lens 354 is coated with a coating that is opaque to the light from the

light sources

381 and 391 . The deformation detection optical system 350 is arranged so that the amount of light received by the photodetector 357 is maximized when the subject's eye is in a predetermined deformation state (for example, an applanation state).

The deformation detection optical system 350 also serves as a part of the first working distance detection system 360b, and the projection optical system of the first working distance detection system also serves as the projection optical system 350a of the deformation detection optical system 350. do. The first working distance detection system 360b for receiving the light reflected by the cornea Ec from the light source 351 has, for example, the lens 354 of the projection optical system 350a, the beam splitter 358, the condenser lens 359, and the position detection element 360. An optical axis L22 is formed as an optical axis.

Illumination light projected from the light source 351 and reflected by the cornea Ec forms a target image, which is a virtual image of the light source 351 . The light of the target image passes through a lens 354 and a beam splitter 355, is reflected by a beam splitter 358, passes through a condenser lens 359, and enters a one-dimensional or two-dimensional position detection element 360 such as a PSD or line sensor. do. When the eye E (cornea Ec) moves in the working distance direction (Z direction), the position detection element 360 moves the target image from the light source 351 on the position detection element 360 . Working distance information is obtained based on the output signal of . The output signal from the position detection element 360 of this embodiment is used for alignment (coarse adjustment) in the working distance direction (Z direction). The magnification of the first working distance detection system 360b is not as large as that of the light receiving optical system 370b, which will be described later. Therefore, the distance detection range in the Z direction of the position detection element 360 is wider than that of the light receiving element 377 .

(corneal thickness measurement optical system)
The corneal thickness measuring optical system 370 includes a light projecting optical system 370a and a light receiving optical system 370b, and is used to measure the corneal thickness of the eye E to be examined. The projection optical system 370a also serves as part of the deformation detection optical system 350 and the first working distance detection system 360b.

The light projecting optical system 370a has an optical axis L22 as a light projecting optical axis, and irradiates the cornea Ec of the eye E to be examined with illumination light (measurement light) from an oblique direction. The projection optical system 370a has, for example, a light source 371, a condenser lens 372, a light limiting member 373, a concave lens 374, and a lens 354 that also serves as a deformation detection optical system. A visible light source or an infrared light source (including near-infrared) is used for the light source 371, and for example, a light source such as an LED or a laser is used. The condenser lens 372 collects the light emitted from the light source 371 .

The light limiting member 373 is arranged on the optical path of the light projection optical system 370 a and limits the light emitted from the light source 371 . The light restricting member 373 is arranged at a substantially conjugate position with respect to the cornea Ec. As the light restricting member 373, for example, a pinhole plate, a slit plate, or the like is used. The light restricting member 373 is used as an aperture that allows part of the light emitted from the light source 371 to pass therethrough and blocks other light. Then, the projection optical system 370a forms a predetermined pattern light flux (for example, a spot light flux, a slit light flux) on the cornea of the eye E to be examined.

The light-receiving optical system 370b has a light-receiving element 377, and receives the reflected light of the illumination light from the corneal surface and back surface of the eye E to be examined. The light receiving optical system 370b is arranged substantially symmetrically with the light projecting optical system 370a with respect to the optical axis L21. The light-receiving optical system 370b has, for example, a light-receiving lens 375, a concave lens 376, and a light-receiving element 377, and forms an optical axis L23 as a light-receiving optical axis. The light-receiving optical system 370b in FIG. 5 also serves as a second working distance detection system for detecting the alignment state of the eye E in the Z direction.

The light receiving element 377 has a plurality of photoelectric conversion elements and receives reflected light from the front and back surfaces of the cornea. A photodetection device such as a one-dimensional line sensor, a two-dimensional area sensor, or the like is used for the light receiving element 377, for example. The corneal thickness measurement optical system and the light receiving optical system 370b of the second working distance detection system increase the magnification for observation. Therefore, the distance detection range in the Z direction of the light receiving element 377 is narrower than that of the position detection element 360 .

When the subject's eye E (cornea Ec) moves in the working distance direction (Z direction), the reflected light from the light source 371 on the cornea Ec also moves on the light receiving element 377. Working distance information is obtained based on the output signal from the light receiving element 377 .

The light emitted from the light source 371 is condensed by the condensing lens 372 and illuminates the light restricting member 373 from behind. The light from the light source 371 is imaged (focused) near the cornea Ec by the lens 354 after being restricted by the light restricting member 373 . For example, a pinhole image (when using a pinhole plate) and a slit image (when using a slit plate) are formed near the cornea Ec. At this time, the light from the light source 371 forms an image near the intersection with the visual axis on the cornea Ec.

When the illumination light is projected onto the cornea Ec by the projection optical system 370a, the reflected light of the illumination light from the cornea Ec travels in a direction symmetrical to the projected light flux with respect to the optical axis L21. The reflected light is imaged on the light receiving surface of the light receiving element 377 by the light receiving lens 375 .

[Control action]
In the ophthalmologic apparatus 1 as described above, the control operation during measurement will be described based on the flowchart of FIG.

(S1: first alignment)
First, the control unit 70 aligns the first measurement unit 3a with respect to the eye E to be examined in order to measure the refractive power of the eye. For example, in a state where the first fixation target optical system 130 presents the fixation target to the subject's eye E, the control unit 70 can perform , the eye to be examined E and the first measuring unit 3a are adjusted to a predetermined positional relationship. More specifically, the controller 70 performs alignment in the XY directions such that the optical axis L11 coincides with the corneal vertex of the eye E to be examined. Further, the control unit 70 performs alignment in the Z direction so that the distance between the subject's eye E and the first measuring unit 3a is a predetermined working distance. At this time, the control unit 70 projects an alignment index onto the cornea and adjusts the alignment based on the alignment index detected in the observed image.

(S2: Corneal shape measurement)
Next, the corneal shape of the subject's eye E is measured. The control unit 70 projects a point image index from the first index optical system 160 and captures a corneal Purkinje image of the point image index using the first observation optical system 150 . The control unit 70 also acquires corneal shape information based on the corneal Purkinje image. For example, the corneal shape information is derived based on the image height of the corneal Purkinje image. In this embodiment, at least each value of the corneal curvature, the astigmatic power, and the astigmatic axis angle is acquired as the corneal shape information.

(S3: eye refractive power measurement)
Next, the ocular refractive power of the subject's eye E is measured. For example, in eye refractive power measurement, preliminary measurement may be performed first, and main measurement may be performed later. In the preliminary measurement, the ocular refractive power of the subject's eye E is measured with the fixation target placed at a predetermined presentation distance. At the time of measurement, the fixation target plate 132 may be placed at an initial position that is optically sufficiently far away from the subject's eye E and that corresponds to the far point of the 0D eye. A ring image captured by the imaging device 124 based on the measurement light irradiated in this state is image-analyzed by the control unit 70 . As an analysis result, the refractive power value in each meridian direction is obtained. At least the spherical power in the preliminary measurement is obtained by subjecting the refractive power in each meridional direction to a predetermined process.

Subsequently, the control unit 70 moves the fixation target plate 132 to the fog start position where the subject's eye E is focused, according to the pre-measured spherical power of the subject's eye. As a result, the eye E to be examined can clearly observe the fixation target. Thereafter, the control unit 70 adds fog to the subject's eye E by moving the fixation target from the fog start position. This cancels the adjustment of the eye E to be examined.

The main measurement is performed with fog added to the subject's eye E. By performing a predetermined analysis process on the ring image captured for the subject's eye E to which fog is added, SPSH of the subject's eye E: spherical power, CYL: cylindrical power, AXIS: astigmatism axis angle objective value is retrieved.

(S4: second alignment)
When the measurement by the first measurement unit 3a is completed, the control unit 70 aligns the second measurement unit 3b. For example, the control unit 70 causes the driving unit 5 to move the measuring unit 3 downward from the measurement completion position of the first measuring unit 3a so that the optical axis L21 of the second measuring unit 3b is aligned with the height of the eye to be examined. adjust to Then, the control unit 70 turns on the

light sources

331, 381, and 391 to turn on the light source 331, the light source 381, and the light source 391, and based on the observation image obtained by the second observation optical system 340 in a state in which the subject is fixated, performs the first observation of the subject's eye. 2 Perform XY alignment of the measuring section 3b. Further, the control unit 70 turns on the

light sources

351 and 371 and performs Z alignment based on the light receiving results of the position detection element 360 and the light receiving element 377 .

(S5: Axial length measurement)
The control unit 70 turns on the light source 311 to irradiate the subject's eye with measurement light. The measurement light is reflected by the subject's eye and enters the light receiving element 319 . Further, the control section 70 controls the driving section 320 to reciprocate the first triangular prism 314 . Then, the control unit 70 calculates the eye axial length based on the timing at which the light receiving element 319 detects the interference light.

The movement position of the first triangular prism 314 when the interference signal is output from the light receiving element 319 as described above differs according to the axial length of the subject's eye. The movement position of the first triangular prism 314 when the interference signal is output can be detected based on a signal output from a position detection sensor (not shown). Therefore, the axial length value can be calculated by obtaining in advance the relationship between the moving position of the first triangular prism 314 and the axial length of the subject's eye using a predetermined arithmetic expression, table, or the like. The configuration is not limited to that described above, and the eye size may be measured based on the time at which the interference signal is detected while the first triangular prism 314 is moving.

(S6: working distance adjustment)
The control unit 70 switches the working distance for measuring the axial length to the working distance for measuring the intraocular pressure. That is, the control unit 70 is aligned from the working distance of the axial length measuring optical system 310 to the working distance of the intraocular pressure measuring optical system (the deformation detecting optical system 350, the corneal thickness measuring optical system 370, etc.). state. For example, in this embodiment, the working distance when measuring the axial length is set longer than the working distance when measuring the intraocular pressure. Therefore, when the axial length measurement is completed, the control unit 70 causes the driving unit 5 to move the second measuring unit 3b forward (toward the subject's eye). As a result, when measuring the axial length of the eye, it is possible to secure a sufficient distance between the eye to be examined and the device compared to when measuring the intraocular pressure, and it is possible to prevent the subject from feeling oppressive or fearful. . Since the axial length measurement optical system 310 is an optical system that irradiates the eye to be inspected with parallel light, the distance relationship between the apparatus and the eye to be inspected can be set arbitrarily.

Note that the second fixation target optical system 330 and the second observation optical system 340 can be adjusted in focus so that the subject's eye can be focused even if the working distance differs between the axial length measurement and the intraocular pressure measurement. A lens may be provided. This enables stable alignment even at an arbitrary working distance.

(S7: intraocular pressure measurement)
The control unit 70 measures the intraocular pressure of the subject's eye. For example, the controller 70 drives the solenoid 203 . When the solenoid 203 is driven to move the piston 202, the air in the cylinder 201 is compressed and the compressed air is blown from the nozzle 206 toward the cornea Ec. The cornea Ec is gradually deformed by the blowing of compressed air, and the maximum amount of light is incident on the photodetector 357 when the cornea Ec reaches a flattened state. The controller 70 obtains the intraocular pressure value based on the output signal from the pressure sensor 210 and the output signal from the photodetector 357 .

(S8: Measurement result output)
The control unit 70 causes the display unit 75 or the like to display the measurement result. For example, the control unit 70 causes the display unit 75 to display corneal shape information, eye refractive power (SPH, CYL, AXIS), axial length, intraocular pressure, etc. of the eye E to be examined. In addition, when there is a past measurement result for the subject's eye E, the current measurement result may be displayed together with the past measurement result. For example, the measurement results may be displayed as a trend graph in which the horizontal axis is age (measurement date) and the vertical axis is eye refractive power, eye axial length, and intraocular pressure.

As described above, the ophthalmologic apparatus 1 of the present embodiment can measure the eye refractive power, the intraocular pressure, and the axial length of the eye with a single apparatus. , efficient inspection can be performed.

In addition, by providing the axial length measurement optical system 310 in the same second measurement unit 3b as the intraocular pressure measurement optical system (deformation detection optical system 350, etc.), the space of the second measurement unit 3b can be effectively used and the second measurement unit 3b can be used. Further space saving can be achieved by sharing the observation optical system 340 .

In addition, with the above structure, each measurement unit functions independently, so if the axial length measurement optical system 310 is removed, the composite device capable of measuring the refractive power and the intraocular pressure, the piston 202 and the nozzle 206 can be used. It becomes a combined device capable of measuring refractive power and axial length by detaching it, and becomes a combined device capable of measuring intraocular pressure and axial length by removing the first measuring unit 3a. .

<transformation example>
In the above examples, the axial length measurement optical system is provided with an interference optical system to measure the axial length, but the present invention is not limited to this. For example, a cross-sectional image of the anterior segment of the eye is acquired using a Scheimpflug camera or the like, and the positions and curvatures of the anterior corneal surface, posterior corneal surface, anterior lens surface, and posterior lens surface detected from the tomographic image are obtained. The axial length may be calculated from the relationship with the refractive power of the eye to be examined as a whole.

<Second embodiment>
The ophthalmologic apparatus 1a of the second embodiment will be described below. The ophthalmologic apparatus 1a of the second embodiment includes a Scheimpflug camera (sectional imaging optical system 400) and an eye refractive power measuring unit (first measurement The axial length of the eye is measured by the optical system 100). The ophthalmologic apparatus 1a of the second embodiment includes a first measuring section 3a and a second measuring section 3b, like the first embodiment. The first measuring unit 3a of the second embodiment includes a first measuring optical system 100 for measuring eye refractive power, a cross-sectional imaging optical system 400 for acquiring an anterior segment cross-sectional image, and the like. The first measurement optical system 100 and the cross-sectional imaging optical system 400 share a part of the optical system such as the objective lens. The second measuring section 3b of the second embodiment is similar to the second measuring section 3b of the first embodiment except that the axial length measuring optical system 310 and the corneal thickness measuring optical system 370 are removed. Therefore, the description is omitted.

FIG. 7 is a schematic diagram showing the optical system of the first measuring section 3a of the ophthalmologic apparatus 1a. As an example, the ophthalmologic apparatus 1 a includes a first measurement optical system 100 , a first fixation target presentation optical system 130 , a first observation optical system 150 , a first target optical system 160 and a cross-section imaging optical system 400 . It also has half mirrors 116 and 117, a dichroic mirror 503, an objective lens 118, etc. for branching and coupling the optical paths of the respective optical systems. Since the configuration other than the cross-sectional imaging optical system 400 is the same as that of the first embodiment, description thereof is omitted.

(cross-section imaging optical system)
The cross-sectional imaging optical system 400 is used to capture a cross-sectional image of the anterior segment. The cross-section imaging optical system 400 includes an irradiation optical system 400a and a light receiving optical system 400b.

The irradiation optical system 400a is coaxial with the projection optical axis (optical axis L11) of the measurement light in the first measurement optical system 100, and irradiates the anterior segment with slit light (illumination light). The irradiation optical system 400a has a light source 411, a slit 412, and the like. The light source 411 may be an SLD light source, an LED light source, or other light sources. In this embodiment, red visible light or near-infrared light is used as illumination light. For example, red visible light or near-infrared light with peak wavelengths between 650 nm and 800 nm may be utilized. As an example, red visible light with a peak wavelength of 730 nm may be used. Of course, near-infrared light with a predetermined wavelength as a peak wavelength may also be used. The slit 412 may be placed at a pupil conjugate position.

In this embodiment, the passage cross section of the slit light in the anterior segment is referred to as a "cut plane". The cut plane becomes the object plane of the cross-section imaging optical system. In FIG. 7, the opening of the slit 412 has a horizontal direction (the depth direction of the paper surface) as its longitudinal direction. Therefore, in this embodiment, the horizontal plane (XZ section) including the optical axis L1 is set as the cutting plane. In this embodiment, a cut surface is formed at least between the anterior corneal surface and the posterior surface of the lens.

The irradiation optical system 400 a is arranged in the reflection direction of the dichroic mirror 503 arranged on the optical axis L 12 of the first fixation target optical system 130 . At this time, by arranging the irradiation optical system 400a below the first measurement optical system 100, an increase in the height or width of the ophthalmologic apparatus 1a can be suppressed. Of course, the irradiation optical system 400a may be arranged in any direction if there is a margin in height or width.

The light receiving optical system 400b has a lens system 422, an imaging device 421, and the like. In the light-receiving optical system 400b, the lens system 422 and the imaging device 421 are arranged in a Scheimpflug relationship with the cutting plane set in the anterior segment. That is, the optical arrangement is such that the extension planes of the cut plane, the principal plane of the lens system 422, and the imaging surface of the imaging element 421 intersect at one line of intersection (one axis). A cross-sectional image of the anterior segment is acquired based on the signal from the imaging element 421 .

Note that the light receiving optical system 400b of this embodiment is arranged obliquely below the eye E to be examined. In this case, the light-receiving optical system 400b is easily affected by disturbance, but since the second measurement section 3b is located above the first measurement section 3a, the influence of disturbance light can be suppressed by arranging the second measurement section 3b. have a nature. In the case of this embodiment, the light receiving optical system 300b is arranged on the lower side in order to avoid interference with the first target optical system 160. good.

In the cross-sectional imaging optical system 400, the illumination light flux from the light source 411 passes through the slit 412 on the optical axis L15 and becomes a slit light flux. It is coaxial with the axis L12. Further, the light passes through the lens 504, passes through the half mirror 502, and is reflected by the half mirror 501, so that the light becomes coaxial with the optical axis L1. The illumination luminous flux further passes through the objective lens 505 and reaches the anterior segment of the eye. Return light from the cut surface formed in the anterior segment reaches the imaging device 321 via the lens 322 .

<Control operation>
The control operation of the ophthalmologic apparatus 1a will be described with reference to the flowchart shown in FIG. In this embodiment, the ophthalmologic apparatus 1a sequentially performs corneal curvature measurement, eye refractive power measurement, and photographing of an anterior segment cross-sectional image, and the axial length is obtained based on the results of the measurements and photographing. be. A tonometry is then performed.

(S201: first alignment)
First, alignment of the first measurement unit 3a with respect to the eye E to be examined is performed. The alignment method is the same as in the first embodiment.

(S202: Corneal shape measurement)
Next, the corneal shape of the subject's eye E is measured. The measuring method is the same as in the first embodiment.

(S203: eye refractive power measurement)
Next, the ocular refractive power of the subject's eye E is measured. The measuring method is the same as in the first embodiment.

(S204: Capturing an anterior segment cross-sectional image)
Next, a cross-sectional image (Scheimpflug image) of the anterior segment of the subject's eye E is captured. As shown in FIG. 9, the cross-sectional image P includes, for example, the cornea, the iris, the lens, and the like. Immediately after the main measurement of the eye refractive power is completed, the control unit 70 captures a cross-sectional image of the anterior segment of the eye. For example, the operation of capturing a cross-sectional image may be performed using the completion of the main measurement of the eye refractive power as a trigger. That is, immediately after the completion of the main measurement, illumination light is emitted from the illumination optical system 400a, and the scattered light scattered by the cornea and lens is imaged on the imaging device 421 to form an image of the anterior segment cross section. Get an image. This reduces misalignment between the measurement of the eye refractive power and the imaging of the cross-sectional image.

(S205: Analysis of cross-sectional image of anterior segment)
Based on the cross-sectional image P of the anterior segment of the eye E to be examined, the control unit 70 acquires anterior segment shape information regarding the shape of the anterior segment. For example, the anterior segment shape information includes the radius of curvature of the anterior corneal surface (Ra), the radius of curvature of the posterior corneal surface (Rp), the corneal thickness (CT), the depth of the anterior chamber (ACD), the radius of curvature of the anterior lens surface (ra), A plurality of parameter information may be included that are measurements such as the radius of curvature of the posterior lens surface (rp), lens thickness (LT), and the like. The corneal shape information acquired in step S202 can also be used as the anterior segment shape information.

The control unit 70 performs image processing on the cross-sectional image P to detect each translucent body (for example, the cornea, aqueous humor, crystalline lens, etc.) and acquire anterior segment shape information. For example, the brightness information of the cross-sectional image P may be used to detect pixel positions corresponding to tissue boundaries (corneal anterior and posterior surfaces, lens anterior and posterior surfaces, iris, etc.) and acquire information such as the radius of curvature. Further, for example, the distance between the pixel positions corresponding to the boundary of the tissue may be obtained, and information such as the thickness and depth of the tissue may be obtained.

(S206: Axial length calculation)
Next, the axial length of the eye E to be examined is calculated. The control unit 70 calculates the axial length based on the refractive power of the eye E to be examined and a plurality of parameter information in the anterior segment shape information of the eye E to be examined.

First, the control unit 70 obtains the position of the far point FP (see FIG. 10) with respect to the corneal vertex C based on the measurement result of the eye refractive power of the eye E to be examined. For example, if the subject's eye E has no astigmatism, SPH=−5D, and VD=12 mm, the distance from the corneal vertex C to the far point FP is 12+1000/5=212 mm. Light rays from the far point FP are considered to be imaged on the fundus. Note that VD=12 mm is a constant value indicating the distance between the corneal vertices on the premise of wearing spectacle lenses. VD may vary from device to device.

In this embodiment, the eye axial length may be derived based on the ray tracing calculation on the cut plane of the anterior segment. For example, the control unit 70 performs ray tracing calculation based on the position of the far point FP, the refractive index of each translucent body, and the parameter information in the anterior segment shape information.

The control unit 70 traces a light ray (e.g., light ray Lx in FIG. 10) incident from the far point FP toward the eye E to be examined, refracts the light ray by each translucent body of the eye E to be examined, and aligns the light ray with the optical axis. Find the position of the crossing point. For example, the position of the fundus oculi Ef is obtained by such ray tracing calculation. The control unit 50 derives the distance between the corneal vertex C and the fundus Ef as the axial length AL. In deriving the axial length AL, at least the anterior surface of the cornea, the posterior surface of the cornea, and the anterior surface of the crystalline lens should be captured in the cross-sectional image P, and the parameters of other parts may be determined by interpolation. See Japanese Patent Application No. 2021-061511 for the method of calculating the axial length.

(S207: second alignment)
When the measurement by the first measurement unit 3a is completed, the control unit 70 aligns the second measurement unit 3b. The alignment method is the same as in the first embodiment.

(S208: intraocular pressure measurement)
The control unit 70 measures the intraocular pressure of the subject's eye using the second measurement unit 3b. The measuring method is the same as in the first embodiment.

(S209: intraocular pressure correction)
The control unit 70 functions as correction means for correcting the measured value, and corrects (the measured value of) the intraocular pressure acquired in step S208. For example, the control unit 70 corrects the intraocular pressure based on the cross-sectional image P acquired by the cross-sectional imaging optical system 400 of the first measuring unit 3a. For example, the control unit 70 corrects the intraocular pressure based on the corneal thickness obtained from the cross-sectional image P. In this manner, even if the second measuring unit 3b is not provided with a corneal thickness measuring means, the intraocular pressure can be corrected by the measurement value obtained by the first measuring unit 3a, so that the configuration of the second measuring unit 3b is not increased. Measurement accuracy can be improved.

Note that the measured value obtained in step S205 may be used as it is as the measured value used for correcting the intraocular pressure. As a result, there is no need to take another cross-sectional image of the anterior segment to correct the intraocular pressure, so the intraocular pressure can be corrected efficiently. Of course, a cross-sectional image P for correcting the intraocular pressure may be acquired by taking an image with the cross-sectional imaging optical system 400 separately from that for measuring the axial length of the eye.

Note that the control unit 70 may correct other measured values based on the cross-sectional image P, not limited to the intraocular pressure. For example, the control unit 70 may correct the corneal shape or eye refractive power obtained in steps S202 and S203 based on the anterior segment shape information obtained from the cross-sectional image P. This makes it possible to further improve the measurement accuracy.

(S210: Measurement result output)
The control unit 70 causes the display unit 75 or the like to display the measurement result. For example, the control unit 70 causes the display unit 75 to display corneal shape information, eye refractive power, eye axial length, corrected intraocular pressure value, etc. of the eye E to be examined.

As described above, the ophthalmologic apparatus 1a of the second embodiment can measure the eye refractive power, the intraocular pressure, and the axial length of the eye with a single apparatus. can be reduced and an efficient examination can be performed. Further, the ophthalmologic apparatus 1a of the second embodiment can measure the axial length of the eye with a simple configuration by using a cross-sectional image based on the Scheimpflug principle, and also acquires anterior segment shape information such as corneal thickness from the cross-sectional image. Therefore, measurement values such as eye refractive power, corneal shape, and intraocular pressure value can be corrected from the anterior segment shape information, and more accurate examination can be performed.

Further, the ophthalmologic apparatus 1a of the second embodiment eliminates the need to dispose the corneal thickness measuring optical system 370 in the second measuring section 3b as in the first embodiment, and also has more ( shape information (other than corneal thickness) can be obtained. If the cross-section imaging optical system 400 is arranged in the second measuring unit 3b, only the corneal thickness and the corneal front curvature can be obtained because the working distance between the eye to be examined E and the second measuring unit 3b is short. By arranging the cross-sectional imaging optical system 400 in the first measuring section 3a where a sufficient working distance to the eye to be examined E is ensured, as in the embodiment, a wider range of cross-sectional images can be obtained, and more shape information can be obtained. can be obtained and used for axial length measurement and intraocular pressure correction.

1 Ophthalmic Apparatus 1a Ophthalmic Apparatus 3 Measuring Unit 3a First Measuring Unit 3b Second Measuring Unit 70 Control Unit 100 First Measuring Optical System 200 Fluid Ejecting Unit 300 Second Measuring Optical System 400 Cross-sectional Imaging Optical System

Claims

An ophthalmic device for examining an eye to be examined,
eye refractive power measuring means for measuring the eye refractive power of the eye to be examined;
intraocular pressure measuring means for measuring the intraocular pressure of the eye to be examined;
Axial length measuring means for measuring the axial length of the eye to be examined;
An ophthalmic device comprising:
The ophthalmologic apparatus according to claim 1, wherein said intraocular pressure measuring means and said axial length measuring means share a part of an optical system.
The ophthalmologic apparatus according to claim 2, wherein said intraocular pressure measuring means and said axial length measuring means share an observation optical system.
The ophthalmologic apparatus according to any one of claims 1 to 3, wherein the intraocular pressure measuring means and the axial length measuring means have different working distances.
driving means for three-dimensionally driving the intraocular pressure measuring means and the axial length measuring means;
and a control means for controlling driving of the driving means,
the working distance of the intraocular pressure measuring means is shorter than the working distance of the axial length measuring means;
When the intraocular pressure measurement is performed after the axial length measurement is performed, the control means adjusts the distance in the working distance direction so as to be the working distance of the intraocular pressure measuring means after the completion of the axial length measurement. The ophthalmologic apparatus according to any one of claims 1 to 4, wherein said driving means is controlled so that said intraocular pressure measurement is performed after said intraocular pressure measuring means is brought close to said eye to be examined.
The ophthalmologic apparatus according to any one of claims 1 to 5, wherein said control means measures the eye axial length by said eye axial length measuring means after measuring eye refractive power by said eye refractive power measuring means.
The ophthalmologic apparatus according to any one of claims 1 to 6, further comprising corneal shape measuring means for measuring the corneal shape of the eye to be examined.
The axial length measuring means projects measurement light onto the anterior segment of the eye to be inspected to form a light section passing through the optical axis of the eye refractive power measuring means in the anterior segment. a cross-sectional image capturing optical system for acquiring an anterior segment cross-sectional image of the subject eye based on light returned from the light-section plane of the measuring light, wherein the eye refractive power and the anterior segment cross-sectional image are obtained; 2. The ophthalmologic apparatus according to claim 1, wherein said axial length is calculated based on .
The ophthalmologic apparatus according to claim 8, wherein said eye refractive power measuring means and said eye axial length measuring means share a part of an optical system.
correction means for correcting the intraocular pressure, the eye refractive power, or the corneal shape of the subject's eye measured by the corneal shape measuring means, based on the anterior segment cross-sectional image acquired by the cross-sectional image capturing optical system; 10. An ophthalmic device according to claim 8 or 9, further comprising.
11. The ophthalmologic apparatus according to any one of claims 8 to 10, wherein said correction means corrects said intraocular pressure based on corneal thickness obtained from said anterior segment cross-sectional image.