Ophthalmologic apparatus

Abstract

To provide an ophthalmologic apparatus capable of easily setting a limit position according to attachment and detachment of an attachment.SOLUTION: An ophthalmologic apparatus that can be mounted with an attachment for examining eye characteristics of an eye to be examined includes: examination means for examining eye characteristics of the eye to be examined; moving means for changing relative positional relationships between the eye to be examined and the examination means; setting means for setting a limit position of an advancing movement of the examination means with respect to the eye to be examined; and control means for controlling the moving means on the basis of the limit position set by the setting means for advancing the examination means with respect to the eye to be examined. The setting means sets a first limit position when the attachment is not mounted, and sets a second limit position when the attachment is mounted, which is changed by a distance corresponding to the attachment with respect to the first limit position. The control means controls the moving means on the basis of the second limit position set by the setting means when the attachment is mounted.SELECTED DRAWING: Figure 1

Description

[Technical field]

[0001] The present disclosure relates to an ophthalmic apparatus for examining an eye to be examined. [Background technology]

[0002] Conventionally, ophthalmic devices include intraocular pressure measuring devices, corneal shape measuring devices, eye refractive power measuring devices, fundus cameras, OCT (Optical Coherence Tomography), SLO (Scanning Light Ophthalmoscope), etc. Some ophthalmic devices are capable of attaching and detaching attachments (adapters) according to the measurement of the subject's eye. As an example, in Patent Document 1, an attachment is attached to capture a wide-angle image of the fundus of the subject's eye. [Prior art documents] [Patent documents]

[0003] [Patent Document 1] JP 2019-195422 A Summary of the Invention [Problem to be solved by the invention]

[0004] In the above-mentioned ophthalmic device, a limit position for restricting the movement of the measurement unit for measuring the subject's eye may be set in advance so that the measurement unit does not come into contact with the subject. However, when an attachment is attached to the ophthalmic device, the distance between the subject's eye and the measurement unit changes depending on the attachment, so that the measurement unit may come into contact with the subject before it reaches the limit position.

[0005] In view of the above problems, the present disclosure has as its technical object to provide an ophthalmic apparatus that can easily set limit positions in accordance with the attachment or detachment. [Means for solving the problem]

[0006] In order to solve the above problems, the present invention is characterized by having the following configuration.

[0007] An ophthalmic apparatus according to a first aspect of the present disclosure is an ophthalmic apparatus for examining a test eye, and is capable of being fitted with an attachment for testing ocular characteristics of the test eye, and comprises an inspection means for inspecting the ocular characteristics of the test eye, a moving means for changing the relative positional relationship between the test eye and the inspection means, a setting means for setting a limit position for forward movement of the inspection means relative to the test eye, and a control means for controlling the moving means based on the limit position set by the setting means in order to move the inspection means forward relative to the test eye, wherein the setting means sets a first limit position when the attachment is not attached, and sets a second limit position when the attachment is attached, the second limit position being changed from the first limit position by a distance corresponding to the attachment, and the control means controls the moving means based on the second limit position set by the setting means when the attachment is attached. [Brief description of the drawings]

[0008] [Figure 1] FIG. 1 is a diagram showing an external configuration of an ophthalmologic apparatus. [Diagram 2] FIG. 2 is a diagram showing an optical system of a first measurement unit. [Diagram 3] FIG. 2 is a diagram showing a configuration of an attachment. [Figure 4] FIG. 4 is a diagram showing the internal configuration of a second measurement unit. [Diagram 5] FIG. 4 is a diagram showing the optical system of a second measurement unit. [Figure 6] FIG. 2 is a schematic diagram of a control system of the ophthalmic apparatus. [Figure 7] 4 is a diagram showing a movable range and limit positions of a measuring unit. FIG. [Figure 8] 13 is an example of an examination screen. [Figure 9] 13 is an example of an examination screen. [Figure 10]13 is an example of an examination screen. [Figure 11] 13 is an example of an examination screen. [Figure 12] 13A and 13B are diagrams for explaining retraction of the measuring unit and attachment of the attachment. [Figure 13] 13 is an example of an examination screen. [Figure 14] 13 is an example of an examination screen. [Figure 15] FIG. 11 is a diagram showing the relationship between the first limit position and the working distance depending on the subject's face shape. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0009] <Summary> An overview of an ophthalmic device according to an embodiment of the present disclosure will be described. The items classified in <> below can be used independently or in conjunction with each other.

[0010] <Ophthalmological equipment> The ophthalmic apparatus of the present embodiment is an apparatus for examining an eye to be examined. For example, the ophthalmic apparatus may be an objective ophthalmic examination apparatus that objectively measures the eye characteristics (eye refractive power, axial length, corneal shape, etc.) of the eye to be examined. For example, the ophthalmic apparatus may be an ophthalmic imaging apparatus that photographs the anterior part of the eye to be examined and obtains anterior part image data of the eye to be examined, corneal shape data of the eye to be examined, etc. Also, for example, the ophthalmic apparatus may be an ophthalmic imaging apparatus that photographs the fundus of the eye to be examined and obtains frontal fundus image data of the eye to be examined, fundus tomographic image data of the eye to be examined, etc. That is, the ophthalmic apparatus may be at least one of an eye refractive power measuring apparatus, a corneal curvature measuring apparatus, a corneal shape measuring apparatus, an intraocular pressure measuring apparatus, an axial length measuring apparatus, a fundus camera, an OCT (Optical Coherence Tomography), an SLO (Scanning Laser Ophthalmoscope), etc.

[0011] The ophthalmic apparatus of the present embodiment may be an ophthalmic apparatus to which an attachment for testing ocular characteristics of a subject's eye can be attached. For example, the attachment may be used to obtain a second ocular characteristic of the subject's eye that is different from a first ocular characteristic obtained when the attachment is not attached.

[0012] For example, the attachment may be used to measure the corneal shape distribution of the subject's eye. For example, the attachment may be attached to an eye refraction measurement means described later, thereby adding a corneal shape distribution measurement means for measuring the corneal shape distribution of the subject's eye to the eye refraction measurement means. For example, the attachment may be used to place a corneal shape distribution measurement optical system in the optical path of the eye refraction measurement optical system, thereby adding a corneal shape distribution measurement optical system as a part of the eye refraction measurement optical system. For example, in this case, the attachment may be an attachment for projecting a measurement index onto the cornea to obtain the corneal shape distribution of the subject's eye.

[0013] <Testing method> The ophthalmologic apparatus of this embodiment may include an inspection means (e.g., a measurement unit 3). The inspection means inspects the ocular characteristics of the subject's eye. For example, the inspection means may include an inspection optical system as a part of the inspection means. As an example, the inspection optical system may have at least one of various optical systems such as an eye photographing optical system (fundus photographing optical system, tomographic image photographing optical system, etc.) for photographing the tissue of the subject's eye, and an eye characteristic measuring optical system (e.g., intraocular pressure measuring optical system, axial length measuring optical system, eye refractive power measuring optical system, corneal curvature measuring optical system, etc.) for measuring the ocular characteristics of the subject's eye.

[0014] For example, the examination means may include an eye refraction measuring means. For example, the eye refraction measuring means projects a measurement light beam onto the fundus of the eye to be examined, and measures the eye refraction of the eye to be examined based on a reflected light beam of the measurement light beam reflected by the fundus. For example, the eye refraction measuring means may include an eye refraction measuring optical system (for example, the first measuring optical system 100) as a part constituting the eye refraction measuring means. Also, for example, the examination means may include an intraocular pressure measuring means. For example, the intraocular pressure measuring means has a fluid ejection means (for example, the fluid ejection unit 200) that ejects a fluid onto the cornea of ​​the eye to be examined, and measures the intraocular pressure by deforming the cornea with the fluid. For example, the intraocular pressure measuring means may include an intraocular pressure measuring optical system (for example, the second measuring optical system 300) as a part constituting the intraocular pressure measuring means. Also, for example, the examination means may include a corneal shape distribution measuring means (for example, the corneal shape distribution measuring unit 500, the attachment 510). For example, the corneal shape distribution measuring means measures the corneal shape distribution of the subject's eye. For example, the corneal shape distribution measuring means may include a corneal shape distribution measuring optical system as a part constituting the corneal shape distribution measuring means. Note that, for example, a part of the eye refractive power measuring optical system may also be used as a part of the corneal shape distribution measuring optical system.

[0015] <Detection Method> The ophthalmic device of this embodiment may include a detection means (e.g., a control unit 70). For example, the detection means detects the attachment of the attachment to the ophthalmic device. For example, the detection means is required to at least detect whether or not the attachment is in contact with the ophthalmic device when the attachment is attached to the ophthalmic device. In this case, the detection means may be a contact detector (e.g., a physical sensor), a non-contact detector (e.g., an optical sensor, a magnetic sensor), or the like.

[0016] For example, the attachment of the attachment to the ophthalmic device may include an electrical connection between the ophthalmic device and the attachment, and the detection means may detect whether or not they are electrically connected. In this case, the detection means may be a non-contact detector (e.g., a current sensor, a voltage sensor, etc.).

[0017] <Acquisition method> The ophthalmologic apparatus of this embodiment may include an acquisition means (e.g., a control unit 70). For example, the acquisition means acquires a captured image of the subject's eye. For example, the captured image of the subject's eye may be a facial image including at least one of the left eye and the right eye. Also, for example, the captured image of the subject's eye may be an anterior segment image of at least one of the left eye and the right eye.

[0018] The acquisition means may include, as a part of the acquisition means, an illumination optical system (e.g., face illumination optical system 410) for illuminating the subject's eye. For example, the illumination optical system may have at least a light source and emit an illumination light beam toward the subject or the subject's eye. The acquisition means may also include, as a part of the acquisition means, an imaging optical system (e.g., face imaging optical system 420, first observation optical system 150, second observation optical system 340) for capturing an image of the subject's eye. For example, the face imaging optical system may have at least an image sensor and receive a reflected light beam from the subject or the subject's eye.

[0019] <Transportation> The ophthalmologic apparatus of this embodiment may include a moving means (e.g., a drive unit 5). For example, the moving means may be for changing the relative positional relationship between the subject's eye and the inspection means. For example, the moving means may be for moving the inspection means relative to the subject's eye in at least one of the left-right direction (X direction), the up-down direction (Y direction), and the front-back direction (Z direction).

[0020] <Operation means> The ophthalmic apparatus of this embodiment may include an operation means (e.g., an operation unit 76). For example, the operation means may be used to set a limit position of forward movement of the inspection means relative to the subject's eye. Also, for example, the operation means may be used to finely adjust a limit position (described later) of forward movement of the inspection means relative to the subject's eye. For example, the operation means may be at least one of an operation button provided on the ophthalmic apparatus main body, an operation button displayed on a display means (e.g., a display unit 75) included in the ophthalmic apparatus, a controller connected to the ophthalmic apparatus, and the like.

[0021] <Storage means> The ophthalmic apparatus of this embodiment may include a storage means (e.g., a memory 74). For example, the storage means may store at least one of the first limit position or the second limit position after a change (after fine adjustment) set by a setting means described later. For example, at least one of a storage medium included in the ophthalmic apparatus, a storage medium detachable from the ophthalmic apparatus, a storage medium included in a personal computer (PC) or other device connected to the ophthalmic apparatus, a server or a cloud connected to the ophthalmic apparatus, etc. may be used as the storage means.

[0022] <Settings> The ophthalmologic apparatus of this embodiment may include a setting means (e.g., a control unit 70). For example, the setting means sets a limit position for the forward movement of the inspection means relative to the subject's eye. For example, the limit position may be a position for limiting at least the forward movement of the inspection means. Of course, for example, the limit position may be a position for limiting at least one of the left-right and up-down movement of the inspection means in addition to the forward movement.

[0023] The setting means may set limit positions corresponding to when the attachment is not attached and when it is attached. For example, the setting means may set a first limit position when the attachment is not attached, and a second limit position when the attachment is attached, the second limit position being changed from the first limit position by a distance corresponding to the attachment.

[0024] The setting means may change and set the first limit position to the second limit position based on a detection signal from the detection means that detects the attachment being attached, thereby improving, for example, the operability of the device and making it easier to set the second limit position.

[0025] The setting means may change and set the first limit position and the second limit position based on an operation signal from an operation means for finely adjusting the limit position of the forward movement of the inspection means relative to the subject's eye. For example, when the first limit position is finely adjusted and changed, the second limit position may be set by changing the first limit position after the fine adjustment by a distance corresponding to the attachment. More specifically, the second limit position may be set based on the amount of change in the first limit position before and after the fine adjustment and the distance corresponding to the attachment. Also, for example, when the second limit position is finely adjusted and changed, the second limit position may be set by changing the second limit position after the fine adjustment by a distance corresponding to the attachment. More specifically, the first limit position may be set based on the amount of change in the second limit position before and after the fine adjustment and the distance corresponding to the attachment.

[0026] The setting means may set at least one of the first limit position or the second limit position after fine adjustment stored in the storage means on a different examination date of the subject's eye. For example, this allows the limit position once determined for a specific subject to be easily recalled, thereby reducing the trouble of setting the limit position every time the examination date changes.

[0027] In this embodiment, when the testing means for testing the eye characteristics of the subject eye includes an eye refraction measuring means and an intraocular pressure measuring means, and an attachment is attached to the eye refraction measuring means to add a corneal topography distribution measuring means, the setting means may set a first limit position for the forward movement of the eye refraction measuring means, a second limit position for the forward movement of the corneal topography distribution measuring means, and a third limit position for the forward movement of the fluid ejecting means, respectively. That is, the setting means may set a first limit position when the attachment is not attached in the eye refraction measurement of the subject eye, a second limit position when the attachment is attached in the corneal topography distribution measurement of the subject eye, and a third limit position in the intraocular pressure measurement of the subject eye, respectively.

[0028] <Control Means> The ophthalmic apparatus of the present embodiment may include a control means (e.g., a control unit 70). For example, the control means may control the moving means based on a limit position set by the setting means to move the inspection means forward relative to the subject's eye. For example, the control means may control the moving means based on a first limit position set by the setting means to move the inspection means forward. Also, for example, the control means may control the moving means based on a second limit position set by the setting means when the attachment is attached to move the inspection means forward. For example, some ophthalmic apparatuses can test the eye characteristics of the subject's eye under different conditions or test a plurality of different eye characteristics of the subject's eye by selectively using the non-attachment and attachment of the attachment. For this reason, for example, the limit position set so that the inspection means does not come into contact with the subject is changed according to the attachment being attached or detached, thereby reducing the troublesomeness of the examiner resetting the limit position of the inspection means each time.

[0029] <Display control means> The ophthalmologic apparatus of this embodiment may include a display control means (e.g., a control unit 70). For example, the display control means displays the movable range of the forward movement of the inspection means and the limit position for the movable range on a display means (e.g., a display unit 75). For example, at least one of a first limit position, a second limit position, and a third limit position for the movable range may be displayed on the display means. For example, the movable range of the forward movement of the inspection means may be a range from a position when the inspection means is moved most backward with respect to the subject's eye to a position when the inspection means is moved most forward toward the subject's eye. For example, this allows the examiner to visually determine whether the limit position is appropriate for the subject's eye.

[0030] For example, the display control means may display a gauge indicating the movable range of the forward movement of the inspection means and the limit position by superimposing the gauge and the limit position on the captured image of the subject's eye. For example, this allows the examiner to intuitively grasp the relationship between the movable range of the inspection means and the limit position. Also, for example, the examiner can easily fine-tune the first limit position or the second limit position while checking the movable range and limit position of the inspection means.

[0031] For example, the display control means may display the current position of the inspection means in real time relative to the movable range of the forward movement of the inspection means. For example, the display control means may display the current position of the inspection means in real time based on the movement amount of the movement means for moving the inspection means forward. For example, this allows the examiner to easily determine whether the limit position of the inspection means with respect to the subject's eye is appropriate.

[0032] <Example> An example of the ophthalmic apparatus according to the present embodiment will be described.

[0033] <Device configuration> FIG. 1 is a diagram showing the external configuration of an ophthalmic apparatus 1. For example, the ophthalmic apparatus 1 includes a measurement unit 3 that measures the eye to be examined. The measurement unit 3 includes a first measurement unit 3a and a second measurement unit 3b. The first measurement unit 3a functions as an ocular refractive power measurement means that measures the ocular refractive power of the eye to be examined. The first measurement unit 3a also functions as a corneal shape distribution measurement means that measures the corneal shape distribution of the eye to be examined by attaching an attachment to be described later. The second measurement unit 3b functions as an ocular pressure measurement means that measures the intraocular pressure of the eye to be examined.

[0034] Also, for example, the ophthalmic device 1 includes a base 2, a face support unit 4, a drive unit 5, a speaker 6, a display unit 75, an operation unit 76, a control unit 70, and the like. The base 2 supports each unit of the ophthalmic device 1. The face support unit 4 is used to fix the face of the subject. The face support unit 4 is fixed to the base 2 and supports the face of the subject. For example, the face support unit 4 includes a forehead rest 4a, a chin rest 4b, a chin rest sensor 4c, a chin rest drive unit 4d, and the like. The chin rest sensor 4c detects whether or not the chin is placed on the chin rest 4b. The chin rest drive unit 4d drives the chin rest 4b in the Y direction to change the height. The drive unit 5 drives the first measurement unit 3a and the second measurement unit 3b integrally. The drive unit 5 moves the first measurement unit 3a and the second measurement unit 3b in three-dimensional directions, up and down, left and right, front and back, relative to the base. The speaker 6 generates voice announcements, etc.

[0035] The display unit 75 is controlled by the control unit 70 and displays the measurement results of the subject's eye, etc. For example, the display unit 75 displays the ocular refractive power of the subject's eye, the corneal shape distribution, the intraocular pressure, a frontal image of the anterior segment, etc. on the screen.

[0036] The operation unit 76 accepts operations by the examiner. When the display unit 75 has a touch panel, the display unit 75 may function as the operation unit 76.

[0037] The first measurement unit 3a has an eye examination window 101, to which an attachment 510 is attached. When the attachment 510 is attached to the first measurement unit 3a, the eye examination axis L1 of the first measurement unit 3a and the central axis LO of the attachment 510 are coaxial. The attachment 510 projects a measurement index for obtaining the corneal shape distribution of the subject's eye onto the cornea of ​​the subject's eye. The attachment 510 is a component of a corneal shape distribution measurement unit 500 that obtains the corneal shape distribution of the subject's eye (details will be described later).

[0038] The attachment 510 is inserted into and removed from the measurement position of the eye examination window 101 by an insertion / removal drive unit 550 described later, and is moved between the measurement position and a retreat position (a position off the eye examination path of the first measurement unit 3a). The measurement unit 3 is provided with a storage unit 560 corresponding to the retreat position of the attachment 510. For example, the retreat position of the attachment 510 is a rear position away from the eye examination window 101, or a position on the same plane as the eye examination window 101, where the attachment 510 does not protrude at least beyond the eye examination window 101 to the eye examination side. When the attachment 510 is not used, the attachment 510 is stored in the storage unit 560 inside the cover of the measurement unit 3, thereby reducing adhesion of dust and dirt, and also reducing damage due to contact. Furthermore, the storage unit 560 may be provided with an openable and closable door.

[0039] <1st measurement section> 2 is a diagram showing the optical system of the first measurement unit 3a. The first measurement unit 3a includes a first measurement optical system 100, a first fixation target optical system 130, a first observation optical system 150, and a first indicator optical system 160. It also includes half mirrors 116 and 117 that split and combine the optical paths of the optical systems, an objective lens 118, and the like.

[0040] <1st measurement optical system> The first measuring optical system 100 objectively measures the ocular refractive power of the subject's eye E. The first measuring optical system 100 has a light projecting optical system 100a and a light receiving optical system 100b.

[0041] The light projecting optical system 100a has a measurement light source 111, and projects a spot-shaped measurement light onto the fundus of the subject's eye E through the center of the pupil or the corneal apex of the subject's eye E. 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 having a peak wavelength between 800 nm and 900 nm may be used. As an example, near-infrared light having a peak wavelength of 870 nm may be used. Of course, light of other wavelengths may be used.

[0042] The light receiving optical system 100b has at least a ring lens 123 and an image sensor 124. The light receiving optical system 100b extracts the measurement light reflected from the fundus in a ring shape through the periphery of the pupil. The ring lens 123 is disposed at a pupil conjugate position, and the image sensor 124 is disposed at a fundus conjugate position. A ring image is formed on the image sensor 124 via the ring lens 123.

[0043] In this embodiment, a prism 115 is disposed on a common path of the light projecting optical system 100a and the light receiving optical system 100b. The prism 115 is rotated about the optical axis, so that the projecting light beam on the pupil is eccentrically rotated at high speed. As an example, in this embodiment, the projecting light beam is eccentrically rotated in a region on the pupil of φ2 mm to φ4 mm. This region is the measurement region of the eye refractive power in this embodiment.

[0044] In this embodiment, since the measurement light is eccentrically rotated at high speed on the pupil, an analysis process is performed on an output image from the image sensor 124 based on an exposure time that is sufficiently long with respect to the rotation period, or an additive image of image data sequentially output from the image sensor 124, to derive the ocular refractive power. In this embodiment, values ​​such as SPH: spherical power, CYL: cylindrical power, and AXIS: astigmatism axis angle are acquired as the results of the analysis process.

[0045] 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 image sensor 124. The measurement light beam from the measurement light source 111 passes through the hole of the hole mirror 114 and the prism 115, and is reflected by the half mirror 116 and the half mirror 117, respectively, so as to become coaxial with the optical axis L1, and then reaches the fundus via the objective lens 118. The reflected light beam of the measurement light beam reflected by the fundus passes through the optical path that the measurement light beam passed through, is reflected by the mirror part of the hole mirror 114, and reaches the image sensor 124 via the ring lens 123.

[0046] <First fixation target optical system> The first fixation target optical system 130 presents a fixation target to the subject's eye E. The first fixation target optical system 130 fixates the subject's eye, and applies fogging 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 disposed at a position conjugate with the fundus. A fixation light beam from the light source 131 passes through the fixation target plate 132, the lens 133, the lens 134, and the half mirror 116 on the optical axis L2, and is reflected by the half mirror 117 to become coaxial with the optical axis L1. The fixation light beam further passes through the objective lens 118 to reach the fundus.

[0047] The measurement light source 111, the ring lens 123, and the image sensor 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 can be moved integrally along the optical axis by the drive unit 141 as the drive unit 140. For example, the focal length in the drive unit 140 in the first measurement optical system 100 and the focal length in the drive unit 140 in the first fixation target optical system 130 have a predetermined relationship. For example, by moving the drive unit according to the ocular refractive power of the test eye E, the presentation distance of the fixation target plate 132 relative to the test eye E (i.e., the presentation position of the fixation target) can be changed, and the measurement light source 111 and the image sensor 124 are optically conjugated with the fundus. At this time, regardless of the movement of the drive unit, the hole mirror 114 and the ring lens 123 are pupil conjugated at a constant magnification.

[0048] <First observation optical system> The first observation optical system 150 captures a front image of the anterior segment of the subject's eye E. For example, the first observation optical system 150 includes an image sensor 151 and the like. The image sensor 151 may be disposed at a pupil conjugate position. The front image is used for alignment and the like. In addition, an index image (point image) projected onto the cornea from the first target optical system 160 and an index image (Mayer ring image) are captured by the first observation optical system 150.

[0049] <1st index optical system> The first indicator optical system 160 projects an index on the subject's eye. The first indicator optical system 160 is used, for example, for alignment (positioning) of the subject's eye E. The first indicator optical system 160 includes a plurality of point light sources 161 and a light source 162. The point light source 161 projects an infinite 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 symmetrically in the vertical direction and the horizontal direction with respect to the optical axis L1. For example, in this embodiment, two point light sources are provided on each side. As a result, four point image indices are projected on the cornea. Note that the shape of the indices is not limited to this, and may include linear indices. Also, the number of indices is not limited to this, and may be composed of three or more point image indices.

[0050] The light source 162 projects a finite index by irradiating the cornea with diffused light. The light source 162 emits infrared light. However, it may be visible light. The light source 162 is arranged in a ring shape centered on the optical axis L1. As a result, in this embodiment, a ring index (so-called Mayer ring) is projected onto the cornea.

[0051] In this embodiment, the working distance is adjusted by moving the measuring unit 3 in the forward / backward 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. <Corneal shape distribution measuring section> 3 is a diagram showing a schematic configuration of the corneal shape distribution measuring part 500. The corneal shape distribution measuring part 500 includes an attachment 510. For example, the attachment 510 is an index projection attachment that is a cone-shaped index projector.

[0052] The attachment 510 includes an inner cylinder portion 522 having a conical shape centered on the central axis LO of the attachment 510, and an outer shell portion 532. An opening 522a on the tip side of the inner cylinder portion 522 is formed in a shape wider than an opening 522b on the rear end side. The opening 522b is positioned at the eye examination window 101.

[0053] The inner cylinder 522 is formed with a number of (for example, five or more) slits 524 serving as light passing sections. The slits 524 are formed in a ring shape centered on the central axis LO. The ring-shaped slits 524 are used as a Placido ring index 524a projected onto the cornea of ​​the subject's eye. Note that the slits 524 may be missing a part of the ring shape as a connecting section in order to maintain the shape of the inner cylinder 522.

[0054] The tip side of the outer shell part 532 has a tapered shape. The rear end side of the outer shell part 532 has a shape that can accommodate an annular pattern indicator plate 543. For example, a hollow light transmitting part 534 is formed between the outer shell part 532 and the inner cylinder part 522.

[0055] In this embodiment, by attaching the attachment 510 to the first measurement unit 3a, the first index projection optical system 160 for projecting an alignment index onto the subject's eye E is used as a measurement optical system for measuring the corneal shape distribution of the subject's eye. For example, the point light source 161 and the light source 162 of the first index optical system 160 are also used as light sources for projecting the Placido ring index 524a onto the cornea of ​​the subject's eye. For example, the light emitted from the point light source 161 and the light source 162 passes through the pattern index plate 163 and is emitted from the multiple slits 524 via the light transmission unit 534. As a result, the Placido ring index 524a is projected onto the cornea of ​​the subject's eye.

[0056] The light source for projecting the Placido ring indicator 524a may not be shared with the first indicator optical system 160, but may be provided exclusively inside the attachment 510 (for example, inside the light transmitting portion 534).

[0057] In this embodiment, by attaching an attachment 510 to the first measurement unit 3a, the first fixation target optical system 130 for presenting a fixation target to the subject's eye and the first observation optical system 150 for capturing a front image of the anterior part of the subject's eye are used as a measurement optical system for measuring the corneal shape distribution of the subject's eye. For example, an anterior part image including an image of the Placido ring index 524a in a state in which the subject's eye is fixated on the fixation target plate 132 is captured (acquired) by the image sensor 151 of the first observation optical system 150. An analysis process is performed on the output image from the image sensor 151 or on the added image of the image data sequentially output from the image sensor 151, thereby deriving the corneal shape distribution.

[0058] A rotating arm 542 is connected to a part of the outer shell 532 of the attachment 510. A rotating shaft 544 is attached to the rotating arm 542, and the rotating shaft 544 is rotated by an insertion / removal drive unit 550. The rotating arm 542 and the rotating shaft 544 are components of the insertion / removal mechanism 540. For example, the insertion / removal drive unit 550, which is a component of the insertion / removal mechanism 540, is composed of a rotation transmission mechanism such as a motor and a gear. When the insertion / removal drive unit 550 is driven, the attachment 510 is rotated integrally around the axis of the rotating shaft 544. As a result, the attachment 510 is moved between the measurement position of the optometry window 101 and the retracted position (storage unit 560). Note that whether the attachment 510 is placed at the measurement position may be detected by an insertion / removal sensor 570. Furthermore, when the attachment 510 is placed at the measurement position, the position of the attachment 510 may be fixed at the measurement position by a latch mechanism 555.

[0059] <Second measurement section> 4 is a diagram showing the internal configuration of the second measurement unit 3b. The second measurement unit 3b includes a face photographing unit 400, a fluid discharge unit 200, and a second measurement optical system 300. The fluid discharge unit 200 generates compressed air for intraocular pressure measurement. The face photographing unit 400 photographs the subject's face. The second measurement optical system 300 includes an optical system for measuring intraocular pressure.

[0060] <Facial Photography Department> The face photographing unit 400 includes a face illumination optical system 410, a face photographing optical system 420, etc. The face illumination optical system 410 illuminates the face of the subject. The face illumination optical system 410 includes an illumination light source 411, etc. The illumination light source 411 may be a light source with low directivity. The illumination light source 411 may also be a light source that emits infrared light.

[0061] The face photographing optical system 420 photographs the face of the subject. The face photographing optical system 420 includes an imaging lens 421, an imaging element 422, and the like. The imaging element 422 receives a light beam reflected from the face. This allows a face image including at least one of the left eye and the right eye of the subject's eye E to be captured. An output signal from the imaging element 422 is input to the control unit 70 and the display unit 75.

[0062] <Fluid discharge section> The fluid discharge unit 200 discharges a fluid onto the cornea of ​​the subject's eye E. The fluid discharge unit 200 includes a cylinder 201, a piston 202, a solenoid actuator 203 (hereinafter, solenoid 203), a nozzle 206, and the like. The cylinder 201 and the piston 202 are used as an air compression mechanism for compressing air to be discharged onto the subject's eye. For example, the cylinder 201 is cylindrical. The piston 202 slides along the axial direction of the cylinder 201. The piston 202 compresses air in an air compression chamber 234 inside the cylinder 201. The solenoid 203 of this embodiment is a so-called direct acting solenoid, and operates linearly. The solenoid 203 includes a movable body 204 and a coil 205. For example, a magnetic body such as a permanent magnet is used for the movable body 204. When a current flows through the coil 205, a magnetic field is generated inside the coil 205. The movable body 204 is moved in the direction A in Fig. 4 by the electromagnetic force received from the magnetic field. The movable body 204 is fixed to the piston 202 by screws, bolts, nuts, etc. (not shown). Therefore, the piston 202 moves together with the movable body 204. The movement of the movable body 204 moves the piston 202 in the compression direction (or forward direction, direction A in Fig. 4). The nozzle 206 discharges the compressed air to the outside of the device.

[0063] The fluid compressed in the air compression chamber 234 in the cylinder 201 by the movement of the piston 202 is discharged from the nozzle 206 toward the cornea of ​​the subject's eye E through a tube (which may be a pipe) 220 connected to the tip of the cylinder 201 and an airtight chamber 221 that contains the compressed air. For example, the cylinder 201 may be arranged parallel to a horizontal plane (XZ plane), and the piston 202 may be moved horizontally in the cylinder 201 by driving the solenoid 203, thereby compressing the fluid. For example, the cylinder 201 may be arranged such that its longitudinal direction is parallel to the horizontal direction, and the inner surface of the cylinder 201 guides the piston 202. For this reason, the movement direction (compression direction) of the piston 202 is horizontal. The above-mentioned components are each arranged on a stage provided in the housing of the device main body.

[0064] In addition, the solenoid 203 of this embodiment can change the moving direction of the movable body 204 by changing the direction of the current flowing through the coil 205. For example, when a current flows in the forward direction through the coil 205, the movable body 204 moves in the compression direction (forward direction, direction A in FIG. 4), and when a current flows in the reverse direction, the movable body 204 moves in the opposite direction (rearward direction, 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, after a current flows in the forward direction through the coil 205, the piston 202 moves in the direction A to compress the fluid in the air compression chamber 234, and then a current flows in the reverse direction through the coil 205, the piston 202 moves in the direction B to return to the initial position.

[0065] For example, the fluid ejection unit 200 may include a glass plate 208 and a glass plate 209. The glass plate 208 is transparent, holds the nozzle 206, and transmits observation light and alignment light. The glass plate 209 forms a rear wall of the airtight chamber 221 and transmits observation light and alignment light.

[0066] For example, the fluid discharge section 200 may include a pressure sensor 212 and an air vent hole 213. The pressure sensor 212 detects, for example, the pressure in the airtight chamber 221. The air vent hole 213 reduces resistance until the piston 202 gains initial velocity, for example, and can obtain a pressure change that rises proportional to time.

[0067] <Second measurement optical system> 5 is a diagram showing the second measurement optical system 300. The second measurement optical system 300 measures the intraocular pressure of the subject's eye. For example, the second measurement optical system 300 includes a second fixation target optical system 330, a second observation optical system 340, a second index optical system 390, a deformation detection optical system 350, and a corneal thickness measurement optical system 370.

[0068] <Second fixation target optical system> The second fixation target optical system 330 presents a fixation target from the front direction to the subject's eye E. 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, and projects light onto the subject's eye E to fixate the subject's eye E in the front direction. The light source 331 may be a light source such as an LED or a laser. The light source 331 may be, for example, a pattern light source such as a point light source, a slit light source, or a ring light source, or a two-dimensional display such as a liquid crystal display.

[0069] 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 then projected onto the fundus of the subject's eye E. This causes the subject's eye E to fixate on a fixation point in the front direction, and the line of sight 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 beam.

[0070] <Second observation optical system> The second observation optical system 340 is disposed to capture an image of the anterior part of the subject's eye. The 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 property 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 part of the eye. The second observation optical system 340 includes an imaging lens 342, a filter 343, and an imaging element (such as a CCD) 344. The imaging lens 342 collects the reflected light from the subject's eye on the imaging element 344. The filter 343 has a property of transmitting, for example, the light of the light source 381 and the light source 391 and being opaque to the light of the light source 351 for detecting corneal deformation described later and visible light. The imaging element 344 receives the reflected light from the subject's eye. The imaging element 344 outputs the acquired light reception signal to the control unit 70.

[0071] The illumination light from the light source 381 reflected by the subject's eye passes through the nozzle 206 , passes through the objective lens 302 , is reflected by the dichroic mirror 333 and the beam splitter 341 , and passes through the imaging lens 342 and the filter 343 to form an image on the imaging element 344 .

[0072] <Second index optical system> The second index optical system 390 projects an index onto the subject's eye. The second index optical system 390 includes, for example, a light source 391, a projection lens 392, and a beam splitter 393. Infrared light projected from the light source 391 via the projection lens 392 is reflected by the beam splitter 393 and projected onto the subject's eye from the front. A corneal bright spot formed on the corneal apex by the light source 391 is imaged on the image sensor 344 of the second observation optical system 340 and is used for detecting alignment in the up, down, left, and right directions.

[0073] <Deformation detection optical system> The deformation detection optical system 350 includes a light projecting optical system 350a and a light receiving optical system 350b, and is used to detect the deformation state of the cornea Ec.

[0074] The light projecting optical system 350a has an optical axis L13 as a light projecting optical axis, and irradiates illumination light from an oblique direction toward the cornea Ec of the eye E. The light projecting optical system 350a has, for example, a light source 351, a collimator lens 352, and a beam splitter 353. The light receiving optical system 350b has a photodetector 357, and receives the illumination light reflected by the cornea Ec of the eye E. The light receiving optical system 350b is disposed approximately symmetrically to the light projecting optical system 350a with respect to the optical axis L11. 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 L12 as a light receiving optical axis.

[0075] The light (e.g., infrared light) emitted from the light source 351 is made into a substantially parallel beam by the collimator lens 352, and after being reflected by the beam splitter 353, becomes coaxial (coincident) with the optical axis L23 of the light receiving optical system 370b described later, and is projected onto the cornea Ec of the subject's eye. The light reflected by the cornea Ec becomes coaxial (coincident) with the optical axis L12 of the light projecting optical system 370a described later, passes through the lens 354, is reflected by the beam splitter 355, passes through the pinhole plate 356, and is received by the photodetector 357. The lens 354 is coated with a coating that is opaque to the light from the light source 381 and the light source 391. The deformation detection optical system 350 is disposed so that the amount of light received by the photodetector 357 is maximized when the subject's eye is in a predetermined deformation state (e.g., applanation state).

[0076] This deformation detection optical system 350 also serves as a part of a first working distance detection system 360b, and the light projecting optical system of the first working distance detection system also serves as the light projecting optical system 350a of the deformation detection optical system 350. The first working distance detection system 360b, which receives light reflected by the cornea Ec from the light source 351, has, for example, the lens 354, beam splitter 358, condenser lens 359, and position detection element 360 of the light projecting optical system 350a, and forms an optical axis L12 as a light receiving optical axis.

[0077] Illumination light projected from the light source 351 and reflected by the cornea Ec forms an index image, which is a virtual image of the light source 351. The light of the index 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 a line sensor. When the subject's eye E (cornea Ec) moves in the working distance direction (Z direction), the index image formed by the light source 351 also moves on the position detection element 360, so that the control unit 70 obtains working distance information based on the output signal from the position detection element 360. Note that the output signal from the position detection element 360 in 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 described later. Therefore, the distance detection range of the position detection element 360 in the Z direction is wider than that of the light receiving element 377.

[0078] <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 subject's eye E. In addition, the light projecting optical system 370a also serves as a part of the deformation detecting optical system 350 and the first working distance detecting system 360b.

[0079] The light projection optical system 370a has an optical axis L12 as a light projection optical axis, and irradiates illumination light (measurement light) from an oblique direction toward the cornea Ec of the subject's eye E. The light 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 the deformation detection optical system. A visible light source or an infrared light source (including near-infrared) is used as the light source 371, and a light source such as an LED or a laser is used. The condenser lens 372 condenses the light emitted from the light source 371.

[0080] The light limiting member 373 is disposed in the optical path of the light projecting optical system 370a and limits the light emitted from the light source 371. The light limiting member 373 is disposed at a position approximately conjugate with the cornea Ec. For example, a pinhole plate, a slit plate, or the like is used as the light limiting member 373. The light limiting member 373 is used as an aperture that passes a portion of the light emitted from the light source 371 and blocks the other light. The light projecting optical system 370a forms a predetermined pattern light beam (for example, a spot light beam, a slit light beam) on the cornea of ​​the subject's eye E.

[0081] The light receiving optical system 370b has a light receiving element 377 and receives the illumination light reflected by the front and back surfaces of the cornea of ​​the subject's eye E. The light receiving optical system 370b is disposed approximately symmetrically with the light projecting optical system 370a with respect to the optical axis L11. 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 L13 as a light receiving optical axis. The light receiving optical system 370b in FIG. 5 also serves as a second working distance detection system that detects an alignment state in the Z direction with respect to the subject's eye E.

[0082] 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. For example, a light detection device such as a one-dimensional line sensor or a two-dimensional area sensor is used for the light receiving element 377. The corneal thickness measurement optical system and the light receiving optical system 370b of the second working distance detection system perform observation with a large magnification. 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.

[0083] When the test eye E (cornea Ec) moves in the working distance direction (Z direction), the reflected light of the light source 371 on the cornea Ec also moves on the light receiving element 377, and the control unit 70 obtains working distance information based on the output signal from the light receiving element 377 of the second working distance detection system.

[0084] Light emitted from the light source 371 is collected by the collecting lens 372 and illuminates the light limiting member 373 from behind. Then, the light from the light source 371 is limited by the light limiting member 373, and then imaged (collected) near the cornea Ec by the lens 354. For example, a pinhole image (when a pinhole plate is used) or a slit image (when a slit plate is used) is formed near the cornea Ec. At this time, the light from the light source 371 is imaged near the intersection with the visual axis on the cornea Ec.

[0085] When illumination light is projected onto the cornea Ec by the light projecting optical system 370a, the illumination light reflected by the cornea Ec travels in a direction symmetrical to the projected light beam with respect to the optical axis L11. The reflected light is then imaged on the light receiving surface of the light receiving element 377 by the light receiving lens 375.

[0086] <Control Unit> 6 is a schematic diagram of a control system of the ophthalmic apparatus. The control unit 70 includes a CPU (processor), RAM, ROM, etc. The CPU controls the driving of each part in the intraocular pressure measuring device 1. The RAM temporarily stores various information. The ROM stores various programs executed by the CPU, etc. The control unit 70 may be composed of multiple control units (i.e., multiple processors).

[0087] The control unit 70 is electrically connected to the first measurement unit 3a, the second measurement unit 3b, the face support unit 4, the drive unit 5, the speaker 6, the display unit 75, the operation unit 76, the fluid discharge unit 200, the intraocular pressure measurement unit 300, the face photographing unit 400, the corneal shape distribution measurement unit 500, a non-volatile memory 74 (hereinafter, memory 74), and the like. The memory 74 is a non-transient storage medium that can retain the stored contents even if the power supply is cut off. For example, the memory 74 may be a hard disk drive, a flash ROM, a USB memory, or the like. The memory 74 may store the measurement results of the subject's eye E, the limit position Lim (first limit position Lim1 to third limit position Lim3) described later, and the like.

[0088] <Measurement unit movement range and limit positions> In this embodiment, in order to prevent contact between the subject's eye and the measurement unit 3, limit positions are set for the forward movement (movement toward the subject's eye) of the measurement unit 3 by the drive unit 5. For example, a limit position when the first measurement unit 3a is not attached to an attachment, a limit position when the first measurement unit 3a is attached to an attachment, and a limit position of the second measurement unit 3b (more specifically, the fluid discharge unit 200) are each set.

[0089] FIG. 7 is a diagram showing a schematic view of the movable range and limit positions of the measurement unit 3. FIG. 7(a) shows the first limit position Lim1 when the attachment of the first measurement unit 3a is not attached. FIG. 7(b) shows the second limit position Lim2 when the attachment of the first measurement unit 3a is attached. FIG. 7(c) shows the third limit position Lim3 of the second measurement unit 3b. FIG. 7(d) shows the positional relationship between the subject's eye and the first limit position Lim1 to the third limit position Lim2. In FIG. 7, the position where the measurement unit 3 is most retreated in the Z direction is the initial position (reference position 21) for the forward movement of the measurement unit 3, and the position where the measurement unit 3 is most advanced in the Z direction is the limit position 22 for the forward movement of the measurement unit 3. That is, the measurement unit 3 can move in the front-rear direction within the range from the reference position 21 to the limit position 22 (hereinafter, the movable range 20).

[0090] For example, when the attachment of the first measurement unit 3a shown in FIG. 7(a) is not attached, in order to suppress contact between the subject's eye and the eye examination window 101, the first limit position Lim1 for the first measurement unit 3a is set at a predetermined position within the movable range 20 of the measurement unit 3. For example, the first limit position Lim1 (in other words, the stop position of the forward movement) is set based on the approximate Z-direction position of the subject's eye obtained by a simulation or the like when the subject is supported by the face support unit 4. More specifically, the first limit position Lim1 is set so that the approximate Z-direction position of the subject's eye and the position of the eye examination window 101 maintain a distance D1. Therefore, in this embodiment, when the ocular refractive power of the subject's eye is objectively measured, the maximum position to which the measurement unit 3 can move forward with respect to the subject's eye is the first limit position Lim1.

[0091] 7(b) is attached, in order to prevent contact between the subject's eye and the tip of the attachment 510, a second limit position Lim2 for the first measurement unit 3a is set at a predetermined position within the movable range 20 of the measurement unit 3. For example, a position away from the first limit position Lim1 of the first measurement unit 3a toward the reference position 21 by a distance corresponding to the attachment 510 is set as the second limit position Lim2. Therefore, in this embodiment, when measuring the corneal shape distribution of the subject's eye, the maximum position to which the measurement unit 3 can move forward with respect to the subject's eye is the second limit position Lim2.

[0092] In addition, in the measurement of the subject's eye using the first measurement unit 3a, if an appropriate working distance WD1 (see FIG. 7(a)) from the subject's eye to the eye examination window 101 is the same as an appropriate working distance WD2 (see FIG. 7(b)) from the subject's eye to the opening 522 of the inner tube part 522, the distance D2 between the approximate Z-direction position of the subject's eye and the position of the opening 522a of the inner tube part 522 may be the same as the distance D1, and the second limit position Lim2 may be set by subtracting the distance corresponding to the attachment 510. On the other hand, if the working distance WD1 and the working distance WD2 are different distances, the second limit position Lim2 may be set by subtracting the difference between the working distances and the distance corresponding to the attachment 510.

[0093] For example, in the second measurement unit 3b shown in FIG. 7(c), in order to suppress contact between the test eye and the tip of the nozzle 206 of the fluid discharge unit 200, a third limit position Lim3 for the second measurement unit 3b is set at a predetermined position within the movable range 20 of the measurement unit 3. For example, the second measurement unit 3b is moved forward with respect to the first measurement unit 3a, and the nozzle 206 of the fluid discharge unit 200 is placed at a position protruding from the optometry window 101 of the first measurement unit 3a. In addition, in the measurement of the test eye using the second measurement unit 3b, it is necessary to bring the nozzle 206 closer to the test eye. For this reason, for example, the third limit position Lim3 is set so that the approximate position of the test eye in the Z direction and the position of the tip of the nozzle 206 maintain a distance D3 shorter than the distance D1. Therefore, in this embodiment, when measuring the intraocular pressure of the test eye, the maximum position to which the measurement unit 3 can move forward with respect to the test eye is the first limit position Lim3.

[0094] In this embodiment, as shown in Figure 7 (d), in the direction in which the measurement unit 3 moves forward, the limit positions are set in the following order: the second limit position Lim2 when measuring the corneal shape distribution, the first limit position Lim1 when measuring the ocular refractive power, and the third limit position Lim3 when measuring the intraocular pressure.

[0095] <Control action> The control operation of the ophthalmic apparatus 1 having the above-mentioned configuration will be described. For example, the ophthalmic apparatus 1 measures the subject eye by fully automatically executing the processes from alignment of the subject eye E with the measurement unit 3 to acquisition of various measurement data. In this embodiment, a case will be illustrated in which an ocular refractive power measurement mode for measuring the ocular refractive power of the subject eye, a corneal thickness and intraocular pressure measurement mode for measuring the corneal pressure and intraocular pressure of the subject eye, and a corneal shape distribution measurement mode for measuring the corneal shape distribution of the subject eye are set in this order.

[0096] <Eye refraction measurement mode> For example, when the control unit 70 detects that the subject has placed his / her chin on the chin rest 4b based on the detection result of the chin rest sensor 4c, it sets the eye refractive power measurement mode and sets the first limit position Lim1, outputs a voice announcement from the speaker 6 instructing the subject to fixate the fixation target, and executes alignment. The control unit 70 turns on the light source 131 of the first fixation target optical system 130 in the first measurement unit 3a, the point light source 161 and the light source 162 of the first index optical system 160, and the illumination light source 411 of the face photographing optical system 420 in the second measurement unit 3b. This illuminates the face of the subject, and a facial image of the subject is captured. The control unit 70 causes the display unit 75 to display the facial image.

[0097] FIG. 8 is an example of an examination screen 700 including a face image 701 of the subject's eye. For example, the examination screen 700 displays the face image 701, a setting change button 702, a movable range gauge 703, a first limit position mark 704, a current position mark 705, and the like. The face image 701 is a photographed image photographed in real time by the image sensor 422 of the face photographing optical system 420. The setting change button 702 is a plurality of buttons for changing various settings in the measurement of the subject's eye (for example, selection of the subject's eye (measurement eye) and the like). The movable range gauge 703 is a gauge representing the movable range 20 (see FIG. 7) of the measurement unit 3. For example, the lower end of the movable range gauge 703 represents a position corresponding to the reference position 21 when the measurement unit 3 is moved most backward in the Z direction, and the upper end of the movable range gauge 703 represents a position corresponding to the limit position 22 when the measurement unit 3 is moved most forward in the Z direction. The first limit position mark 704 is a mark that indicates the position of the first limit position Lim1 relative to the movable range 20 of the measurement unit 3. The current position mark 705 is a mark that indicates the current position of the measurement unit 3 relative to the movable range 20 of the measurement unit 3.

[0098] The control unit 70 moves the first measurement unit 3a in the X, Y, and Z directions relative to the subject's eye. For example, the control unit 70 moves the measurement unit 3 in the X and Y directions so that the first measurement unit 3a is positioned in front of the subject's eye (measurement eye). Also, for example, the control unit 70 moves the measurement unit 3 in the Z direction so that the first measurement unit 3a approaches the subject's eye (measurement eye).

[0099] For example, the control unit 70 determines the amount of forward movement of the measurement unit 3 from the reference position 21 based on the drive amount of the drive unit 5, and converts the amount of movement (actual distance) of the measurement unit 3 into a relative distance with respect to the movable range gauge 703. In addition, for example, the control unit 70 gradually moves the display position of the current position mark 705 from the bottom end to the top end in accordance with the change in such relative distance that is successively updated as the measurement unit 3 moves forward.

[0100] Here, the forward movement of the measurement unit 3 relative to the subject's eye is set to a limit position Lim1 when performing eye refractive power measurement. For example, if the subject's eye is not properly detected from the face image 701, the measurement unit 3 continues to move forward, but when the measurement unit 3 reaches the limit position Lim1, the forward movement of the measurement unit 3 is automatically stopped. That is, when the display position of the first limit position mark 704 of the movable range gauge 703 and the display position of the current position mark 705 match, the forward movement of the measurement unit 3 is automatically stopped. This makes it possible to appropriately suppress contact between the subject and the first measurement unit 3a. In addition, the examiner can easily grasp the positional relationship between the first limit position Lim1 and the current position of the first measurement unit 3a by checking the movable range gauge 703, etc.

[0101] On the other hand, for example, when the subject's eye is detected from the face image 701, the measurement unit 3 moves forward based on the three-dimensional position information of the subject's eye. When the first measurement unit 3a approaches the subject's eye, an anterior eye image of the subject's eye is captured by the imaging element 151. When the control unit 70 acquires the anterior eye image 706 of the subject's eye, it shifts from rough alignment using the face image 701 of the subject's eye to fine alignment using the anterior eye image 706. In addition, the control unit 70 switches the face image 701 on the examination screen 700 to the anterior eye image 706 for display.

[0102] FIG. 9 is an example of an examination screen 720 including an anterior eye image 706 of the subject's eye. The anterior eye image 706 is a photographed image photographed in real time by the image sensor 124 of the first observation optical system 150. The anterior eye image 706 also includes a point image and a Mayer ring image projected by the first target optical system 160. The control unit 70 uses the point image and the Mayer ring image of the anterior eye image 706 to move the first measurement unit 3a in the XYZ directions. For example, the control unit 70 moves the measurement unit 3 in the XY directions so that the pupil of the subject's eye and the optical axis of the first measurement unit 3a coincide with each other. Also, for example, the control unit 70 moves the measurement unit 3 in the Z direction so that the working distance WD1 between the subject's eye and the first measurement unit 3a is an appropriate working distance. Furthermore, for example, the control unit 70 determines the amount of forward movement of the measurement unit 3 based on the drive amount of the drive unit 5, and converts the amount of movement of the measurement unit 3 into a relative distance with respect to the movable range gauge 703, thereby gradually moving the display position of the current position mark 705 relative to the movable range gauge 703. Note that when the measurement unit 3 reaches the first limit position Lim1, the forward movement of the measurement unit 3 may be automatically stopped.

[0103] When the distance between the eye and the first measurement unit 3a becomes an appropriate working distance WD1, the control unit 70 completes fine alignment of the measurement unit 3 with respect to the eye. Based on an input signal indicating completion of alignment of the eye, the control unit 70 controls the first measurement optical system 100 to measure the ocular refractive power of the eye. More specifically, the control unit 70 irradiates the fundus of the eye with measurement light, and measures the ocular refractive power of the eye based on a detection result of the measurement light reflected by the fundus.

[0104] <Corneal thickness / intraocular pressure measurement mode> When the control unit 70 acquires the measurement result of the ocular refractive power of the subject's eye, the control unit 70 transitions to a corneal thickness / intraocular pressure measurement mode and sets a third limit position Lim3. For example, as described above, the third limit position Lim3 is set in consideration of the approach between the subject's eye and the nozzle 206 and the protrusion of the nozzle 206.

[0105] 10 is an example of an examination screen 730 including an anterior eye image 707 of an eye to be examined. For example, the control unit 70 displays a third limit position mark 708 in the movable range gauge 703 as a result of changing the setting from the first limit position Lim1 to the third limit position Lim3. As an example, the first limit position mark 704 may be moved and displayed as the third limit position mark 708. As another example, the first limit position mark 704 may be hidden and the third limit position mark 708 may be newly displayed. Of course, the third limit position mark 708 may be displayed while the first limit position mark 704 is still displayed.

[0106] For example, the control unit 70 causes the measurement unit 3 to move backward by controlling the drive unit 5, and causes the nozzle 206 of the fluid discharge unit 200 to protrude by controlling a drive unit (not shown). At the same time, for example, the control unit 70 causes the measurement unit 3 to move downward by a predetermined distance by controlling the drive unit 5, and adjusts the height so that the optical axis L11 of the second measurement unit 3b is aligned with the subject's eye. Then, the control unit 70 turns on the light source 331 of the second fixation target optical system 330 and the light sources 381 and 391 of the second observation optical system 340. This illuminates the anterior eye of the subject, and an image of the anterior eye of the subject is captured. The control unit 70 causes the display unit 75 to display the anterior eye image.

[0107] FIG. 11 is an example of an examination screen 740 including an anterior eye image 709 of the subject's eye. The anterior eye image 709 is a captured image captured in real time by the imaging element 344 of the second observation optical system 340. The anterior eye image 709 also includes a corneal bright spot image projected by the second target optical system 390. The control unit 70 uses the corneal bright spot image of the anterior eye image to perform alignment in the XY direction of the second measurement unit 3b. As an example, the control unit 70 moves the measurement unit 3 in the XY direction so that the corneal apex of the subject's eye coincides with the optical axis of the second measurement unit 3b. The control unit 70 also turns on the light source 351 of the deformation detection optical system 350 and the light source 371 of the light projection optical system 370a, and performs alignment in the Z direction based on the light reception results of the position detection element 360 and the light receiving element 377. As an example, the control unit 70 moves the measurement unit 3 in the Z direction so that the distance between the eye and the second measurement unit 3b is an appropriate working distance WD3. At this time, as the measurement unit 3 moves forward, the display position of the current position mark 705 relative to the movable range gauge 703 gradually moves.

[0108] For example, if a corneal bright spot image is not successfully detected from the anterior eye image 709, the measurement unit 3 continues to move forward, but when the measurement unit 3 reaches the third limit position Lim3, the forward movement of the measurement unit 3 is automatically stopped. In other words, when the display position of the third limit position mark 708 of the movable range gauge 703 coincides with the display position of the current position mark 705, the forward movement of the measurement unit 3 is automatically stopped. This makes it possible to appropriately suppress contact between the subject and the second measurement unit 3b (e.g., the nozzle 206), and to easily grasp the positional relationship between the third limit position Lim3 of the second measurement unit 3b and the current position. On the other hand, for example, if a corneal bright spot image is detected from the anterior eye image 709, the measurement unit 3 is moved in the Z direction based on the corneal bright spot image so that the working distance WD3 between the subject's eye and the second measurement unit 3b is an appropriate working distance.

[0109] When the distance between the eye and the second measurement unit 3b becomes an appropriate working distance WD3, the control unit 70 completes the alignment of the measurement unit 3 with respect to the eye. Based on an input signal indicating the completion of the alignment of the eye, the control unit 70 sequentially performs the corneal pressure measurement and the intraocular pressure measurement of the eye. For example, the control unit 70 controls the corneal thickness measurement optical system 370 to calculate the distance (peak-to-peak distance) between the reflection signal at the front surface of the cornea and the reflection signal at the rear surface of the cornea detected by the light receiving element 377. Next, for example, the control unit 70 controls the fluid discharge unit 200 to drive the solenoid 203 to move the piston 202, thereby compressing the air in the cylinder 201 and blowing the compressed air from the nozzle 206. Based on the output signal from the pressure sensor 212 and the output signal from the photodetector 57 when the cornea gradually deforms due to the blowing of the compressed air and reaches a flat (or applanation) state, the control unit 70 measures the intraocular pressure value.

[0110] <Corneal shape distribution measurement> When the control unit 70 acquires the measurement results of the corneal pressure and intraocular pressure value of the subject's eye, it transitions to a corneal shape distribution measurement mode and sets the second limit position Lim2. For example, as described above, the second limit position Lim2 is set in consideration of the attachment 510 being attached between the subject's eye and the optometry window 101. Note that, for example, the control unit 70 displays the second limit position mark 710 in the movable range gauge 703 due to the setting being changed from the third limit position Lim3 to the second limit position Lim2 (see FIG. 13).

[0111] FIG. 12 is a diagram for explaining the retraction of the measurement unit 3 and the attachment 510. For example, the control unit 70 retracts the measurement unit 3 by controlling the drive unit 5, and disposes the attachment 510 from the retracted position to the measurement position. For example, the control unit 70 retracts the measurement unit 3 to a position Z2 that sufficiently avoids the possibility of the attachment 510 coming into contact with the subject's face, relative to the position Z1 during eye refractive power measurement. Also, for example, the control unit 70 controls the insertion / removal drive unit 550 to move the attachment 510 in front of the eye examination window 101 (measurement position). Furthermore, for example, when the control unit 70 detects that the attachment 510 is attached, The point light source 161 and the light source 162 of the first target optical system 160 are turned on. This illuminates the anterior eye of the subject, and an image of the anterior eye of the subject is captured. The control unit 70 causes the display unit 75 to display the anterior eye image.

[0112] 13 is an example of an examination screen 750 including an anterior eye image 711 of an eye to be examined. The anterior eye image 711 is a photographed image photographed in real time by the imaging element 151 of the first observation optical system 150. The anterior eye image 711 also includes a Placido ring index image 712 formed by light emitted from the point light source 161 and the light source 162 passing through the pattern index plate 163, the transmission portion 534, and the slit portion 524. The control unit 70 uses the Placido ring index image 712 of the anterior eye image 711 to perform alignment in the XY directions of the first measurement unit 3a to which the attachment 510 is attached. As an example, the control unit 70 performs alignment in the XY directions by moving the first measurement unit 3a in the XY directions so that the ring center of the innermost ring image of the Placido ring index image 712 is aligned with the ring center 713 of the target mark. The control unit 70 also performs alignment in the Z direction based on the image interval between the point images captured by the imaging element 151 of the first observation optical system 150 and the image interval between the innermost ring images of the Placido ring index image 712. As an example, the control unit 70 moves the measurement unit 3 in the Z direction so that an appropriate working distance WD2 is established between the subject's eye and the attachment 510. At this time, as the measurement unit 3 moves forward, the display position of the current position mark 705 relative to the movable range gauge 703 gradually moves.

[0113] For example, if at least one of the point image and the Placido ring index image is not successfully detected from the anterior eye image 711, the measurement unit 3 continues to move forward, but when the measurement unit 3 reaches the second limit position Lim2, the forward movement of the measurement unit 3 is automatically stopped. In other words, when the display position of the second limit position mark 710 of the movable range gauge 703 and the display position of the current position mark 705 match, the forward movement of the measurement unit 3 is automatically stopped. This makes it possible to appropriately suppress contact between the subject and the first measurement unit 3a (for example, the attachment 510), and to easily grasp the positional relationship between the second limit position Lim2 of the first measurement unit 3a and the current position. On the other hand, for example, if both the point image and the Placido ring index image are detected from the anterior eye image 711, the measurement unit 3 is moved in the Z direction based on the detection result so that the subject's eye and the first measurement unit 3a are at an appropriate working distance WD2.

[0114] For example, when the distance between the eye and the attachment 510 becomes an appropriate working distance WD2, the control unit 70 completes the alignment of the measurement unit 3 with respect to the eye. For example, the control unit 70 controls the first measurement optical system 100 based on an input signal indicating the completion of the alignment of the eye to measure the corneal shape distribution. More specifically, the control unit 70 captures a Placido ring image by photographing the eye to measure the corneal shape distribution by analyzing the Placido ring image in each meridian direction. The corneal shape distribution may be expressed as a corneal shape map, a color-coded color map, a contour map, or the like.

[0115] For example, when the control unit 70 acquires measurement results such as the ocular refractive power, corneal thickness, intraocular pressure, and corneal shape distribution of the subject's eye, the control unit 70 outputs the measurement results (measurement data) to the display unit 75 and stores them in the memory 74.

[0116] As described above, for example, the ophthalmic apparatus of this embodiment sets a first limit position of the forward movement of the inspection means when the attachment is not attached, and sets a second limit position of the forward movement of the inspection means when the attachment is attached, which is changed from the first limit position by a distance corresponding to the attachment, and controls the moving means for changing the relative positional relationship between the subject's eye and the inspection means based on the second limit position when the attachment is attached. For example, some ophthalmic apparatuses can test the eye characteristics of the subject's eye under different conditions or test a plurality of different eye characteristics of the subject's eye by switching between not attaching and attaching the attachment. Therefore, for example, the limit position set so that the inspection means does not come into contact with the subject is changed according to the attachment being attached or detached, thereby reducing the troublesomeness of the examiner resetting the limit position of the inspection means each time.

[0117] In addition, for example, the ophthalmologic apparatus of the present embodiment displays the movable range of the forward movement of the inspection means and at least the second limit position for the movable range, so that, for example, the examiner can visually determine whether the second limit position is appropriate for the subject's eye.

[0118] In addition, for example, the ophthalmic device of this embodiment detects the attachment of the attachment to the ophthalmic device, and changes the first limit position to the second limit position based on the detection signal, thereby improving the operability of the device, for example, and making it easy to set the second limit position.

[0119] Also, for example, the ophthalmologic apparatus of this embodiment acquires a photographed image of the subject's eye, and displays a gauge indicating the movable range of the forward movement of the inspection means and the limit position by superimposing the gauge on the photographed image. For example, this allows the examiner to intuitively grasp the relationship between the movable range of the inspection means and the limit position. Also, for example, the examiner can easily fine-tune the first limit position or the second limit position while checking the movable range and limit position of the inspection means.

[0120] In addition, for example, the ophthalmologic apparatus of the present embodiment displays the current position of the inspection means in real time relative to the movable range of the forward movement of the inspection means, which allows the examiner to easily determine whether the limit position of the inspection means relative to the subject's eye is appropriate.

[0121] Also, for example, in the ophthalmologic apparatus of the present embodiment, the examination means includes an eye refraction measuring means for projecting a measurement light beam onto the fundus of the eye to measure the eye refraction of the eye based on the reflected light beam of the measurement light beam reflected by the fundus, and an intraocular pressure measuring means having a fluid ejection means for ejecting a fluid onto the cornea of ​​the eye to measure the intraocular pressure by deforming the cornea with the fluid, the attachment is attached to the eye refraction measuring means to add a corneal shape distribution measuring means for measuring the corneal shape distribution of the eye to the eye refraction measuring means, and the setting means sets a first limit position for the forward movement of the eye refraction measuring means, a second limit position for the forward movement of the corneal shape distribution measuring means, and a third limit position for the forward movement of the fluid ejection means, respectively. For example, this reduces the trouble of setting the limit positions every time the examination item changes.

[0122] <Example of transformation> The ophthalmologic apparatus of the present embodiment has been described with an example of a configuration in which the limit position when each measurement mode is executed on the subject's eye is a preset position, but is not limited thereto. For example, the limit position when each measurement mode is executed on the subject's eye may be finely adjusted by the examiner. For example, in this case, the examiner may be able to set an arbitrary limit position after starting measurement of the subject's eye in accordance with the shape of the subject's face, etc. Also, for example, in this case, the examiner may be able to set an arbitrary limit position before starting measurement of the subject's eye in accordance with the shape of the subject's face, etc.

[0123] Hereinafter, the setting of the limit position after the start of the eye refractive power measurement of the subject's eye will be described as an example. FIG. 14 is an example of an examination screen 760 including an anterior eye image 706 of the subject's eye. For example, the examination screen 760 may display a limit position change tab 714 in addition to the movable range gauge 703, the first limit position mark 704, the current position mark 705, and the like. The limit position change tab 714 is a tab for changing the display position of the first limit position mark 704. For example, when the tab is operated to slide up or down, the first limit position mark 704 moves in conjunction with the sliding direction. In addition, the first limit position Lim1 for the movable range 20 of the measurement unit 3 is also changed appropriately accordingly.

[0124] FIG. 15 is a diagram showing the relationship between the first limit position Lim1 and the working distance WD1 depending on the difference in the face shape of the subject. FIG. 15(a) shows a case where the face shape of the subject is standard. FIG. 15(b) shows a case where the face shape of the subject is deeply carved (the subject's eye is deep-set). For example, when the face shape of the subject is standard, the subject's eye is placed at a predetermined position in the Z direction, so that the appropriate working distance WD1 from the subject's eye to the first measurement unit 3a (eye examination window 101) is longer than the distance D1 from the subject's eye to the first limit position Lim1. Therefore, for example, if the subject's eye can be detected from the face image 701, the relative positions of the subject's eye and the first measurement unit 3a will be at the appropriate working distance WD1 before the first measurement unit 3a moves forward and reaches the first limit position Lim1, and the alignment in the Z direction can be completed. Furthermore, even if the subject's eye cannot be detected from the face image 701 and the first measurement unit 3a moves forward beyond the working distance WD, the first measurement unit 3a is stopped at the first limit position Lim1. Therefore, contact between the subject and the first measurement unit 3a is suppressed.

[0125] However, for example, when the face shape of the subject is deeply chiseled, the subject's eye is located further back than a predetermined position in the Z direction, so that the appropriate working distance WD1 from the subject's eye to the first measurement unit 3a (eye examination window 101) is shorter than the distance D1 from the subject's eye to the first limit position Lim1. For this reason, even if the subject's eye can be detected from the face image 701, the first measurement unit 3a moves forward and reaches the first limit position Lim1 first, so that the relative positions of the subject's eye and the first measurement unit 3a do not become the appropriate working distance WD1, and the alignment in the Z direction cannot be completed. Therefore, for example, the examiner may operate the limit position change tab 714 to move the display position of the first limit position mark 704 in a direction closer to the subject's eye. For example, the control unit 70 re-sets the first limit position Lim1 for the movable range 20 of the measurement unit 3 based on the amount of movement of the limit position mark 704. For example, if the appropriate working distance WD1 becomes longer than the distance D1, when the first measurement unit 3a moves forward again, the appropriate working distance WD1 will be reached before the first limit position Lim1 is reached, so that alignment in the Z direction can be completed. If the examiner finds that the forward movement of the first measurement unit 3a is insufficient after one adjustment using the limit position change tab 714, he or she may further operate the tab to repeat fine adjustment.

[0126] In contrast to a case where the face of the subject is normal, when the face of the subject is shallowly contoured (when the subject has protruding eyes), the distance D1 from the subject's eye to the first limit position Lim1 becomes shorter, and the subject's eye is more likely to come into contact with the first measurement unit 3a when the subject's eye cannot be detected from the face image 701. For this reason, for example, the examiner may operate the limit position change tab 714 in advance before starting measurement of the subject's eye to move the display position of the first limit position mark 704 in a direction away from the subject's eye, thereby resetting the first limit position Lim1.

[0127] In this way, for example, the ophthalmic apparatus of this embodiment changes the first limit position and the second limit position based on an operation signal for finely adjusting the limit position of the forward movement of the inspection means relative to the subject's eye. For example, the limit position of the forward movement of the inspection means may be set in advance so that the inspection means does not come into contact with the subject. However, for example, when the subject's face is large, the subject's eye is placed forward (apparatus side) of the expected inspection position, and when the subject's eye cannot be detected properly, the inspection means may come into contact with the limit position before reaching the limit position. Also, for example, when the subject's face is small, or when the subject's face is deeply carved and the eyes are set deep inside, the subject's eye is placed backward (opposite side of the apparatus) of the expected inspection position, and the inspection means may reach the limit position before detecting the subject's eye, and the subject's eye may not be detected properly. For this reason, for example, the examiner can finely adjust the limit position arbitrarily according to the subject, thereby smoothly performing alignment.

[0128] In the ophthalmologic apparatus of this embodiment, the first limit position Lim1 in the eye refractive power measurement mode that is reset by the examiner using the limit position change tab 714 may be linked to an ID or the like for each examinee and stored in the memory 74. Of course, when the second limit position Lim2 in the corneal thickness / intraocular pressure measurement mode, the third limit position Lim3 in the intraocular pressure measurement mode, etc. are changed again, these limit positions may also be linked to an ID or the like for each examinee and stored in the memory 74. In this case, when the examinee's eye is examined at a different date and time, the previous limit position may be called up from the examinee's ID, and the setting may be automatically reflected.

[0129] In this manner, for example, the ophthalmologic apparatus of this embodiment stores at least one of the first limit position and the second limit position after a change (fine adjustment) in the forward movement of the examination means, and sets at least one of the stored first limit position and the second limit position on a different examination date of the subject's eye. For example, this allows the limit position once determined for a specific subject to be easily recalled, thereby reducing the trouble of setting the limit position every time the examination date changes.

[0130] The ophthalmologic apparatus of the present embodiment has been described with reference to an example in which one limit position mark corresponding to the set measurement mode is displayed on the examination screen 700, but is not limited thereto. For example, a configuration in which a plurality of limit position marks corresponding to each measurement mode are displayed on the examination screen 700 may be used. As an example, a first limit position mark 704 corresponding to the eye refractive power measurement mode, a second limit position mark 709 corresponding to the corneal thickness / intraocular pressure measurement mode, and a third limit position mark 708 corresponding to the intraocular pressure measurement mode may be displayed on the examination screen 700 together with the movable range gauge 703. In such a case, the limit position marks may be color-coded or the like so that they can be distinguished from one another. This makes it easier to visually determine the limit positions of the measurement unit 3 set in each measurement mode. [Explanation of symbols]

[0131] 1 Ophthalmology equipment 70 Control section 100 1st measurement optical system 200 Fluid discharge section 300 Second measurement optical system 400 Face Photography Section 500 Corneal shape distribution measurement section 510 Attachment

Claims

1. An ophthalmic device for examining the eye under examination, An ophthalmic device capable of attaching an attachment for examining the ocular characteristics of the eye under examination, An examination means for examining the ocular characteristics of the eye under examination, A means for changing the relative positional relationship between the eye under examination and the examination means, A setting means for setting the limit position of the forward movement of the examination means relative to the eye being examined, A control means controls the moving means based on the limit position set by the setting means in order to move the examination means forward relative to the eye being examined. Equipped with, The setting means sets a first limit position when the attachment is not attached, and sets a second limit position when the attachment is attached, which is a second limit position that is changed from the first limit position by a distance corresponding to the attachment. The ophthalmic device is characterized in that the control means controls the moving means based on the second limit position set by the setting means when the attachment is mounted.

2. In the ophthalmic device according to claim 1, An ophthalmic apparatus characterized by comprising a display control means that displays the range of motion of the forward movement of the inspection means and at least the second limit position relative to the range of motion on a display means.

3. In the ophthalmic device according to claim 1 or 2, The device includes a detection means for detecting the attachment of the attachment to the ophthalmic device, The setting means is characterized by changing the first limit position to the second limit position based on the detection signal from the detection means.

4. In the ophthalmic device according to claim 1, The system includes an operating means for finely adjusting the limit position of the forward movement of the examination means relative to the eye being examined, The setting means is characterized by changing the first limit position and the second limit position based on an operation signal from the operating means.

5. In the ophthalmic device of claim 1, The system includes means for acquiring images of the eye being examined, The ophthalmic apparatus is characterized in that the display control means displays a gauge representing the movable range of the forward movement of the inspection means and the limit position superimposed on the captured image.

6. In the ophthalmic device of claim 1, The aforementioned inspection means is A refractive power measuring means that projects a measuring light beam onto the fundus of the eye under examination and measures the refractive power of the eye under examination based on the reflected light beam that is reflected from the fundus of the eye under examination, An intraocular pressure measuring means having a fluid discharge means for discharging fluid onto the cornea of ​​the eye under examination, and which measures intraocular pressure by deforming the cornea with the fluid, Equipped with, The attachment is attached to the refractive power measuring means, thereby adding a corneal shape distribution measuring means to the refractive power measuring means for measuring the corneal shape distribution of the eye under examination. The ophthalmic apparatus is characterized in that the setting means sets the first limit position for the forward movement of the refractive power measuring means, the second limit position for the forward movement of the corneal shape distribution measuring means, and the third limit position for the forward movement of the fluid discharge means, respectively.

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