Ophthalmologic apparatus and operation method of ophthalmologic apparatus

Abstract

To provide an ophthalmologic apparatus capable of easily discriminating reliability of an ophthalmic characteristic acquisition result for an eye to be examined, and to provide an operation method of the ophthalmologic apparatus.SOLUTION: An ophthalmologic apparatus 1 equipped with an ophthalmic characteristic acquisition unit (measurement head 5) for acquiring ophthalmic characteristics of an eye E to be examined includes: a vibration detection unit (acceleration sensor 28) for detecting vibration of the ophthalmologic apparatus at least while ophthalmic characteristics are being acquired by the ophthalmic characteristic acquisition unit; and a reliability evaluation unit 48 for evaluating reliability of an acquisition result for the ophthalmic characteristics acquired by the ophthalmic characteristic acquisition unit on the basis of a result of the detection by the vibration detection unit.SELECTED DRAWING: Figure 5

Description

[Technical field]

[0001] The present invention relates to an ophthalmic apparatus for acquiring ocular characteristics of a subject's eye and an operation method of the ophthalmic apparatus. [Background technology]

[0002] In ophthalmology, an ophthalmic device is used to obtain (measure, photograph, observe, etc.) various eye characteristics of a subject's eye, such as the ocular refractive power, corneal shape, intraocular pressure, and number of corneal endothelial cells. Patent Document 1 discloses a handheld ophthalmic device. This ophthalmic device includes an acceleration sensor and an image stabilization optical system that corrects the examiner's hand shake based on the detection result of the acceleration sensor. [Prior art documents] [Patent documents]

[0003] [Patent Document 1] International Publication No. 2013 / 098981 Summary of the Invention [Problem to be solved by the invention]

[0004] However, if vibration occurs in the ophthalmic device during acquisition of the ocular characteristics of the subject's eye, the reliability of the acquisition result of the ophthalmic characteristics by the ophthalmic device decreases. However, it is difficult for the examiner to determine whether the acquisition result of the ophthalmic characteristics of the subject's eye is acquired while the ophthalmic device is vibrating or while the device is stationary, that is, to determine whether the acquisition result of the ophthalmic characteristics of the subject's eye is unreliable. Therefore, when vibration occurs in the ophthalmic device, it is necessary to wait until the vibration stops before acquiring the ophthalmic characteristics of the subject's eye.

[0005] Although it is possible to provide an image stabilization optical system as in the ophthalmic apparatus described in Patent Document 1, there are cases where an image stabilization optical system cannot be installed due to installation space restrictions. In addition, even if an image stabilization optical system is provided in the ophthalmic apparatus, there are cases where the vibration of the ophthalmic apparatus cannot be completely canceled. Therefore, even in the ophthalmic apparatus described in Patent Document 1, it is still difficult to determine whether the reliability of the acquired results of the eye characteristics of the subject eye is low.

[0006] The present invention has been made in consideration of the above circumstances, and aims to provide an ophthalmic apparatus and an operating method for an ophthalmic apparatus that can easily determine the reliability of the results of obtaining the eye characteristics of a subject's eye. [Means for solving the problem]

[0007] An ophthalmic apparatus for achieving the object of the present invention is an ophthalmic apparatus equipped with an ophthalmic characteristic acquisition unit that acquires the ophthalmic characteristics of a test eye, and is equipped with a vibration detection unit that detects vibrations of the ophthalmic apparatus at least while acquisition of the ophthalmic characteristics is being performed by the ophthalmic characteristic acquisition unit, and a reliability evaluation unit that evaluates the reliability of the acquisition results of the ophthalmic characteristics acquired by the ophthalmic characteristic acquisition unit based on the detection result of the vibration detection unit.

[0008] According to this ophthalmologic apparatus, it is possible to evaluate the reliability of the acquired results of the eye characteristics based on the detection result of the vibration detection unit.

[0009] In the ophthalmologic apparatus according to another aspect of the present invention, a notification unit is provided that notifies an examiner of warning information when the reliability evaluation unit evaluates the reliability as low, thereby notifying an examiner that the reliability of the acquired results of the eye characteristics is low.

[0010] In an ophthalmologic apparatus according to another aspect of the present invention, a display unit is provided that displays the results acquired by the ophthalmic characteristic acquisition unit, and a display control unit is provided that causes only the results evaluated as having high reliability by the reliability evaluation unit to be displayed on the display unit, thereby making it possible to present only the results of the highly reliable ophthalmic characteristics to the examiner.

[0011] In the ophthalmologic apparatus according to another aspect of the present invention, a selection unit is provided that keeps acquired results that have been evaluated as having high reliability by the reliability evaluation unit and deletes acquired results that have been evaluated as having low reliability by the reliability evaluation unit, thereby making it possible to present only acquired results of eye characteristics with high reliability to the examiner.

[0012] In an ophthalmologic apparatus according to another aspect of the present invention, the ocular characteristic acquisition unit includes an objective lens, a measurement light source that projects measurement light onto the subject's eye, an image sensor that captures return light from the subject's eye onto which the measurement light is projected, and an alignment detection system that detects the relative position of the subject's eye with respect to the ocular characteristic acquisition unit, and the vibration detection unit is provided at a mounting position of at least one of the objective lens, the measurement light source, the image sensor, and the alignment detection system. This makes it possible to evaluate the reliability of the acquisition result of the ocular characteristic based on the detection result of the vibration detection unit.

[0013] In the ophthalmologic apparatus according to another aspect of the present invention, the vibration detection unit is provided at the mounting position via a flexible mounting member, whereby the magnitude of vibration detected by the vibration detection unit can be increased, thereby further improving the accuracy of the reliability evaluation of the acquired results of eye characteristics.

[0014] In an ophthalmologic device according to another aspect of the present invention, an operation unit is provided in an ophthalmic characteristic acquisition unit and receives an input operation from an examiner, the operation unit is provided at a position farther from the center of gravity of the ophthalmologic device than the ophthalmic characteristic acquisition unit, and a vibration detection unit is provided in the operation unit. This makes it possible to increase the magnitude of vibration detected by the vibration detection unit, thereby further improving the accuracy of the reliability evaluation of the acquisition result of the ophthalmic characteristics.

[0015] In an ophthalmic device according to another aspect of the present invention, an operation unit is provided in an ophthalmic characteristic acquisition unit and receives an input operation from an examiner, the operation unit is provided at a position farther from a center of gravity of the ophthalmic device than the ophthalmic characteristic acquisition unit, and when a distance from the center of gravity to the operation unit is defined as a first distance, a holding unit is provided in the ophthalmic characteristic acquisition unit and holds the vibration detection unit at a position a second distance away from the center of gravity that is longer than the first distance. This makes it possible to further improve the accuracy of reliability evaluation of the acquisition results of the ophthalmic characteristics.

[0016] In an ophthalmologic apparatus according to another aspect of the present invention, the eye characteristic acquisition unit is a non-contact tonometer that blows air from a nozzle onto the subject's eye, and the vibration detection unit is provided at an attachment position of the nozzle.

[0017] In the ophthalmologic apparatus according to another aspect of the present invention, the vibration detection unit is an acceleration sensor.

[0018] An operating method of an ophthalmic apparatus for achieving the object of the present invention, in which an ophthalmic apparatus is provided with an ophthalmic characteristic acquisition unit that acquires the ocular characteristics of a test eye, includes a vibration detection step of detecting vibrations of the ophthalmic apparatus at least while acquisition of the ophthalmic characteristics is being performed by the ophthalmic characteristic acquisition unit, and a reliability evaluation step of evaluating the reliability of the acquisition results of the ophthalmic characteristics acquired by the ophthalmic characteristic acquisition unit based on the detection result of the vibration detection step. Effect of the Invention

[0019] According to the present invention, the reliability of the acquired results of the ocular characteristics of the subject's eye can be easily determined. [Brief description of the drawings]

[0020] [Figure 1] FIG. 2 is a side view of the ophthalmologic apparatus according to the first embodiment. [Diagram 2] FIG. 2 is a block diagram showing the configuration of an optical system of a measuring head. [Diagram 3] FIG. 2 is a perspective view of the appearance of the objective lens with the cover of the measurement head removed. [Figure 4] FIG. 2 is a perspective view of the appearance of the imaging element with the cover of the measuring head removed. [Diagram 5] FIG. 2 is a functional block diagram of a control device according to the first embodiment. [Figure 6] 4 is an explanatory diagram for explaining display of eye characteristic measurement data by a display unit. FIG. [Figure 7] 5 is a flowchart showing a flow of a process for measuring ocular characteristics of a subject's eye by the ophthalmologic apparatus of the first embodiment. [Figure 8] FIG. 13 is a block diagram showing the configuration of an ophthalmologic apparatus according to a second embodiment. [Figure 9] 11 is a graph showing the change over time in the acceleration or vibration amplitude of the objective lens and the image sensor from the start of alignment to the end of all ocular characteristic measurements of the subject's eye a predetermined number of times. [Figure 10] 10 is a flowchart showing a flow of a process for measuring ocular characteristics of a subject's eye by an ophthalmologic apparatus according to a second embodiment. [Figure 11] FIG. 11 is a perspective view showing a state in which the cover of the display unit of the ophthalmologic apparatus of the third embodiment is removed. [Figure 12] FIG. 13 is an external perspective view of an ophthalmic apparatus according to a fourth embodiment with a measurement head cover removed. [Figure 13] 13 is an enlarged view of the sensor attachment portion as viewed from the direction of the arrow D in FIG. 12. [Figure 14] FIG. 13 is an external perspective view of an ophthalmic apparatus according to a fifth embodiment with a measurement head cover removed. [Figure 15] 11 is an explanatory diagram for explaining an example of how an acceleration sensor is attached when the ophthalmic apparatus is a non-contact tonometer. FIG. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0021] [First embodiment] 1 is a side view of an ophthalmic apparatus 1 according to a first embodiment. Among the mutually orthogonal XYZ directions (three directions) in the figure, the Y direction is the up-down direction, the Z direction is the front-back direction (also called the working distance direction) parallel to the front direction approaching the subject's eye E (subject) and the rear direction away from the subject, and the X direction is the left-right direction perpendicular to both the up-down direction and the front-back direction.

[0022] [Overall configuration of ophthalmic equipment] The ophthalmic apparatus 1 is an autorefractive keratometer capable of measuring eye characteristics such as ocular refractive power and corneal shape of a subject's eye E. The ophthalmic apparatus 1 includes a base 2, a face support unit 3, a drive mechanism 4, a measurement head 5 (also referred to as an apparatus main body), and a display unit 6.

[0023] A face support unit 3 and a drive mechanism 4 are provided on the base 2.

[0024] The face support part 3 has a chin rest part 3a for supporting the chin of the subject and a forehead rest part 3b against which the forehead of the subject comes into contact, and supports the face of the subject. The position of the chin rest part 3a can be adjusted in the Y direction (up and down direction) by an actuator (not shown).

[0025] The drive mechanism 4 is composed of an actuator (not shown), such as a motor. The drive mechanism 4 moves the measurement head 5 in the X, Y and Z directions relative to the base 2. This allows the measurement head 5 to be moved in the X, Y and Z directions relative to the subject's eye E, making it possible to align the measurement head 5 with the subject's eye E in the X, Y and Z directions.

[0026] The measurement head 5 has a function of measuring the eye characteristics (eye refractive power and corneal shape) of the subject eye E, and functions as an eye characteristic acquisition unit of the present invention together with a control device 9 (see FIG. 2) described below. A display unit 6 is attached to this measurement head 5. Also, various optical systems (including an image sensor, various light sources, and various driving units) corresponding to the measurement of eye refractive power and corneal shape, and the control device 9 are provided within the measurement head 5.

[0027] For example, a touch panel monitor is used as the display unit 6. The display unit 6 is rotatably held by the measurement head 5, and the position and orientation can be manually adjusted. The display unit 6 displays an observation image of the subject's eye E acquired by the measurement head 5, measurement results (acquired results) of eye characteristics such as the eye refractive power and corneal shape of the subject's eye E, a setting menu screen for performing various settings, and an operation menu screen for performing various operations.

[0028] The display surface of the display unit 6 receives input operations by touch operations by the examiner, and therefore functions as an operation unit of the present invention. Note that the ophthalmologic apparatus 1 may be provided with a known operation unit other than the display unit 6.

[0029] [Configuration of the optical system of the measurement head] Fig. 2 is a block diagram showing the configuration of the optical system of the measurement head 5. As shown in Fig. 2, the optical system of the measurement head 5 includes an observation optical system 12, a Z alignment optical system 13, an XY alignment optical system 14, a visual target projection optical system 15, a measurement pattern projection optical system 16, and a light receiving optical system 17.

[0030] (Configuration of the observation optical system) The observation optical system 12 is an optical system used for observing the anterior part of the subject's eye E and photographing the anterior part. The observation optical system 12 has a main optical axis O1 parallel to the Z direction. In the observation optical system 12, an objective lens 12a, a dichroic filter 12b, a half mirror 12c, a relay lens 12d, a dichroic filter 12e, an imaging lens 12f, and a CMOS (complementary metal oxide semiconductor) type or CCD (charge coupled device) type image sensor 12g are arranged along the main optical axis O1 in this order from the subject's eye E side. The observation optical system 12 also has an illumination light source (not shown). Note that each part constituting the observation optical system 12 is a known technique, and therefore detailed description thereof will be omitted.

[0031] Illumination light emitted from an illumination light source of the observation optical system 12 illuminates the anterior segment of the subject's eye E and is reflected by the anterior segment. This reflected light is incident on the objective lens 12a, passes through each part of the observation optical system 12 from the objective lens 12a, and is incident on the imaging surface of the imaging element 12g. As a result, the reflected light is imaged by the imaging element 12g, and an observation image (image data) of the anterior segment of the subject's eye E is obtained by the imaging element 12g. The imaging element 12g outputs the observation image to the control device 9.

[0032] Around the objective lens 12a, a keratoscopic plate 12h and a keratoscopic ring light source 12i are provided to measure the corneal shape of the cornea Ec of the subject's eye E. The keratoscopic plate 12h and the keratoscopic ring light source 12i project a single or multiple ring-shaped light beam onto the cornea Ec. The ring-shaped light beam reflected by the cornea Ec is incident on the imaging surface of the imaging element 12g via the objective lens 12a and the dichroic filter 12b, etc. As a result, a keratoscopic image is captured by the imaging element 12g. The imaging element 12g outputs the keratoscopic image (image data) to the control device 9.

[0033] (Z alignment optical system) The Z alignment optical system 13 is used to detect the alignment state of the measurement head 5 in the Z direction with respect to the subject's eye E. The Z alignment optical system 13 is provided at two locations behind the keratoconus plate 12h (on the imaging element 12g side). Each Z alignment optical system 13 has an alignment light source 13a and a projection lens 13b. Each alignment light source 13a emits a light beam toward the projection lens 13b. A pair of light beams emitted from each alignment light source 13a is converted into parallel light beams by each projection lens 13b, and then passes through a pair of transmission holes (not shown) in the keratoconus plate 12h to be projected onto the cornea Ec.

[0034] A pair of light beams reflected by the cornea Ec are incident on the imaging surface of the imaging element 12g via the objective lens 12a and the dichroic filter 12b. As a result, a pair of bright spot images are captured by the imaging element 12g, and the imaging element 12g outputs the pair of bright spot images (image data) to the control device 9. As a result, the pair of bright spot images can be displayed on the display unit 6 together with the observation image and the keratinizing image described above. Then, the control device 9 automatically or the examiner manually drives the driving mechanism 4 to move the measurement head 5 in the Z direction so that the keratinizing image and the pair of bright spot images have a predetermined positional relationship, thereby performing alignment in the Z direction (Z alignment). Note that Z alignment may be performed using other known methods.

[0035] (XY alignment optical system) The XY alignment optical system 14 is used to detect the alignment state of the measurement head 5 in the X and Y directions with respect to the subject's eye E. The XY alignment optical system 14 forms an optical path branched from the observation optical system 12 via a half mirror 12c. The XY alignment optical system 14 has an alignment light source 14a and a projection lens 14b. The alignment light source 14a emits a light beam toward the projection lens 14b. The light beam emitted from the alignment light source 14a is converted into a parallel light beam by the projection lens 14b, reflected by the half mirror 12c, and projected onto the cornea Ec via the dichroic filter 12b and the objective lens 12a.

[0036] The light beam reflected by the cornea Ec is incident on the imaging surface of the imaging element 12g via the objective lens 12a and the dichroic filter 12b. As a result, a bright spot image is captured by the imaging element 12g, and the imaging element 12g outputs the bright spot image (image data) to the control device 9. As a result, the display unit 6 can display a bright spot image for XY alignment together with the above-mentioned observation image, keratinizing image, and pair of bright spot images. Then, the control device 9 automatically or the examiner manually drives the driving mechanism 4 to adjust the position of the bright spot image in the X direction and the Y direction, thereby performing alignment in the X direction and the Y direction (XY alignment). Note that other known methods may be used for XY alignment.

[0037] The observation optical system 12 (image pickup element 12g) picks up an image of the alignment light beam during Z alignment and XY alignment, and therefore functions as an alignment detection system of the present invention together with the Z alignment optical system 13 and the XY alignment optical system 14.

[0038] (Configuration of visual target projection optical system) The target projection optical system 15 projects a light beam of a fixation target onto the fundus Ef of the subject's eye E in order to fixate or fogging the subject's eye E during objective measurement of the eye refractive power of the subject's eye E.

[0039] The target projection optical system 15 has a target display unit 15a, a half mirror 15b, a relay lens 15c, a reflecting mirror 15d, a focusing lens 15e (also called a movable lens), a relay lens 15f, a field lens 15g, a VCC lens 15h which is a variable cross cylinder lens, a reflecting mirror 15i, dichroic filters 15j and 12b, and an objective lens 12a.

[0040] In addition, the visual target projection optical system 15 has an optical axis O2 parallel to the aforementioned main optical axis O1, and the above-mentioned focusing lens 15e, relay lens 15f, field lens 15g, and VCC lens 15h are arranged on this optical axis O2.

[0041] The target display unit 15a may be, for example, a dot matrix liquid crystal display (LCD) or a matrix light emitting diode (LED). The target display unit 15a displays a fixation target and emits a light beam from the fixation target toward the half mirror 15b. Since the target display unit 15a is a dot matrix LCD or the like, the display mode (shape, etc.) and display position of the fixation target can be set arbitrarily. The target display unit 15a can also display targets for measuring visual acuity in addition to fixation targets.

[0042] The light beam of the fixation target displayed on the target display unit 15a is reflected by the half mirror 15b, and then passes through the relay lens 15c, the reflecting mirror 15d, the focusing lens 15e, the relay lens 15f, the field lens 15g, the VCC lens 15h, the reflecting mirror 15i, the dichroic filters 15j and 12b, and the objective lens 12a, before being projected onto the subject's eye E. This makes it possible to present a fixation target or the like to the subject's eye E.

[0043] The target projection optical system 15 also has a glare light source 15k used for a glare test of the subject's eye E. The glare light source 15k emits glare light to the half mirror 15b during the glare test. As a result, the glare light is projected onto the subject's eye E via each part from the half mirror 15b to the objective lens 12a.

[0044] The focusing lens 15e is disposed so as to be freely movable forward and backward along the optical axis O2 of the target projection optical system 15. The focusing lens 15e is moved forward and backward on the optical axis O2 by an interlocking movement mechanism 27 described later. This allows the refractive power of the light beam of the fixation target, etc. to be changed, and therefore the presentation distance of the fixation target, etc. relative to the subject's eye E can be changed. As a result, the subject's eye E can be fixed or clouded by the fixation target.

[0045] The VCC lens 15h has a pair of positive and negative cylinder lenses. The pair of cylinder lenses can rotate independently around the optical axis O2. The VCC lens 15h has a function of correcting (correcting) the cylindrical power (cylindrical power) and the axial angle (cylindrical axial angle) of the aberrations caused by the refractive characteristics of the subject's eye E.

[0046] (Configuration of the measurement pattern projection optical system) The measurement pattern projection optical system 16 projects a light beam of a ring-shaped measurement pattern (corresponding to the measurement light of the present invention) used for measuring the objective ocular refractive power of the subject's eye E onto the fundus Ef.

[0047] The measurement pattern projection optical system 16 includes a reflector measurement unit 16a, a relay lens 16b, a pupil ring 16c, a field lens 16d, a hole prism 16e, a rotary prism 16f, a dichroic filter 15j, a dichroic filter 12b, and an objective lens 12a.

[0048] The measurement pattern projection optical system 16 also has an optical axis O3 parallel to the above-mentioned main optical axis O1 and optical axis O2. A reflector measurement unit 16a, a relay lens 16b, a pupil ring 16c, a field lens 16d, and a holed prism 16e are arranged on this optical axis O3.

[0049] The reflex measurement unit 16a corresponds to the measurement light source of the present invention, and includes an LED light source 16h using an LED (light emitting diode), a collimator lens 16i, a conical prism 16j, and a measurement pattern formation plate 16k. The LED light source 16h and the pupil ring 16c are disposed in an optically conjugate position. The formation plate 16k and the fundus Ef are disposed in an optically conjugate position.

[0050] The reflector measurement unit 16a is disposed so as to be movable forward and backward along an optical axis O3 of the measurement pattern projection optical system 16. The reflector measurement unit 16a is moved forward and backward on the optical axis O3 by an interlocking movement mechanism 27, which will be described later.

[0051] The light beam emitted from the LED light source 16h is collimated by the collimator lens 16i, and then emitted toward the relay lens 16b via the conical prism 16j and the forming plate 16k. This light beam passes through the relay lens 16b, the pupil ring 16c, the field lens 16d, the reflecting surface of the apertured prism 16e, the rotary prism 16f, the dichroic filter 15j, the dichroic filter 12b, and the objective lens 12a, and is projected onto the fundus Ef. As a result, a ring-shaped measurement pattern is projected onto the fundus Ef. The measurement pattern is projected onto the fundus Ef with its shape distorted by the ocular refractive power of the subject's eye E.

[0052] (Configuration of the light receiving optical system) The light receiving optical system 17 receives fundus reflected light (corresponding to the return light of the present invention) of the measurement pattern projected onto the fundus Ef by the measurement pattern projection optical system 16. The light receiving optical system 17 has an objective lens 12a, dichroic filters 12b and 15J, a rotary prism 16f, a holed prism 16e, a field lens 17a, a reflecting mirror 17b, a relay lens 17c, a focusing lens 17d (also referred to as a moving lens), a reflecting mirror 17e, a dichroic filter 12e, an imaging lens 12f, and an image sensor 12g.

[0053] The light receiving optical system 17 also has an optical axis O4 parallel to the above-mentioned main optical axis O1, optical axis O2, and optical axis O3. A reflecting mirror 17b, a relay lens 17c, a focusing lens 17d, and a reflecting mirror 17e are arranged on the optical axis O4.

[0054] The focusing lens 17d is disposed so as to be movable forward and backward along an optical axis O4 of the light receiving optical system 17. The focusing lens 17d is moved forward and backward on the optical axis O4 by an interlocking movement mechanism 27, which will be described later.

[0055] The fundus reflected light of the measurement light reflected by the fundus Ef passes through the objective lens 12a, the dichroic filters 12b and 15J, the rotary prism 16f, the hole of the perforated prism 16e, the field lens 17a, the reflecting mirror 17b, the relay lens 17c, the focusing lens 17d (also called a moving lens), the reflecting mirror 17e, the dichroic filter 12e, and the imaging lens 12f, and is incident on the light receiving surface of the image sensor 12g. The image sensor 12g captures the fundus reflected light and outputs a ring image (image data) to the control device 9.

[0056] Although not shown, the interlocking movement mechanism 27 includes a holding member that integrally holds (connects) the focusing lens 15e, the reflex measurement unit 16a, and the focusing lens 17d, a slide mechanism that holds the holding member so as to be slidable in a direction parallel to the main optical axis O1 (each of the optical axes O2 to O4) (Z direction), and a drive mechanism such as a motor that moves the holding member back and forth in the Z direction. As a result, the focusing lens 15e, the reflex measurement unit 16a, and the focusing lens 17d are moved in an interlocking manner (integrally) along the Z direction by the interlocking movement mechanism 27.

[0057] [Accelerometer] Fig. 3 is a perspective view of the objective lens 12a with the cover of the measurement head 5 removed. Fig. 4 is a perspective view of the image pickup element 12g with the cover of the measurement head 5 removed.

[0058] As shown in Figures 3 and 4 and the already described Figure 2, an acceleration sensor 28 (corresponding to the vibration detection unit of the present invention) is provided at a location in the ophthalmic device 1 where the occurrence of vibration (shaking) would reduce the reliability of the ocular characteristic measurement data, which is the acquisition result (measurement result) of the ocular characteristics of the subject eye E.

[0059] Specifically, the acceleration sensor 28 is provided at the mounting position of the objective lens 12a (see FIG. 3) and at the mounting position of the image sensor 12g (see FIG. 4) in the measurement head 5. As described above, the image sensor 12g functions as a part of the alignment detection system of the present invention, so providing the acceleration sensor 28 at the mounting position of the image sensor 12g also corresponds to providing the acceleration sensor 28 at the mounting position of the alignment detection system.

[0060] The objective lens 12a is held by a lens holding portion 30 in the measurement head 5. A sensor mounting portion 32 is fixed to this lens holding portion 30, and an acceleration sensor 28 is further attached to this sensor mounting portion 32. In this way, the acceleration sensor 28 is provided at the mounting position of the objective lens 12a. Note that the mounting position and mounting method of the acceleration sensor 28 are not particularly limited as long as it is possible to detect vibrations of the objective lens 12a.

[0061] Furthermore, the imaging element 12g is held by an imaging element holding portion 34 in the measurement head 5. A sensor attachment portion 36 is fixed to this imaging element holding portion 34, and the acceleration sensor 28 is further attached to this sensor attachment portion 36. In this way, the acceleration sensor 28 is provided at the attachment position of the imaging element 12g. Note that the attachment position and attachment method of the acceleration sensor 28 are not particularly limited as long as it is possible to detect vibrations of the imaging element 12g.

[0062] Each acceleration sensor 28 is a known three-axis type sensor (or a type other than the three-axis type). Each acceleration sensor 28 detects the acceleration (vibration) of the objective lens 12a and the acceleration (vibration) of the imaging element 12g, and outputs an acceleration detection signal to the control device 9.

[0063] In this embodiment, the acceleration sensor 28 is provided at the mounting position of the objective lens 12a and at the mounting position of the image sensor 12g, but the acceleration sensor 28 may be provided at only one of these mounting positions. Furthermore, instead of or in addition to the mounting positions of at least one of the objective lens 12a and the image sensor 12g, the acceleration sensor 28 may be provided at the mounting position of the reflector measurement unit 16a (see FIG. 2), which corresponds to the measurement light source of the present invention.

[0064] [Functions of the control device of the first embodiment] Fig. 5 is a functional block diagram of the control device 9 of the first embodiment. As shown in Fig. 5, the control device 9 controls the operation of each part of the ophthalmologic apparatus 1, and executes alignment of the measurement head 5 with respect to the subject's eye E, measurement of eye characteristics of the subject's eye E, reliability evaluation of eye characteristic measurement data described later, warnings described later, etc. The face support unit 3, the drive mechanism 4, each optical system and acceleration sensor 28 of the measurement head 5, and the display unit 6 are connected to this control device 9.

[0065] The control device 9 includes an arithmetic circuit including various processors and memories. The various processors include a central processing unit (CPU), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), and a programmable logic device (e.g., simple programmable logic devices (SPLD), complex programmable logic devices (CPLD), and field programmable gate arrays (FPGA)). The various functions of the control device 9 may be realized by one processor, or may be realized by multiple processors of the same or different types.

[0066] The control device 9 functions as an alignment control unit 40, an eye characteristic measurement control unit 42, an eye characteristic calculation unit 44, a signal acquisition unit 46, a reliability evaluation unit 48, a display control unit 50, and an alarm control unit 52 by executing a control program stored in a memory unit not shown.

[0067] Before starting eye measurement of the subject's eye E, the alignment control unit 40 controls the observation optical system 12, the keratinizing light source 12i, the Z alignment optical system 13, the XY alignment optical system 14, the visual target projection optical system 15, etc., and performs alignment detection by a known method to detect the relative position of the measurement head 5 in the XYZ directions with respect to the subject's eye E. Next, the alignment control unit 40 performs alignment of the measurement head 5 in the XYZ directions with respect to the subject's eye E by driving the drive mechanism 4 to move the measurement head 5 in the XYZ directions based on the detection result of the alignment detection.

[0068] After the above-mentioned alignment is completed, the eye characteristic measurement control unit 42 controls the observation optical system 12, the keratometry light source 12i, the measurement pattern projection optical system 16, the visual target projection optical system 15, etc. to perform keratometry for measuring the corneal shape of the subject's eye E and refraction measurement for measuring the ocular refractive power of the subject's eye E, as eye characteristic measurements of the subject's eye E. In addition, the eye characteristic calculation unit 44 calculates the corneal shape of the subject's eye E when the keratometry is performed, and calculates the ocular refractive power of the subject's eye E when the refraction measurement is performed.

[0069] For example, in the keratometry of the subject's eye E, the eye characteristic measurement control unit 42 turns on the keratometry ring light source 12i to project a single or multiple ring-shaped light beams onto the cornea Ec, and causes the imaging element 12g to capture an image of the ring-shaped light beams reflected by the cornea Ec. Next, the eye characteristic calculation unit 44 calculates the corneal shape (corneal refractive power, corneal astigmatism, corneal astigmatism axis angle, etc.) of the subject's eye E by a known method based on the keratometry ring image output from the imaging element 12g.

[0070] In the reflex measurement of the eye E, a provisional measurement and a main measurement are performed. In the provisional measurement, the eye characteristic measurement control unit 42 controls the target projection optical system 15 (target display unit 15a) to present a fixation target to the eye E. Next, the eye characteristic measurement control unit 42 controls the measurement pattern projection optical system 16 (LED light source 16h, rotary prism 16f, etc.) to project a ring-shaped measurement pattern light beam onto the fundus Ef, and causes the light receiving optical system 17 (image sensor 12g) to capture an image of the fundus reflected light (ring image) reflected by the fundus Ef.

[0071] Then, the eye characteristic calculation unit 44 calculates the provisional spherical power and cylindrical power of the subject's eye E by a known method based on the captured image of the ring image output from the imaging element. Based on the calculation results of the spherical power and cylindrical power in this provisional measurement, the eye characteristic measurement control unit 42 drives the interlocking movement mechanism 27 to move the focusing lens 15e, the reflex measurement unit 16a, and the focusing lens 17d to the position of the transmitted spherical power. This provisional measurement process may be repeated multiple times.

[0072] In the main measurement, the eye characteristic measurement control unit 42 drives the interlocking movement mechanism 27 to move the focusing lens 15e from the position determined in the provisional measurement to a fogging position, thereby promoting fogging of the subject's eye E. Then, the eye characteristic measurement control unit 42 controls the measurement pattern projection optical system 16 and the light receiving optical system 17 in the same manner as in the provisional measurement to project the light beam of the ring-shaped measurement pattern onto the fundus Ef and capture the ring image by the imaging element 12g. Next, the eye characteristic calculation unit 44 calculates the eye refractive power (spherical power, cylindrical power, and cylindrical axis angle) of the subject's eye E using a known method based on the ring image and the amount of movement of the focusing lens 15e.

[0073] During the period from when alignment is started until the measurement of ocular characteristics of the subject's eye E (keratomileusis measurement, reflex measurement) is being performed, the signal acquiring unit 46 continuously acquires the acceleration detection signals from each acceleration sensor 28 and outputs the detection signals to the reliability evaluating unit 48. Note that the period during which the signal acquiring unit 46 acquires the detection signals may be at least during the measurement of ocular characteristics of the subject's eye E, and acquisition of the detection signals may start after the completion of alignment, for example.

[0074] The reliability evaluation unit 48 evaluates the reliability of the ocular characteristic measurement data (corneal shape, ocular refractive power) of the subject's eye E calculated by the ocular characteristic calculation unit 44 based on the acceleration detection signal continuously input from the signal acquisition unit 46.

[0075] For example, if the acceleration (absolute value) of the objective lens 12a and the image sensor 12g or the amplitude (absolute value) of the vibration indicated by the acceleration detection signal is equal to or less than a predetermined threshold value from the start of alignment to the completion of ocular characteristic measurement of the subject's eye E, the reliability evaluation unit 48 evaluates that the reliability of the ocular characteristic measurement data of the subject's eye E is high. Conversely, if the acceleration or the amplitude of the vibration of the objective lens 12a and the image sensor 12g exceeds a predetermined threshold value from the start of alignment to the completion of ocular characteristic measurement of the subject's eye E, the reliability evaluation unit 48 evaluates that the reliability of the ocular characteristic measurement data of the subject's eye E is low.

[0076] The display control unit 50 controls the display of the display unit 6. The display control unit 50 causes the display unit 6 to display an observation image of the subject's eye E acquired by the observation optical system 12, ocular characteristic data of the subject's eye E calculated by the ocular characteristic calculation unit 44, various menu screens, and the like.

[0077] Fig. 6 is an explanatory diagram for explaining the display of eye characteristic measurement data by the display unit 6. Note that reference symbol VIA in Fig. 6 indicates an example of the display of eye characteristic measurement data evaluated by the reliability evaluation unit 48 as having high reliability, and reference symbol VIB indicates an example of the display of eye characteristic measurement data evaluated by the reliability evaluation unit 48 as having low reliability.

[0078] As shown in Fig. 6 and Fig. 5, when the ocular characteristic calculation unit 44 completes the calculation of the ocular characteristic measurement data (corneal shape, ocular refractive power) of the subject's eye E, the display control unit 50 causes the display unit 6 to display a measurement result field 56 showing the ocular characteristic measurement data. At this time, if the reliability evaluation unit 48 evaluates that the reliability of the ocular characteristic measurement data (corneal shape, ocular refractive power) of the subject's eye E is high, the notification control unit 52 described below does not operate. Therefore, the measurement result field 56 is displayed in the normal display mode on the display unit 6 (see symbol VIA in Fig. 6).

[0079] The notification control unit 52 functions as a notification unit of the present invention together with the display unit 6 and the display control unit 50. When the reliability evaluation unit 48 evaluates that the reliability of the ocular characteristic measurement data (corneal shape, ocular refractive power) of the subject's eye E is low, the notification control unit 52 controls the display control unit 50 to display warning information 58 indicating that the reliability of the ocular characteristic measurement data is low (large vibration during measurement) together with a measurement result field 56 on the display unit 6 (see symbol VIB in FIG. 6).

[0080] Furthermore, when the measurement value of the amplitude of the acceleration or vibration is set to "A1" and its threshold value is set to "A2", the notification control unit 52 calculates a reliability coefficient 59 based on the degree to which the measurement value exceeds the threshold value (for example, |A1|-|A2|). Then, the notification control unit 52 controls the display control unit 50 to cause the display unit 6 to display the reliability coefficient 59 as well. Note that only either the warning information 58 or the reliability coefficient 59 may be displayed on the display unit 6.

[0081] Furthermore, instead of displaying at least one of the warning information 58 and the reliability coefficient 59 on the display unit 6, at least one of them may be output as audio from a speaker (not shown), and the method of notifying the examiner is not particularly limited.

[0082] [Operation of the first embodiment] FIG. 7 is a flowchart showing a flow of a process for measuring ocular characteristics of the subject's eye E by the ophthalmic apparatus 1 of the first embodiment, according to the operation method of the ophthalmic apparatus of the present invention.

[0083] 7, after the subject's face is supported by the face support part 3, when the examiner inputs a measurement start operation to the operation menu screen of the display part 6, the alignment control part 40 controls each part of the measurement head 5 and executes alignment detection in the XYZ directions of the measurement head 5 with respect to the subject's eye E by a known method. This starts alignment of the measurement head 5 with respect to the subject's eye E (step S1).

[0084] Furthermore, when alignment is started, the signal acquisition unit 46 starts acquiring detection signals indicating the acceleration (vibration) of the objective lens 12a and the image sensor 12g from each acceleration sensor 28, and continuously outputs the acquired detection signals to the reliability evaluation unit 48 (step S2, which corresponds to the vibration detection process of the present invention).

[0085] Based on the detection result of the alignment detection, the alignment control unit 40 starts alignment of the measurement head 5 in the XYZ directions with respect to the test eye E by driving the drive mechanism 4 to move the measurement head 5 in the XYZ directions (step S3, NO in step S4).

[0086] When the alignment is completed (YES in step S4), the eye characteristic measurement control unit 42 controls the observation optical system 12, the keratinizing light source 12i, the measurement pattern projection optical system 16, the visual target projection optical system 15, etc. to perform keratinometry and refraction measurement of the subject's eye E. In addition, the eye characteristic calculation unit 44 calculates the corneal shape of the subject's eye E during keratometry, and calculates the ocular refractive power of the subject's eye E during refraction measurement. This allows the eye characteristic measurement data (corneal shape, ocular refractive power) of the subject's eye E to be obtained (step S5).

[0087] On the other hand, the reliability evaluation unit 48 judges whether the acceleration or the amplitude of vibration of the objective lens 12a and the image sensor 12g is equal to or less than a predetermined threshold value from the start of alignment to the completion of the measurement of the eye characteristics, based on the acceleration detection signal continuously input from the signal acquisition unit 46. Then, when the reliability evaluation unit 48 judges that the acceleration or the amplitude is equal to or less than the threshold value (NO in step S6), it evaluates that the reliability of the eye characteristic measurement data is high.

[0088] Conversely, when the reliability evaluation unit 48 determines that the acceleration or amplitude exceeds the threshold value (YES in step S6), it evaluates that the reliability of the eye characteristic measurement data is low. Note that step S6 corresponds to the reliability evaluation step of the present invention.

[0089] If the reliability evaluation unit 48 evaluates that the reliability of the ocular characteristic measurement data of the subject eye E is high, the display control unit 50 causes the display unit 6 to display a measurement result column 56 showing the ocular characteristic measurement data, as shown by symbol VIA in Figure 6 described above (step S7).

[0090] On the other hand, when the reliability evaluation unit 48 evaluates that the reliability of the eye characteristic measurement data (corneal shape, eye refractive power) of the subject eye E is low, as shown by reference symbol VIB in Fig. 6, the notification control unit 52 controls the display control unit 50 to display the warning information 58 and the reliability coefficient 59 together with the measurement result field 56 on the display unit 6 (step S8). This makes it possible to notify the examiner that the reliability of the eye characteristic measurement data is low, and to urge the examiner to perform remeasurement.

[0091] As described above, in the ophthalmic device 1 of the first embodiment, the acceleration sensor 28 is provided at a location in the ophthalmic device 1 where the reliability of the ophthalmic characteristic measurement data decreases especially when vibration occurs, so that the reliability of the ophthalmic characteristic measurement data can be easily determined based on the detection signal of the acceleration sensor 28. In this way, when the reliability of the ophthalmic characteristic measurement data is low, the examiner can be notified of this fact.

[0092] [Second embodiment] 8 is a block diagram showing the configuration of an ophthalmic apparatus 1 according to a second embodiment. The ophthalmic apparatus 1 according to the first embodiment displays warning information 58 and a reliability coefficient 59 when the reliability evaluation unit 48 evaluates the reliability of the ocular characteristic measurement data of the subject's eye E to be low. In contrast, the ophthalmic apparatus 1 according to the second embodiment displays only the ocular characteristic measurement data evaluated by the reliability evaluation unit 48 to be highly reliable on the display unit 6, and deletes the ocular characteristic measurement data evaluated by the reliability evaluation unit 48 to be low reliable. Furthermore, the ophthalmic apparatus 1 according to the second embodiment repeatedly measures the ocular characteristic measurement data of the subject's eye E multiple times.

[0093] 8, the ophthalmic apparatus 1 of the second embodiment has basically the same configuration as the ophthalmic apparatus 1 of the first embodiment, except that the functions of the eye characteristic measurement control unit 42, the signal acquisition unit 46, and the display control unit 50 of the control device 9 are partially different from those of the first embodiment, and the control device 9 further functions as a selection unit 49. For this reason, the same reference numerals are used for components that are the same in function or configuration as those of the first embodiment, and their description will be omitted.

[0094] The eye characteristic measurement control unit 42 of the second embodiment controls each part of the measurement head 5 to repeatedly measure the eye characteristics of the subject eye E a preset number of times (2 or more). Note that a pause section PA is provided between the nth (n is any natural number) eye characteristic measurement and the n+1th eye characteristic measurement (see FIG. 9).

[0095] The signal acquisition unit 46 of the second embodiment continuously acquires acceleration detection signals from each acceleration sensor 28 and outputs the detection signals to the reliability evaluation unit 48 from the start of alignment until all measurements of the eye characteristics of the test eye E for the above-mentioned number of measurements are completed.

[0096] FIG. 9 is a graph showing the change over time in the acceleration or vibration amplitude of the objective lens 12a and the imaging element 12g from the start of alignment to the completion of all eye characteristic measurements of the test eye E for a predetermined number of measurements.

[0097] In Fig. 9, the description will be made assuming that the number of measurements of the eye characteristics of the subject's eye E is set to three. Furthermore, the symbol "T1" in Fig. 9 indicates the period before the measurement of the eye characteristics of the subject's eye E starts (alignment), and the symbol "T2" indicates the period during the measurement of the eye characteristics of the subject's eye E. Furthermore, the symbol "M1" in Fig. 9 indicates the period during which the eye characteristics are measured for the first time, the symbol "M2" indicates the period during which the eye characteristics are measured for the second time, and the symbol "M3" indicates the period during which the eye characteristics are measured for the third time. Furthermore, the symbol "PA" in Fig. 9 indicates a pause period set between successive eye characteristic measurements.

[0098] As shown in Fig. 9 and the above-mentioned Fig. 8, the reliability evaluation unit 48 of the second embodiment evaluates the reliability of the ocular characteristic measurement data for each measurement section M1 to M3 of the ocular characteristics of the subject's eye E based on the detection signal of the acceleration input from the signal acquisition unit 46 from the start of alignment to the end of all measurements of the ocular characteristics of the subject's eye E. Specifically, the reliability evaluation unit 48 judges whether the acceleration of the objective lens 12a and the image sensor 12g or the amplitude of vibration falls within a range (threshold range) from a predetermined threshold value (-A) to a threshold value (+A) for each measurement section M1 to M3. Then, the reliability evaluation unit 48 evaluates whether the reliability of the ocular characteristic measurement data is high or low based on whether the acceleration or amplitude falls within the threshold range for each measurement section M1 to M3.

[0099] 9, since the acceleration or amplitude does not fall within the threshold range in measurement sections M1 and M2 as shown by symbol C1, the reliability evaluation unit 48 evaluates the reliability of the first and second eye characteristic measurement data as low. On the other hand, since the acceleration or amplitude falls within the threshold range in measurement section M3, the reliability evaluation unit 48 evaluates the reliability of the third eye characteristic measurement data as high.

[0100] In the second embodiment, even if the acceleration or amplitude does not fall within the threshold range in the section before the start of measurement of the eye characteristics of the test eye E, as shown by symbol C2, or the acceleration or amplitude does not fall within the threshold range in the pause section PA, as shown by symbol C3, it is not evaluated by the reliability evaluation unit 48.

[0101] The selection unit 49 retains only the ocular characteristic measurement data evaluated by the reliability evaluation unit 48 as having high reliability from the ocular characteristic measurement data of the subject eye E for a predetermined number of measurements calculated by the ocular characteristic calculation unit 44, and conversely, deletes the ocular characteristic measurement data evaluated by the reliability evaluation unit 48 as having low reliability.

[0102] The display control unit 50 of the second embodiment causes the display unit 6 to display only the ocular characteristic measurement data of the subject eye E left by the selection unit 49, i.e., only the ocular characteristic measurement data evaluated as having high reliability by the reliability evaluation unit 48.

[0103] 10 is a flowchart showing a flow of a process of measuring ocular characteristics of a subject's eye E by the ophthalmic apparatus 1 of the second embodiment, which is related to the operation method of the ophthalmic apparatus of the present invention. Note that the processes from step S1 to step S4 are the same as those of the first embodiment shown in FIG. 7, and therefore a detailed description thereof will be omitted here.

[0104] When the alignment is completed (YES in step S4), the eye characteristic measurement control unit 42 controls each part of the measurement head 5 to repeatedly perform the eye characteristic measurement of the subject's eye E a predetermined number of times (NO in steps S5A and S5B). The signal acquisition unit 46 continuously acquires the acceleration detection signals from the acceleration sensors 28 and outputs the detection signals to the reliability evaluation unit 48 until all the eye characteristic measurements of the subject's eye E for the predetermined number of times are completed.

[0105] When all ocular characteristic measurements of the test eye E are completed (YES in step S5B), the reliability evaluation unit 48 evaluates the reliability of the ocular characteristic measurement data individually for each measurement section M1, M2, ... of the ocular characteristics of the test eye E based on the acceleration detection signal input from the signal acquisition unit 46, as shown in Figure 9 above (step S10).

[0106] Next, the selection unit 49 keeps only the eye characteristic measurement data evaluated as having high reliability by the reliability evaluation unit 48 among the eye characteristic measurement data of the subject's eye E for a predetermined number of measurements calculated by the eye characteristic calculation unit 44, and deletes the eye characteristic measurement data evaluated as having low reliability (step S11). Note that the processes of the above-mentioned steps S10 and S11 may be repeatedly executed every time the eye characteristic measurement of the above-mentioned step S5A is executed, not after all the eye characteristic measurements of the subject's eye E are completed (YES in step S5B).

[0107] Then, the display control unit 50 causes the display unit 6 to display only the ocular characteristic measurement data of the subject's eye E left by the selection unit 49, i.e., only the ocular characteristic measurement data evaluated as having high reliability by the reliability evaluation unit 48 (step S12). This makes it possible to present only the ocular characteristic measurement data having high reliability to the examiner.

[0108] As described above, in the ophthalmic apparatus 1 of the second embodiment as well, the reliability of the ocular characteristic measurement data can be easily determined based on the detection signal of the acceleration sensor 28. Moreover, the selection unit 49 deletes ocular characteristic measurement data evaluated as having low reliability by the reliability evaluation unit 48, so that only ocular characteristic measurement data with high reliability can be presented to the examiner. Moreover, when vibrations are occurring in the ophthalmic apparatus 1, it is not necessary to wait until the vibrations subside, and measurement of the ocular characteristics can be started immediately.

[0109] In the second embodiment, the ocular characteristic measurement of the subject's eye E is repeatedly performed a plurality of times by the ophthalmologic apparatus 1, but the present invention is also applicable to the case where the ocular characteristic measurement is performed only once. In this case, when the reliability evaluation unit 48 evaluates that the reliability of the ocular characteristic measurement data is low, all the ocular characteristic measurement data is deleted by the selection unit 49, so that the warning information 58 and the reliability coefficient 59 of the first embodiment are displayed on the display unit 6.

[0110] [Third embodiment] 11 is a perspective view showing a state where the cover of the display unit 6 of the ophthalmic apparatus 1 of the third embodiment is removed. In each of the above embodiments, the acceleration sensor 28 is provided in the measurement head 5, but even if vibrations that do not affect the reliability of the ophthalmic characteristic measurement data, for example, vibrations caused by the environment of the ophthalmic apparatus 1, occur, there is no need to display warning information 58 or delete the ophthalmic characteristic measurement data. Examples of vibrations caused by the environment of the ophthalmic apparatus 1 include work vibrations (walking, etc.) caused by people working nearby and running vibrations of cars traveling on nearby roads. Therefore, when the magnitude of vibration of the ophthalmic device 1 due to the environment is close to the magnitude of vibration of the ophthalmic device 1 that affects the reliability of the eye characteristic measurement data, it is preferable to make it easier to evaluate the reliability of the eye characteristic measurement data by deliberately increasing the latter vibration.

[0111] 11, the ophthalmologic apparatus 1 of the third embodiment is provided with an acceleration sensor 28 on the display unit 6. Specifically, the acceleration sensor 28 is provided at a position on the back surface of the metal plate 6b covering the back side of the display panel 6a (liquid crystal panel or the like) of the display unit 6, where the operating force of the touch operation by the examiner is particularly applied. Note that the position where the acceleration sensor 28 is provided on the display unit 6 is not particularly limited.

[0112] The ophthalmic device 1 of the third embodiment has basically the same configuration as the ophthalmic device 1 of each of the above-mentioned embodiments, except that an acceleration sensor 28 is provided on the display unit 6. Therefore, the same reference numerals are used for the components having the same functions or configurations as those of the above-mentioned embodiments, and the description thereof will be omitted.

[0113] The center of gravity G of the ophthalmic device 1 (see FIG. 12 described later) is located in the measurement head 5 or the drive mechanism 4. Therefore, the display unit 6 is provided at a position farther from the center of gravity G of the ophthalmic device 1 than the measurement head 5 (see FIG. 1). Furthermore, in the third embodiment, the display unit 6 is provided at a position farthest from the center of gravity G in the ophthalmic device 1. When vibrations that affect the reliability of eye characteristic measurement data occur in the ophthalmic device 1, the vibrations become larger the farther away from the center of gravity G. Therefore, the vibrations of the display unit 6, which is located at a position farthest from the center of gravity G in the ophthalmic device 1, become the largest.

[0114] Therefore, by providing the acceleration sensor 28 on the display unit 6, the vibration detected by the acceleration sensor 28 (vibration affecting the reliability of the eye characteristic measurement data) can be increased, and the weak acceleration detection signal output from the acceleration sensor 28 can be amplified. As a result, it is possible to intentionally increase the vibration of the ophthalmic device 1 caused by the environment and the vibration of the ophthalmic device 1 affecting the reliability of the eye characteristic measurement data. Therefore, the magnitude of the vibration of the ophthalmic device 1 caused by the environment and the magnitude of the vibration of the ophthalmic device 1 affecting the reliability of the eye characteristic measurement data are separated, and the vibration affecting the reliability of the eye characteristic measurement data can be easily detected by the acceleration sensor 28. As a result, it becomes easier to evaluate the reliability of the eye characteristic measurement data, and the accuracy of the reliability evaluation of the eye characteristic measurement data of the subject's eye E by the reliability evaluation unit 48 can be further improved.

[0115] [Fourth embodiment] Fig. 12 is an external perspective view of the ophthalmic apparatus 1 of the fourth embodiment with the cover of the measurement head 5 removed. Fig. 13 is an enlarged view of the sensor attachment part 60 as viewed from the direction of the arrow D in Fig. 12. In the third embodiment, the acceleration sensor 28 is provided on the display unit 6, but in the ophthalmic apparatus 1 of the fourth embodiment, the acceleration sensor 28 is provided at a position farther away than the display unit 6.

[0116] The ophthalmic apparatus 1 of the fourth embodiment has basically the same configuration as the ophthalmic apparatus 1 of each of the above-mentioned embodiments, except that the measuring head 5 is provided with a sensor attachment unit 60. Therefore, the same reference numerals are used for the components having the same functions or configurations as those of the above-mentioned embodiments, and the description thereof will be omitted.

[0117] The sensor attachment section 60 corresponds to the holding section of the present invention, and holds the acceleration sensor 28 at a position a second distance LB away from the center of gravity position G, which is longer than the first distance LA, assuming that the distance from the center of gravity position G to the display section 6 is a first distance LA. This allows the acceleration sensor 28 to detect a larger vibration (vibration that affects the reliability of the eye characteristic measurement data) than in the third embodiment. This makes it easier for the acceleration sensor 28 to detect vibration that affects the reliability of the eye characteristic measurement data, making it easier to evaluate the reliability of the eye characteristic measurement data. As a result, the accuracy of the reliability evaluation of the eye characteristic measurement data of the subject's eye E by the reliability evaluation section 48 can be further improved.

[0118] [Fifth embodiment] 14 is an external perspective view of the ophthalmic apparatus 1 of the fifth embodiment with the cover of the measurement head 5 removed. In the above third and fourth embodiments, the acceleration sensor 28 is provided at a position farther away from the center of gravity G in order to increase the vibration detected by the acceleration sensor 28 (vibration that affects the reliability of eye characteristic measurement data), but the ophthalmic apparatus 1 of the fifth embodiment increases the vibration detected by the acceleration sensor 28 by a different method.

[0119] 14, the ophthalmic apparatus 1 of the fifth embodiment has basically the same configuration as the ophthalmic apparatus 1 of each of the above embodiments, except for a different method for attaching the acceleration sensor 28. Therefore, the same reference numerals are used to designate the same components in terms of function or configuration as those of the above embodiments, and the description thereof will be omitted.

[0120] In the ophthalmologic apparatus 1 of the fifth embodiment, the acceleration sensor 28 is attached to the sensor attachment portion 32 via a rubber spacer 62 (corresponding to a mounting member of the present invention). Although not shown, the acceleration sensor 28 may be attached to the sensor attachment portion 36 (see FIG. 4), the metal plate 6b (see FIG. 11), and the sensor attachment portion 60 (see FIG. 13) via the rubber spacer 62.

[0121] By mounting the acceleration sensor 28 at various mounting positions via a mounting member having flexibility (including elasticity) such as the rubber spacer 62, it is possible to amplify the vibration of the acceleration sensor 28 itself when vibrations that affect the reliability of the eye characteristic measurement data occur in the ophthalmic device 1. In this case as well, it is possible to intentionally increase the vibrations of the ophthalmic device 1 that affect the reliability of the eye characteristic measurement data, so that the acceleration sensor 28 can easily detect the vibrations that affect the reliability of the eye characteristic measurement data. As a result, it becomes easier to evaluate the reliability of the eye characteristic measurement data, so that the accuracy of the reliability evaluation of the eye characteristic measurement data by the reliability evaluation unit 48 can be further improved, as in the third and fourth embodiments.

[0122] In the above-mentioned fifth embodiment, the acceleration sensor 28 is attached to various attachment positions via the rubber spacer 62, but the acceleration sensor 28 may be attached via various attachment members (spacers) having flexibility (elasticity), such as a spring-like spacer (leaf spring). Also, the sensor attachment parts 32, 36, 60 themselves may be made flexible by forming the sensor attachment parts 32, 36, 60 in a thin plate shape.

[0123] [others] In the above embodiments, an autorefractometer has been described as an example of the ophthalmic device 1, but the present invention can also be applied to other ophthalmic devices that acquire various ocular characteristics of the subject's eye E [intraocular pressure value, corneal endothelial cells, OCT (Optical Coherence Tomography) image, fundus image, etc.]. In this case, the acceleration sensor 28 is attached to the mounting positions of the objective lens, measurement light source, image sensor, alignment detection system, etc. in the other ophthalmic device. In addition, the location where the acceleration sensor 28 is attached is not limited to the mounting positions of the objective lens, etc., and includes other locations that reduce the reliability of the ocular characteristic measurement data when vibration occurs. These other locations differ depending on the type of ophthalmic device.

[0124] FIG. 15 is an explanatory diagram for explaining an example of mounting the acceleration sensor 28 when the ophthalmic apparatus is a non-contact tonometer 70. In FIG.

[0125] 15, the non-contact tonometer 70 measures the intraocular pressure value of the subject's eye E. The non-contact tonometer 70 measures the intraocular pressure value of the subject's eye E in a non-contact manner by blowing air (or various fluids) from a nozzle 74 toward the cornea Ec to deform the cornea Ec and detecting the state of deformation.

[0126] The measurement head 72 of the non-contact tonometer 70 includes a nozzle 74, a window glass 76 in which the nozzle 74 is provided, and a convex glass holding portion 78 that holds the window glass 76. Although not shown, the measurement head 72 of the non-contact tonometer 70 is also provided with various known optical systems (including the objective lens, measurement light source, image sensor, and alignment detection system of the present invention). Thus, by driving each portion of the measurement head 72, intraocular pressure measurement of the subject's eye E can be performed by a known method.

[0127] In such a non-contact tonometer 70, if vibration occurs in the nozzle 74 and its surroundings, the reliability of the intraocular pressure value (ocular characteristic measurement data) of the subject's eye E decreases. For this reason, an acceleration sensor 28 may be provided at the attachment position (e.g., glass holding portion 78) of the nozzle 74 of the measurement head 72, and the reliability of the intraocular pressure value of the subject's eye E may be evaluated based on a detection signal output from this acceleration sensor 28. Also, as in each of the above embodiments, the acceleration sensor 28 may be provided at the attachment positions of various optical systems.

[0128] In each of the above embodiments, the vibration of the objective lens 12a and the like is detected by the acceleration sensor 28. However, instead of the acceleration sensor 28, any of various known vibration detection units capable of detecting the vibration of the objective lens 12a and the like may be used.

[0129] In the above embodiments, the stationary ophthalmic apparatus 1 has been described as an example, but the present invention can also be applied to a handheld ophthalmic apparatus 1. [Explanation of symbols]

[0130] 1…Ophthalmology equipment 2. Base 3…Face support part 3a…Chin rest 3b…Forehead support 4. Driving mechanism 5…Measuring head 6…Display section 6a…Display panel 6b…Metal plate 9...Control device 12...Observation optical system 12a…Objective lens 12b…Dichroic filter 12c…Half mirror 12d…Relay lens 12e…Dichroic filter 12f...Imaging lens 12g…Image sensor 12h…Kerato board 12i…Keratography light source 13…Z alignment optical system 13a…Alignment light source 13b…Projection lens 14...XY alignment optical system 14a…Alignment light source 14b…Projection lens 15…Target projection optical system 15a...Optotype display section 15b...Half mirror 15c…Relay lens 15d…Reflective mirror 15e…Focusing lens 15f…Relay lens 15g...field lens 15h…VCC lens 15i…Reflective mirror 15j…Dichroic filter 15k…Glare light source 16...Measurement pattern projection optical system 16a…Reflection measurement unit 16b…Relay lens 16c...Eye ring 16d…Field lens 16e...Hole prism 16f...Rotary prism 16h…LED light source 16i…Collimator lens 16j...Cone prism 16k…forming plate 17…Receiving optical system 17a…Field lens 17b…Reflective mirror 17c…Relay lens 17d…Focusing lens 17e…Reflective mirror 27...Interlocking movement mechanism 28...Accelerometer 30…Lens holder 32…Sensor mounting part 34...Image sensor holder 36…Sensor mounting part 40...Alignment control unit 42... Eye characteristic measurement control unit 44...Eye characteristic calculation section 46…Signal acquisition section 48…Reliability Evaluation Department 49… Selection Department 50...Display control unit 52...Notification control unit 56…Measurement result column 58...Warning information 59…Reliability coefficient 60…Sensor mounting part 62...Rubber spacer 70…Non-contact tonometer 72…Measuring head 74…Nozzle 76…Window glass 78…Glass holder E…Examined eye Ec…cornea Ef…fundus G…Center of gravity position LA…1st distance LB…Second distance M1, M2, M3...Measurement section O1…main optical axis O2, O3, O4...Optical axis PA: Suspended section

Claims

1. An ophthalmologic apparatus including an ophthalmic characteristic acquisition unit for acquiring ophthalmic characteristics of a subject's eye, a vibration detection unit that detects vibration of the ophthalmologic apparatus at least while the eye characteristic acquisition unit is acquiring the eye characteristic; and a reliability evaluation unit that evaluates reliability of the result of the eye characteristic acquisition unit based on a detection result of the vibration detection unit; and An ophthalmic apparatus comprising:

2. The ophthalmologic apparatus according to claim 1 , further comprising a notification unit that notifies warning information when the reliability evaluation unit evaluates the reliability to be low.

3. a display unit that displays the acquisition results acquired by the eye characteristic acquisition unit; a display control unit that causes only the acquisition results that have been evaluated as having high reliability by the reliability evaluation unit to be displayed on the display unit; The ophthalmic device of claim 1 .

4. The ophthalmologic apparatus according to claim 1 , further comprising a selection unit that keeps the acquisition results that have been evaluated by the reliability evaluation unit as having high reliability and deletes the acquisition results that have been evaluated by the reliability evaluation unit as having low reliability.

5. the eye characteristic acquisition unit includes an objective lens, a measurement light source that projects measurement light onto the subject's eye, an image sensor that captures an image of return light from the subject's eye onto which the measurement light is projected, and an alignment detection system that detects a relative position of the subject's eye with respect to the eye characteristic acquisition unit, The ophthalmologic apparatus according to claim 1 , wherein the vibration detection unit is provided at a mounting position of at least one of the objective lens, the measurement light source, the image sensor, and the alignment detection system.

6. The ophthalmologic apparatus according to claim 5 , wherein the vibration detection unit is provided at the mounting position via a flexible mounting member.

7. an operation unit that is provided in the ocular characteristic acquisition unit and receives an input operation from an examiner; the operation unit is provided at a position farther from a center of gravity of the ophthalmologic apparatus than the eye characteristic acquisition unit is, The ophthalmologic apparatus according to claim 1 , wherein the vibration detection unit is provided in the operation unit.

8. an operation unit that is provided in the ocular characteristic acquisition unit and receives an input operation from an examiner; the operation unit is provided at a position farther from a center of gravity of the ophthalmologic apparatus than the eye characteristic acquisition unit is, An ophthalmic device as described in any one of claims 1 to 4, wherein a holding unit is provided in the eye characteristic acquisition unit to hold the vibration detection unit at a second distance away from the center of gravity position that is longer than the first distance, when the distance from the center of gravity position to the operation unit is defined as a first distance.

9. the eye characteristic acquisition unit is a non-contact tonometer that blows air onto the subject's eye from a nozzle, The ophthalmic apparatus according to claim 1 , wherein the vibration detection unit is provided at a mounting position of the nozzle.

10. The ophthalmologic apparatus according to claim 1 , wherein the vibration detection unit is an acceleration sensor.

11. A method for operating an ophthalmic apparatus including an ophthalmic characteristic acquisition unit for acquiring ocular characteristics of a subject's eye, comprising: a vibration detection step of detecting vibration of the ophthalmologic apparatus at least while the eye characteristic acquisition unit is acquiring the eye characteristic; a reliability evaluation step of evaluating reliability of the result of the eye characteristic acquisition by the eye characteristic acquisition unit based on a detection result of the vibration detection step; A method for operating an ophthalmic device comprising the steps of:

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