JP6499884B2 - Ophthalmic equipment - Google Patents

Description

  The present invention relates to an ophthalmologic apparatus.

  In the field of ophthalmology, an apparatus capable of obtaining eye information to be examined such as refractive power by projecting a predetermined pattern light on the fundus of the eye to be examined and analyzing a pattern image based on the return light from the fundus is used.

  Such an ophthalmologic apparatus includes, for example, a measurement head provided to be movable in the left-right direction, the up-down direction, and the front-back direction with respect to the base. The measuring head projects the pattern light onto the fundus of the eye to be examined, and optically aligns the optical system with the eye to be examined and optically obtains a pattern image based on the return light from the fundus. Alignment means and the like. For example, the alignment means aligns the position of the optical system with the center of gravity of the pupil of the eye to be examined or the position of the apex of the cornea. The ophthalmologic apparatus optically acquires a pattern image based on the return light from the fundus in the aligned state.

JP 2000-296110 A

  However, depending on the type of disease of the eye to be examined, the pattern image based on the return light from the fundus cannot be analyzed, and the eye information to be examined may not be obtained. For example, when the eye to be examined is a cataract eye, depending on the turbidity of the crystalline lens, the pattern light irradiated to the eye to be examined is diffused, so that a sufficient amount of light does not reach the fundus or the return light from the fundus is detected sufficiently I can't. In this case, the contour portion of the pattern image is blurred, and the shape of the pattern image cannot be analyzed.

  The present invention has been made to solve such problems, and an object of the present invention is to provide an ophthalmologic apparatus capable of obtaining eye information such as refractive power even for an eye having a disease. There is.

The ophthalmologic apparatus according to an embodiment, a projection system for projecting a pattern light to the fundus of the eye, a light receiving system for detecting return light from the fundus of the projected patterned light by the projection system, the return detected by the light receiving system An optical system including an optical member that changes the focus state of an image based on light, a display control unit that displays an image on a display unit, an operation unit that changes the focus state of the image, and operation contents for the operation unit based comprising an optical member controller for controlling the optical member, and a calculation unit for leaving calculate the refractive power of the eye as the eye to be examined information based on the control content for the image and the optical member. The display control unit causes a display unit to display a reference pattern image representing an image based on pattern light projected on a predetermined reference examination eye or eye to be examined in a predetermined focus state on the image based on pattern light.

  According to the ophthalmologic apparatus according to the present invention, it is possible to obtain eye information such as refractive power even for an eye to be examined with a disease.

It is the schematic which shows the structural example of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the ophthalmologic apparatus which concerns on embodiment. It is a flowchart which shows the operation example of the ophthalmologic apparatus which concerns on embodiment. It is explanatory drawing of the operation example of the ophthalmologic apparatus which concerns on embodiment. It is explanatory drawing of the operation example of the ophthalmologic apparatus which concerns on embodiment. It is explanatory drawing of the operation example of the ophthalmologic apparatus which concerns on embodiment. It is explanatory drawing of the operation example of the ophthalmologic apparatus which concerns on embodiment. It is explanatory drawing of the operation example of the ophthalmologic apparatus which concerns on embodiment.

  The ophthalmologic apparatus according to the embodiment can perform any subjective examination and / or any objective examination. The ophthalmologic apparatus according to the following embodiments can execute a distance test, a near-field test, a contrast test, a glare test, etc. as a subjective test, and an objective refraction measurement, a corneal shape measurement, etc. Is an optometry apparatus (auto reflex keratometer). However, the ophthalmologic apparatus according to the present invention is not limited to this, and includes an optical system for projecting pattern light onto the fundus of the eye to be examined and optically acquiring a pattern image based on return light from the fundus. In the ophthalmologic apparatus configured with the optical member for changing the focus state of the pattern image, the eye information (optical characteristics (value) of the eye to be examined) is obtained by analyzing the pattern image whose focus state has been changed. Any device that can be calculated may be used.

  As an ophthalmologic apparatus to which the present invention can be applied, there are an optical coherence tomography (hereinafter referred to as OCT) apparatus, an axial length measuring apparatus, a tonometer and the like in addition to the optometry apparatus according to the following embodiment. . The OCT apparatus is an apparatus that performs OCT on an arbitrary part of an eye to be examined such as a fundus or an anterior eye. The axial length measuring device is, for example, a device that measures the distance from the corneal apex position to the front surface of the retina as the axial length by irradiating light on the subject's eye. A tonometer is a device that measures intraocular pressure based on, for example, the amount of return light from the cornea obtained by illuminating the anterior segment of the subject's eye to which compressed air is blown, the pressure of compressed air, and the like. is there.

[Constitution]
(Appearance structure of ophthalmic device)
An external configuration of the ophthalmologic apparatus according to the embodiment is shown in FIG. The ophthalmologic apparatus 1 includes a base 2, a gantry 3, a head unit 4, a face receiving unit 5, a joystick 8, and a display unit 10. The ophthalmologic apparatus 1 may be a single apparatus or a combination of two or more apparatuses. In the latter case, a plurality of components described below are distributed in two or more apparatuses. For example, the ophthalmologic apparatus 1 includes an apparatus including an optical system, a driving mechanism, a control board, and the like for performing an examination, and a device for performing control and information input to the apparatus, and processing of output information from the apparatus. Consists of.

  The gantry 3 can be moved back and forth and left and right with respect to the base 2. The head unit 4 is configured integrally with the gantry 3. The face receiving portion 5 is configured integrally with the base 2.

  The face receiving portion 5 is provided with a chin rest 6 and a forehead rest 7. The face of the subject (not shown) is fixed by the face receiving unit 5. For example, the examiner performs an examination by positioning the ophthalmologic apparatus 1 on the opposite side of the subject. The joystick 8 and the display unit 10 are arranged at the position on the examiner side. The joystick 8 is provided on the gantry 3. The display unit 10 is provided on the surface of the head unit 4 on the examiner side. The display unit 10 is, for example, a flat panel display such as a liquid crystal display. The display unit 10 includes a touch panel display screen 10a.

  The head unit 4 is moved back and forth and left and right by tilting the joystick 8. The head unit 4 is moved in the vertical direction by rotating the joystick 8 with respect to its axis. By these operations, the position of the head unit 4 with respect to the face of the subject held by the face receiving unit 5 changes. The movement in the left-right direction is performed, for example, in order to switch the examination target by the ophthalmologic apparatus 1 from the left eye to the right eye or from the right eye to the left eye.

  An external device 11 is connected to the ophthalmologic apparatus 1. The external device 11 may be an arbitrary device, and the connection mode (communication mode or the like) between the ophthalmic device 1 and the external device 11 may be arbitrary. The external device 11 includes, for example, a spectacle lens measurement device for measuring the optical characteristics of the lens. The spectacle lens measuring device measures the power of the spectacle lens worn by the subject and inputs this measurement data to the ophthalmic device 1. The external device 11 may be any other ophthalmic device. The external device 11 may be a device (reader) having a function of reading information from a recording medium or a device (writer) having a function of writing information to the recording medium.

  Another example of the external device 11 is a computer used in the medical institution. Such hospital computers include, for example, a hospital information system (HIS) server, a DICOM server, a doctor terminal, and the like. The external device 11 may include a computer that is used outside the medical institution. Examples of such out-of-hospital computers include mobile terminals, personal terminals, servers and terminals on the manufacturer side of the ophthalmic apparatus 1, and cloud servers.

(Configuration of optical system)
The ophthalmologic apparatus 1 has an optical system for inspecting an eye to be examined. A configuration example of this optical system will be described with reference to FIG. The optical system is provided in the head unit 4. The optical system includes an observation system 12, a fixation target projection system 13, an objective measurement system 14, a subjective measurement system 15, and alignment systems 16 and 17. Reference numeral 9 denotes a processing unit that executes various processes.

  The observation system 12 has a function for observing the anterior segment of the eye E. The fixation target projection system 13 has a function for presenting a fixation target to the eye E. The objective measurement system 14 has a function for performing an objective test. The objective measurement system 14 in this example has a function of projecting a predetermined measurement pattern light (pattern light) onto the fundus oculi Ef of the eye E and an image (pattern) based on the return light of the measurement pattern light projected onto the fundus oculi Ef. Image). The subjective measurement system 15 has a function for performing a subjective examination. The subjective measurement system 15 of this example has a function of presenting a visual target to the eye E to be examined. The alignment systems 16 and 17 have a function for aligning the optical system with the eye E (alignment). The alignment system 16 has a function for performing alignment in the direction (front-rear direction) along the optical axis of the observation system 12. The alignment system 17 has a function for performing alignment in a direction (vertical direction, horizontal direction) orthogonal to the optical axis of the observation system 12.

(Observation system 12)
The observation system 12 includes 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 an image sensor (CCD) 12g. The output of the image sensor 12g is input to the processing unit 9. The processing unit 9 displays the anterior segment image E ′ on the display unit 10 based on the signal input from the image sensor 12g.

  A kerato plate 12h is provided between the objective lens 12a and the eye E to be examined. The kerato plate 12h is used to project a ring-shaped light beam for measuring the corneal shape onto the cornea K of the eye E. A configuration example of the kerato plate 12h is shown in FIG.

(Alignment systems 16 and 17)
An alignment system 16 is provided behind the kerato plate 12h. As described above, the alignment system 16 is used for alignment in the front-rear direction. The alignment system 16 includes an alignment light source 16a and a projection lens 16b. The projection lens 16b converts the light beam output from the alignment light source 16a into a parallel light beam and projects it onto the cornea K. The user or the processing unit 9 performs alignment by moving the head unit 4 in the front-rear direction with reference to an image (bright spot image) projected onto the cornea K by the alignment system 16.

  The alignment system 17 forms an optical path branched from the observation system 12 via the half mirror 12c. As described above, the alignment system 17 is used for vertical and horizontal alignment. The alignment system 17 includes an alignment light source 17a and a projection lens 17b. The projection lens 17b converts the light beam output from the alignment light source 17a into a parallel light beam. This parallel light beam is reflected by the half mirror 12 c and projected onto the cornea K through the optical path of the observation system 12. The user or the processing unit 9 performs alignment by moving the head unit 4 in the vertical direction and the horizontal direction based on the image (bright spot image) projected onto the cornea K by the alignment system 17.

  As shown in FIG. 2, an alignment mark AL and an index image (bright spot image) Br are displayed on the display screen 10a together with the anterior segment image E '. The alignment in the front-rear direction is performed, for example, by adjusting the position of the head unit 4 so that the index image Br is focused by the alignment light source 17a. Further, the alignment in the front-rear direction may be performed by adjusting the position of the head unit 4 so that the ratio of the distance between the two bright spot images by the alignment light source 16a and the diameter of the keratling image falls within a predetermined range.

  When the alignment is performed manually, the user adjusts the position of the head unit 4 by operating the joystick 8 while referring to the information displayed on the display screen 10a, for example. At this time, for example, the processing unit 9 may calculate an alignment shift amount from the ratio and display the shift amount on the display screen 10a. The processing unit 9 can perform control so as to start measurement in response to the completion of alignment.

  When the alignment is performed automatically, for example, the processing unit 9 calculates an alignment shift amount from the above ratio, and moves the head unit 4 by controlling the electric mechanism so that the shift amount is canceled. This mechanism includes an actuator that generates a driving force and a member that transmits the driving force to the head unit 4. The processing unit 9 can perform control so as to start measurement in response to the completion of alignment.

  In this embodiment, when the left-right direction is the X direction (first direction), the up-down direction is the Y direction (second direction) orthogonal to the left-right direction, and the front-rear direction is the Z direction orthogonal to both the left-right direction and the up-down direction. (Third direction).

(Fixation target projection system 13, subjective measurement system 15)
The fixation target projection system 13 (a subjective measurement system 15) includes an LED light source 13a that generates white light, a color correction filter 13b, a collimator lens 13b ′, a chart plate 13c, a half mirror 13d, and a relay lens 13e. A reflecting mirror 13f, a focusing lens 13g, a relay lens 13h, a field lens 13i, a variable cross cylinder lens (hereinafter referred to as a VCC lens) 13j, a reflecting mirror 13k, dichroic filters 13m and 12b, and an objective lens. 12a. The subjective measurement system 15 includes a glare light source 13n that irradiates the eye E with glare light.

  A fixation target and a target chart are formed on the chart plate 13c. The fixation target is a target for fixing the eye E to be examined. The fixation target in this example is, for example, a landscape chart. The optotype chart is an optotype for subjectively measuring the visual acuity value and correction power (distance power, near power, etc.) of the eye E. In this example, a plurality of target charts are formed on the chart plate 13c.

  In an objective test (objective refraction measurement or the like), a landscape chart is projected onto the fundus oculi Ef. Alignment is performed while the subject is staring at the scenery chart, and the eye refractive power is measured in a clouded state.

(Objective measurement system 14)
The objective measurement system 14 includes a ring-shaped light beam projection system 14A and a ring-shaped light beam light receiving system 14B. The ring-shaped luminous flux projection system 14A projects ring-shaped measurement pattern light (ring pattern light) onto the fundus oculi Ef. The ring-shaped light beam receiving system 14B detects return light (reflected light) from the fundus oculi Ef of the measurement pattern light.

  The ring-shaped luminous flux projection system 14A includes a reflex measurement unit 14a, a relay lens 14b, a pupil ring 14c, a field lens 14d, a perforated prism 14e, a rotary prism 14f, dichroic filters 13m and 12b, and an objective lens. 12a. The reflex measurement unit 14a includes a reflex measurement light source (LED) 14h, a collimator lens 14i, a conical prism 14j, and a ring-shaped measurement pattern forming plate 14k.

  The ring-shaped light beam receiving system 14B includes an objective lens 12a, a dichroic filter 12b, a dichroic filter 13m, a rotary prism 14f, a perforated prism 14e, a field lens 14m, a reflection mirror 14n, and a relay lens 14p. It includes a focusing lens 14q, a reflecting mirror 14r, a dichroic filter 12e, an imaging lens 12f, and an image sensor (CCD) 12g.

  Each unit of the ophthalmologic apparatus 1 is controlled by the processing unit 9. For example, the processing unit 9 includes the LED light source 13a, the light source 14h, the glare light source 13n, the alignment light sources 16a and 17a, the kerato ring light source 12h ′ of the kerato plate 12h, the reflex measurement unit portion 14a, the focusing lenses 13g and 14q, and the chart plate 13c. , VCC lens 13j, display unit 10 and the like are controlled.

(alignment)
The ophthalmologic apparatus 1 moves the head unit 4 with respect to the subject's eye to be examined fixed to the face receiving unit 5, thereby obtaining various types of information about the subject's eye with respect to the subject's eye E. It is possible to perform alignment (alignment).

  When alignment is performed, the processing unit 9 turns on the alignment light sources 16a and 17a. The light beam output from the alignment light source 16a is projected onto the cornea K via the projection lens 16b and the kerato plate 12h. The light beam projected onto the cornea K is guided to the imaging element 12g via the kerato plate 12h, the objective lens 12a, the dichroic filter 12b, the half mirror 12c, the relay lens 12d, the dichroic filter 12e, and the imaging lens 12f. Thereby, two index images (bright spot images) of the alignment light source 16a are formed on the image sensor 12g. On the display screen 10a, index images (bright spot images) Lr1 and Lr2 are displayed on the anterior segment image E '. For example, the processing unit 9 controls the actuator so that the index images Lr1 and Lr2 have a predetermined positional relationship, thereby moving the head unit 4 in the front-rear direction to perform front-rear alignment.

  The light beam output from the alignment light source 17a is projected onto the cornea K via the projection lens 17b, the half mirror 12c, the dichroic filter 12b, the objective lens 12a, and the kerato plate 12h. The light beam projected onto the cornea K by the alignment light source 17a is guided to the imaging device 12g through the same path as the light beam projected onto the cornea K by the alignment light source 16a. Thereby, an index image (bright spot image) of the alignment light source 17a is formed on the image sensor 12g. On the display screen 10a, an index image Br is displayed on the anterior segment image E '. For example, the processing unit 9 moves the head unit 4 in the horizontal direction and the vertical direction by controlling the actuator so that the deviation amount between the position of the index image Br and the center position in the alignment mark AL is cancelled. Direction and vertical alignment.

(Cornea shape measurement function)
When the corneal shape measurement mode is selected, the processing unit 9 turns on the kerating light source 12h ′. The light beam output from the kerato ring light source 12h ′ is projected onto the cornea K as a corneal shape measuring ring light beam. The dichroic filter 12b transmits the corneal shape measurement ring-shaped light beam projected onto the cornea K. As a result, the image sensor 12g detects an image (not shown) of the corneal shape measurement ring-shaped light beam.

(Objective measurement function)
When the objective measurement mode is selected, the processing unit 9 turns on the light source 14h. The reflex measurement unit 14a is moved in the optical axis direction, and the focusing lens 13g is moved in the optical axis direction correspondingly. The reflex measurement unit 14a, the focusing lens 13g, and the focusing lens 14q are configured to move in the respective optical axis directions in conjunction with each other.

  The light from the light source 14h is converted into parallel light by the collimator lens 14i, and is guided to the relay lens 14b as ring-shaped measurement pattern light (light beam) via the conical prism 14j and the ring-shaped measurement pattern forming plate 14k. The ring-shaped measurement pattern light is guided to the dichroic filter 13m via the relay lens 14b, the pupil stop 14c, the field lens 14d, and the reflection surface 14e 'of the perforated prism 14e. The measurement pattern light reflected by the dichroic filter 13m is guided to the objective lens 12a via the dichroic filter 12b and projected onto the fundus oculi Ef.

  The ring-shaped measurement pattern light formed on the fundus oculi Ef is collected by the objective lens 12a, and the dichroic filters 12b and 13m, the rotary prism 14f, the hole 14e "of the holed prism 14e, the field lens 14m, the reflection mirror 14n, The image is formed on the image sensor 12g by the imaging lens 12f via the relay lens 14p, the focusing lens 14q, the reflection mirror 14r, and the dichroic filter 12e, whereby the image sensor 12g returns the return light of the ring-shaped measurement pattern light. The image (measurement pattern image, not shown) formed by the above is detected.

(Awareness measurement function)
When the awareness measurement mode is selected, the processing unit 9 turns on the LED light source 13a. The luminous flux output from the LED light source 13a illuminates the chart plate 13c via the color correction filter 13b. Various charts (charts) are provided on the chart plate 13c. Further, the processing unit 9 moves the focusing lens 13g to a position corresponding to the result of the objective measurement. Similarly, the processing unit 9 controls the VCC lens 13j so that the astigmatism state is corrected based on the astigmatism state (astigmatism degree, astigmatism axis) of the eye E obtained by objective measurement.

  When the examiner or the processing unit 9 selects the target, the processing unit 9 controls the chart plate 13c so that the selected target is arranged in the optical path. The luminous flux that has passed through the target is a half mirror 13d, a relay lens 13e, a reflecting mirror 13f, a focusing lens 13g, a relay lens 13h, a field lens 13i, a VCC lens 13j, a reflecting mirror 13k, dichroic filters 13m and 12b, and an objective lens. 12a is projected onto the fundus oculi Ef.

  The subject responds to the visual target projected onto the fundus oculi Ef. The selection of the target and the response thereto are repeatedly performed based on the judgment of the examiner or the processing unit 9. The examiner or the processing unit 9 determines the prescription value based on the response from the subject. Further, when the glare inspection is performed, the processing unit 9 turns on the glare light source 13n. In this state, awareness measurement is performed.

  Configuration of objective measurement system 14, configuration of subjective measurement system 15, configuration of alignment systems 16 and 17, configuration of kerato system, measurement principle of eye refractive power (ref), measurement principle of subjective measurement, measurement of corneal shape Since the principle is well-known, detailed description is abbreviate | omitted.

(Information processing system configuration)
The information processing system of the ophthalmologic apparatus 1 will be described. An example of the functional configuration of the information processing system of the ophthalmologic apparatus 1 is shown in FIG. The information processing system includes a control unit 100, an inspection unit 110, a display unit 130, an operation unit 140, and a communication unit 150. The control unit 100 controls the inspection unit 110, the display unit 130, and the communication unit 150.

(Inspection unit 110)
The inspection unit 110 can perform a plurality of different types of inspection. In the ophthalmologic apparatus 1 having the configuration shown in FIG. 2, a plurality of examinations including objective refraction measurement, subjective refraction measurement (distance examination, near-distance examination, contrast examination, glare examination, etc.) and corneal shape measurement are executed. be able to.

  The inspection unit 110 includes an optical system 111 and a moving mechanism 112. The optical system 111 projects ring-shaped measurement pattern light (pattern light) onto the fundus oculi Ef of the eye E, and optically acquires a measurement pattern image (pattern image) based on return light from the fundus oculi Ef.

  The optical system 111 includes a projection system 111A, a light receiving system 111B, and an optical member 111C. The projection system 111A projects ring-shaped measurement pattern light onto the fundus oculi Ef of the eye E. The light receiving system 111B detects return light from the fundus oculi Ef of the measurement pattern light projected by the projection system 111A. The optical member 111C changes the focus state of the measurement pattern image based on the return light detected by the light receiving system 111B. In FIG. 2, the ring-shaped luminous flux projection system 14A is an example of a projection system 111A. The ring-shaped light beam receiving system 14B is an example of the light receiving system 111B. The focusing lens 13g and the focusing lens 14q are examples of the optical member 111C.

  The moving mechanism 112 moves the optical system 111 relative to the eye to be examined. The moving mechanism 112 is a mechanism that drives the optical system 111 and an optical member that constitutes the optical system 111, an actuator that generates a driving force that can be controlled by the control unit 100, and the driving force that is used for the optical system 111 and the optical system 111. And a member that transmits to the optical member that constitutes. Moreover, the test | inspection part 110 may include the function which calculates | requires a test result by analyzing the data acquired by the optical system. In that case, the inspection unit 110 includes at least a part of the processing unit 9 shown in FIG.

(Display unit 130, operation unit 140)
The display unit 130 displays information under the control of the control unit 100. The display unit 130 includes the display unit 10 shown in FIG.

  The operation unit 140 is used for operating the ophthalmologic apparatus 1. The operation unit 140 includes various hardware keys (joystick 8, buttons, switches, etc.) provided in the ophthalmologic apparatus 1. The operation unit 140 includes various software keys (buttons, icons, menus, etc.) displayed on the touch panel display screen 10a.

  At least a part of the display unit 130 and the operation unit 140 may be integrally configured. A typical example is a touch panel display screen 10a.

(Communication unit 150)
The communication unit 150 has a function for communicating with the external device 11 shown in FIG. The communication unit 150 is provided in the processing unit 9, for example. The communication unit 150 has a configuration corresponding to the form of communication with the external device 11.

(Control unit 100)
The information processing system is configured around the control unit 100. The control unit 100 executes various types of information processing such as arithmetic processing and control processing. The control unit 100 includes at least a part of the processing unit 9 shown in FIG. The control unit 100 includes an inspection control unit 101, a display control unit 102, a calculation unit 103, a storage unit 104, and a capture unit 105.

(Inspection control unit 101)
The inspection control unit 101 controls the inspection unit 110. Specifically, the inspection control unit 101 includes an LED light source 13a, a light source 14h, a glare light source 13n, alignment light sources 16a and 17a, a kerat light source 12h ′ of a kerato plate 12h, a reflex measurement unit 14a, and focusing lenses 13g and 14q. The chart plate 13c, the VCC lens 13j, and the like are controlled.

  The inspection control unit 101 can adjust the focus state of the measurement pattern image based on the return light from the fundus oculi Ef. In the case of automatic adjustment, the inspection control unit 101 controls the moving mechanism 112 according to a known focus adjustment method such as a contrast difference detection method or a phase difference detection method, for example, to thereby adjust the focusing lens 13g and the focusing lens 14q. Is controlled in the optical axis direction. When adjusting manually, for example, while displaying manual focus information such as an index, the inspection control unit 101 controls the moving mechanism 112 based on the operation content of the user operation unit 140 referring to the manual focus information. Thus, the positions of the focusing lens 13g and the focusing lens 14q in the optical axis direction are controlled.

  In addition, the inspection control unit 101 can control each of the above units based on the user's operation details on the operation unit 140. For example, the inspection control unit 101 can adjust the focus state of the measurement pattern image based on the return light from the fundus oculi Ef based on the user's operation details on the operation unit 140.

(Display control unit 102)
The display control unit 102 displays various information on the display unit 130. In this embodiment, the display control unit 102 displays an image of the eye to be examined on the display unit 130 (display unit 10) having the touch panel display screen 10a. Examples of the eye image include a real-time image of the eye to be examined, an image of the eye to be examined that has been acquired in the past, an image of the eye to be registered in advance, and an image (schematic diagram, schema) that schematically represents the eye to be examined. The real-time image of the eye to be examined may be an anterior segment image obtained from the detection result of the image sensor 12g. The display control unit 102 may further display the alignment mark AL superimposed on the image of the eye to be examined. The display control unit 102 may further display the index images Br, Lr1, and Lr2 superimposed on the image of the eye to be examined.

  The display control unit 102 can display an operation screen on the display unit 130 having the touch panel display screen 10a. On the operation screen, a measurement pattern image based on the return light from the fundus oculi Ef and an instruction input unit for changing the focus state of the measurement pattern image are displayed. The measurement pattern image is an image formed on the image sensor 12g by the return light from the fundus oculi Ef of the eye E to which the ring-shaped measurement pattern light is projected. The user can perform an instruction operation for moving the focusing lens 13g and the focusing lens 14q in the optical axis direction with respect to the instruction input unit.

  The operation screen may further include a transition instruction input unit for shifting to the clouded vision state, a capture instruction input unit for capturing the measurement pattern image displayed on the operation screen, and the like. The user can perform an instruction operation for shifting to the cloud-viewing state with respect to the shift instruction input unit. Further, the user can perform an instruction operation for capturing an image of the eye to be examined or a measurement pattern image as a still image on the capture instruction input unit.

  Further, the display control unit 102 may display the operation screen superimposed on an image of the eye to be examined such as an anterior segment image. Accordingly, the user can perform an instruction operation on various instruction input units displayed on the operation screen while confirming the state of the eye to be examined.

(Calculation unit 103)
The calculation unit 103 calculates the eye information to be examined based on the measurement pattern image based on the return light from the fundus oculi Ef and the control contents for the focusing lens 13g and the focusing lens 14q. When the focus state of the measurement pattern image is automatically adjusted, the control contents for the focusing lens 13g and the focusing lens 14q are the focusing lens 13g and the focusing performed by the inspection control unit 101 according to a known focus adjustment method. This corresponds to the control content for the lens 14q. When the focus state of the measurement pattern image is manually adjusted, the control content of the focusing lens 13g and the focusing lens 14q corresponds to the user operation content on the operation unit 140.

  The calculation unit 103 can calculate the refractive power of the eye E as the eye information. For example, the calculation unit 103 analyzes the shape (including size, the same applies hereinafter) of the measurement pattern image while taking into account the focus state of the measurement pattern image that has been changed using the operation unit 140, and thereby the refractive power of the eye E to be examined. Ask for.

  The calculation unit 103 includes a specifying unit 103A and a refractive power calculation unit 103B. Storage unit 104 includes a reference pattern storage unit 104A.

(Specification part 103A)
The specifying unit 103A specifies the shape of the measurement pattern image. The specifying unit 103A can acquire the measurement pattern image formed on the imaging element 12g, and can specify the shape of the measurement pattern image by performing predetermined image processing on the acquired measurement pattern image. is there. For example, the specifying unit 103A detects the position (pixel) of the edge of the measurement pattern image by scanning the acquired measurement pattern image in a plurality of meridian directions. The specifying unit 103A performs ellipse approximation by applying a least square method or the like to the edge image specified by the detected positions of the plurality of edges, and specifies the approximate ellipse as the shape of the measurement pattern image. Further, for example, the specifying unit 103A performs thinning processing on the acquired measurement pattern image, performs elliptic approximation by applying a least square method or the like to the pattern image specified by the thinning processing, This approximate ellipse may be specified as the shape of the measurement pattern image.

  In this embodiment, when the shape of the measurement pattern image cannot be specified using the image processing as described above, the operation unit 140 has three or more users for the measurement pattern image displayed on the display unit 130. Used to specify the position of feature points. For example, the user designates the positions of three or more feature points on the measurement pattern image by a touch operation in a frame in which the measurement pattern image displayed on the touch panel display screen 10a is drawn. The specifying unit 103A specifies an approximate ellipse by performing an ellipse approximation process based on the position of the feature point of the measurement pattern image specified by the operation.

(Refractive power calculator 103B)
The refractive power calculation unit 103B calculates the refractive power of the eye E based on the ellipse shape specified by the specifying unit 103A and the control content for the focusing lens 13g and the focusing lens 14q (control content for the optical member 111C). To do. For example, the refractive power calculation unit 103B determines the spherical power S as the refractive power of the eye E based on the elliptical shape specified by the specifying unit 103A and the diopter for focus adjustment for the focusing lens 13g and the focusing lens 14q. Astigmatism power C and astigmatism axis angle A are obtained.

  The length of the major axis of the specified elliptical shape is M1, the length of the minor axis is M2, the radius of the measurement pattern image at 0 diopter is d1, and the focus adjustment amount for the focusing lens 13g and the focusing lens 14q. When the diopter is DP, the refractive power calculation unit 103B can obtain the spherical power S by calculating S = ((M1 + M2) / 2−d1) + DP, for example. The measurement pattern image at 0 diopter is projected onto the fundus of the subject eye or the reference test eye (for example, model eye) at the in-focus position of the focusing lens 13g and the focusing lens 14q when adjusted to 0 diopter. It is an image formed based on the return light of the ring-shaped measurement pattern light. Further, the refractive power calculation unit 103B can obtain the astigmatism power C by a known formula (C = M1-M2). Similarly, the refractive power calculation unit 103B can determine the astigmatism axis angle A according to a known formula using the major axis length M1 and the minor axis length M2.

(Storage unit 104)
The storage unit 104 stores various computer programs and data. The computer program includes a calculation program and a control program for causing the ophthalmologic apparatus 1 to execute various examinations. The data includes data used in various tests. An example of such data is a reference pattern.

(Reference pattern)
The reference pattern represents the shape of the reference pattern image. The reference pattern image is a measurement pattern image formed based on measurement pattern light projected in a predetermined focus state onto a predetermined reference inspection eye or eye to be examined. In this embodiment, the reference pattern is formed in a ring shape based on the return light of the ring-shaped measurement pattern light projected onto the fundus portion of the model eye with the focus state adjusted to 0 diopter (0D). Represents the shape of the measurement pattern image. The reference pattern is generated in advance and stored in the reference pattern storage unit 104A by the control unit 100.

  The display control unit 102 can read the reference pattern stored in the reference pattern storage unit 104A, and cause the display unit 130 to display the reference pattern image corresponding to the reference pattern superimposed on the measurement pattern image. Accordingly, the user can change the focus state of the measurement pattern image using the operation unit 140 so as to match the shape of the reference pattern image while referring to the reference pattern image, for example.

(Capture part 105)
The capture unit 105 captures the measurement pattern image as a still image. The measurement pattern image captured by the capture unit 105 is stored in the storage unit 104. The calculation unit 103 (refractive power calculation unit 103B) calculates the refractive power using the above formula based on the measurement pattern image captured by the capture unit 105 and the control contents for the focusing lens 13g and the focusing lens 14q. To do.

[Operation example]
The operation of the ophthalmologic apparatus 1 will be described.

  FIG. 5 shows a flowchart of an operation example of the ophthalmologic apparatus 1. FIG. 5 shows an operation example when the reflex measurement is performed on the eye to be examined which is a cataract eye.

(S1)
First, when the user turns on the power of the ophthalmologic apparatus 1, puts the face of the subject on the face receiving unit 5, and instructs the start of measurement using the operation unit 140, the inspection control unit 101 starts alignment and the head The part 4 is moved to the examination position of the eye E. The inspection position is a position where the eye E can be inspected. The movement of the head unit 4 is executed according to an operation or instruction by the user or an instruction from the inspection control unit 101.

(S2)
Next, the inspection control unit 101 turns on the light source 14h. The light from the light source 14h is projected onto the fundus oculi Ef of the eye E as ring-shaped measurement pattern light by the ring-shaped light beam projection system 14A as described above. The return light of the measurement pattern light from the fundus oculi Ef is imaged as a ring-shaped measurement pattern image on the imaging surface of the image sensor 12g by the ring-shaped light beam receiving system 14B as described above. Stored in the storage unit 104). The display control unit 102 displays an operation screen OG1 as shown in FIG. 6 on the display unit 130 (touch panel type display screen 10a).

  The operation screen OG1 displays a measurement pattern image RP and an instruction input unit SL1 for changing the focus state of the measurement pattern image RP. The instruction input unit SL1 is a slider configured such that the knob unit TM1 can move on a straight line (track) by a drag operation in a range of −20 diopter (−20D) to +20 diopter (+ 20D) with 0 diopter (0D) as the center. including. The position of the knob portion TM1 is associated with the position on the optical axis of each of the focusing lens 13g and the focusing lens 14q. When the user moves the position of the knob part TM1 by a drag operation, the inspection control unit 101 controls the moving mechanism 112 to control the focusing lens 13g and the focusing lens 13g at positions on the respective optical axes corresponding to the position of the knob part TM1. Each of the focal lenses 14q is moved.

  Note that the calculation unit 103 may perform an ellipse approximation process on the measurement pattern image RP and specify the major axis rd1 and the minor axis rd2 of the approximate ellipse obtained by the ellipse approximation process. The display control unit 102 may temporarily display the major axis rd1 and the minor axis rd2 of the ellipse specified by the calculation unit 103 so as to be superimposed on the measurement pattern image RP (see FIG. 6).

(S3)
Next, as shown in FIG. 7, the display control unit 102 causes the reference pattern image BP based on the reference pattern stored in the reference pattern storage unit 104A to be displayed superimposed on the measurement pattern image RP in the operation screen OG1.

(S4)
When the focus adjustment of the measurement pattern image RP is performed (S4: Y), the operation of the ophthalmologic apparatus 1 proceeds to S5. When the focus adjustment of the measurement pattern image RP is not performed (S4: N), the operation of the ophthalmologic apparatus 1 proceeds to S6.

  The ophthalmologic apparatus 1 can determine whether or not to adjust the focus of the measurement pattern image RP by analyzing the measurement pattern image RP displayed on the display unit 130 in S2. For example, the inspection control unit 101 specifies, as the contour portion of the measurement pattern image RP, a portion where the contrast difference near the contour of the measurement pattern image RP is equal to or greater than a predetermined first threshold value. The inspection control unit 101 determines that the focus adjustment of the measurement pattern image RP is performed when the width of the specified contour portion includes a portion that is equal to or larger than the predetermined second threshold value, and the width of the specified contour portion is the second threshold value. When the above portion is not included, it is determined that the focus adjustment of the measurement pattern image RP is not performed.

  Further, the inspection control unit 101 can determine whether or not to adjust the focus of the measurement pattern image RP based on the measurement pattern image RP and the reference pattern image BP. For example, the inspection control unit 101 compares the result of the predetermined first analysis process (contrast difference or the like of the contour portion) with respect to the reference pattern image BP and the result of the first analysis process with respect to the measurement pattern image RP, thereby measuring the measurement pattern. It is determined whether or not the focus adjustment of the image RP is performed.

  Further, the ophthalmologic apparatus 1 may perform the focus adjustment of the measurement pattern image RP based on the content of the user operation on the operation unit 140. For example, when the user gives an instruction to the operation unit 140, the operation of the ophthalmologic apparatus 1 proceeds to S5, and when there is no such instruction (or when there is an instruction not to perform focus adjustment), Operation proceeds to S6.

(S5)
When performing the focus adjustment of the measurement pattern image RP (S4: Y), the inspection control unit 101 controls the moving mechanism 112 according to a known focus adjustment method, for example, to change the focusing lens 13g and the focusing lens 14q. Move to the in-focus position. In addition, the inspection control unit 101 controls the moving mechanism 112 so that the diameter of the reference pattern image BP displayed in S3 substantially matches the major axis or minor axis of the measurement pattern image RP, whereby the focusing lens 13g and the focusing lens 13g. The focal lens 14q may be moved to the in-focus position.

  Further, the inspection control unit 101 can move the focusing lens 13g and the focusing lens 14q to the in-focus position by controlling the moving mechanism 112 based on the user's operation content on the operation unit 140. At this time, the user moves the knob TM1 of the instruction input unit SL1 by a touch operation so that the diameter of the reference pattern image BP displayed in S3 substantially matches the major axis or minor axis of the measurement pattern image RP. By controlling 112, the focusing lens 13g and the focusing lens 14q are moved to the focusing position. When it is on the minus side from the in-focus position, the measurement pattern image RP is displayed larger than the reference pattern image BP, and when it is on the plus side from the in-focus position, the measurement pattern image RP is displayed smaller than the reference pattern image BP. Therefore, the user moves the knob portion TM1 so that the major axis or minor axis of the measurement pattern image RP becomes a desired diameter using the diameter of the reference pattern image BP as a guideline, thereby aligning the focusing lens 13g and the focusing lens 14q. It can be moved to the focal position.

  When the focus adjustment as described above is completed, the operation of the ophthalmologic apparatus 1 proceeds to S6.

(S6)
As shown in FIG. 8, the display control unit 102 causes the operation screen OG1 to display a transition instruction input unit CB1 for shifting to the cloud fog state and a capture instruction input unit CB2 for capturing the measurement pattern image RP. When the transition instruction input unit CB1 in the operation screen OG1 is not designated by the user's touch operation and does not shift to the cloud fog state (S6: N), the operation of the ophthalmologic apparatus 1 shifts to S8. When the shift instruction input unit CB1 is designated by the user's touch operation and shifts to the cloud fog state (S6: Y), the operation of the ophthalmologic apparatus 1 shifts to S7.

(S7)
When the transition instruction input unit CB1 is designated by the user's touch operation (S6: Y), the inspection control unit 101 moves the focusing lens 13g and the focusing lens 14q so as to cloud the measurement pattern image RP.

(S8)
Next, the inspection control unit 101 waits until the capture instruction input unit CB2 in the operation screen OG1 displayed on the touch panel display screen 10a is designated by the user's touch operation (S8: N). When the capture instruction input unit CB2 is designated by the user's touch operation (S8: Y), the operation of the ophthalmologic apparatus 1 proceeds to S9.

(S9)
When the capture instruction input unit CB2 is designated by the user's touch operation (S8: Y), the capture unit 105 captures the measurement pattern image RP as a still image. That is, the capture unit 105 captures the measurement pattern image RP in a state where the measurement pattern image RP is fogged by the focusing lens 13g and the focusing lens 14q. The measurement pattern image captured by the capture unit 105 is stored in the storage unit 104. For example, the display control unit 102 switches the measurement pattern image RP before capture to the measurement pattern image RP ′ stored in the storage unit 104 and displays it on the operation screen OG1 of the display screen 10a.

  When the measurement pattern image RP is displayed superimposed on the image of the eye to be examined (anterior eye image or the like), the capture unit 105 can capture the image of the eye to be examined together with the measurement pattern image RP in S9. Is possible. Thereby, the user can determine whether the captured measurement pattern image RP is suitable for calculation of the eye information while checking the state of the eye.

(S10)
Next, the specifying unit 103A performs ellipse approximation on the measurement pattern image RP ′ captured in S9, specifies the approximated ellipse shape as the shape of the measurement pattern image RP ′, and specifies the specified measurement pattern image RP. The positions of three or more feature points (feature points P1 to P4 in FIG. 8) are designated.

  In S10, the operation unit 140 may receive designation of positions of three or more feature points by the user with respect to the measurement pattern image RP '. In this case, the specifying unit 103A specifies the feature points P1 to P4 specified by the user operation on the operation unit 140. Thereby, even when the eye E has a disease such as cataract, the user can specify the shape of the measurement pattern image RP ′ by visually specifying the feature points on the measurement pattern image RP ′. It becomes possible.

  In S10, each time a position of a new feature point is specified after the position of two or more feature points is specified using the operation unit 140, the specifying unit 103A includes three or more positions including the new feature point position. A new approximate ellipse may be specified based on the feature point position. At this time, the display control unit 102 may display the approximate ellipse with a dotted line or the like so that the identified new approximate ellipse can be identified. The refractive power calculation unit 103B calculates a new refractive power based on the new approximate ellipse specified by the specifying unit 103A, and the display control unit 102 displays the new refractive power calculated by the refractive power calculation unit 103B. It can be temporarily displayed on the screen 10a. Thereby, it becomes possible to easily determine whether or not the new refractive power calculated based on the position of the feature point designated by the user is appropriate.

(S11)
As illustrated in FIG. 9, the specifying unit 103A performs an ellipse approximation process based on the positions of three or more feature points specified by the user as described above to obtain an approximate ellipse represented by the measurement pattern image RP ″. The refractive power calculation unit 103B applies the approximate ellipse (the major axis rd1 ″ and the minor axis rd2 ″ represented in the measurement pattern image RP ″) identified by the identifying unit 103A, the focusing lens 13g, and the focusing lens 14q. Based on the control content (control content for the optical member 111C), the refractive power of the eye E (spherical power S, astigmatism power C, and astigmatism axis angle A) is calculated as described above. Thus, the operation of the ophthalmologic apparatus 1 ends (END).

  Note that the display control unit 102 may display the operation screen OG1 as shown in FIGS. 6 to 9 superimposed on the image of the eye to be examined (for example, the anterior eye image E ′). For example, as shown in FIG. 10, the display control unit 102 operates the anterior segment image E ′ (corneal image K ′, pupil image P ′) on which the alignment mark AL and the index image Br from the alignment light source 17a are superimposed and displayed. It is possible to superimpose and display the screen OG1.

[Action / Effect]
The operation and effect of the ophthalmologic apparatus according to the embodiment will be described.

  An ophthalmologic apparatus (for example, the ophthalmologic apparatus 1) according to the embodiment includes an optical system (for example, the optical system 111), a display control unit (for example, the display control unit 102), an operation unit (for example, the operation unit 140), An optical member control unit (for example, inspection control unit 101) and a calculation unit (for example, calculation unit 103) are included. The optical system includes a projection system (for example, projection system 111A), a light receiving system (for example, light receiving system 111B), and an optical member (for example, optical member 111C). The projection system projects light (eg, measurement pattern light) onto the fundus (eg, fundus oculi Ef) of the eye to be examined (eg, eye E to be examined). The light receiving system detects return light from the fundus of the light projected by the projection system. The optical member changes the focus state of an image (for example, a measurement pattern image) based on the return light detected by the light receiving system. The display control unit displays the image on a display unit (for example, the display unit 130). The operation unit is used to change the focus state of the image. The optical member control unit controls the optical member based on the operation content with respect to the operation unit. The calculation unit calculates eye information based on the image and the control content for the optical member.

  According to such a configuration, the image is identified by changing the focus state of the image based on the return light from the fundus, the identified image, and the operation content of the operation unit for changing the focus state, The eye information to be examined can be calculated based on the above. Thereby, even when the return light from the fundus cannot be sufficiently detected due to a disease associated with the eye to be examined, and the image based on the return light cannot be specified, the eye information on the eye to be examined is obtained. Will be able to.

  The projection system projects pattern light onto the fundus, the light receiving system detects return light from the fundus of the pattern light, and the calculation unit receives an image based on the image based on the pattern light and the control content for the optical member. The refractive power of the optometry may be calculated as the eye information.

  According to such a configuration, even for an eye to be examined with a disease, the refractive power of the eye to be examined can be obtained by projecting pattern light onto the fundus.

  The display control unit also superimposes and displays a reference pattern image representing an image based on pattern light projected on a predetermined reference examination eye or eye to be examined in a predetermined focus state on an image based on the pattern light (measurement pattern image). You may display on a means.

  According to such a configuration, the user can change the focus state of the image based on the return light from the fundus while referring to the reference pattern image displayed on the display unit. An appropriate in-focus position can be determined even in an unclear state. Thereby, even for an eye to be examined with a disease, the refractive power of the eye to be examined can be obtained with higher accuracy.

  The pattern light may be ring pattern light.

  According to such a configuration, the eye information to be examined can be obtained based on the ring pattern light, and thus the eye information to be examined can be obtained by a known method even for the eye to be examined with a disease.

  The operation unit is used for designating three or more positions with respect to the image based on the pattern light displayed on the display means, and the calculation unit is based on the three or more positions designated using the operation unit. Refracting power calculation for calculating the refractive power based on the specifying unit (for example, the specifying unit 103A) for specifying the approximate ellipse by performing the ellipse approximation process, and the approximate ellipse specified by the specifying unit and the control content for the optical member (For example, refractive power calculation unit 103B).

  According to such a configuration, the approximate ellipse of the image based on the pattern light is obtained by performing the ellipse approximation process on the image based on the pattern light displayed on the display unit based on three or more positions designated by the operation unit. Therefore, the eye information can be obtained by a known method.

  Further, when a position is specified using the operation unit, the specifying unit includes a new position every time a new position is specified after two or more positions are specified using the operation unit. A new approximate ellipse may be specified based on the above position, a new refractive power may be calculated based on the new approximate ellipse, and the new refractive power may be displayed on the display unit.

  According to such a configuration, it is possible to easily determine whether or not the new refractive power calculated based on the position designated by the user is appropriate.

  Moreover, it may include a capture unit (for example, the capture unit 105) that captures an image, and the calculation unit may calculate the eye information based on the image captured by the capture unit and the control content for the optical member.

  According to such a configuration, since the eye information is calculated using the captured image, it is possible to calculate the eye information with high reproducibility and high accuracy.

  The optical member control unit may control the optical member so that the image is clouded, and the capture unit may capture the image in a state where the image is clouded by the optical member.

  According to such a configuration, since the eye information is calculated using an image captured in a clouded state, the eye information can be calculated with higher accuracy.

(Modification)
The embodiment described above is merely an example for carrying out the present invention. A person who intends to implement the present invention can make arbitrary modifications, omissions, additions and the like within the scope of the present invention.

  In the above-described embodiment, an ophthalmologic apparatus capable of at least objective refraction measurement (and corneal shape measurement) and capable of subjective refraction measurement has been described. However, the ophthalmologic apparatus to which the present invention is applicable is not limited to these. For example, an apparatus having an arbitrary function that can be used in the ophthalmic field, such as an axial length measurement function, an intraocular pressure measurement function, a fundus imaging function, an anterior ocular segment imaging function, an optical coherence tomography (OCT) function, and an ultrasonic examination function Can have the functions of the present invention. The axial length measurement function is realized by an optical coherence tomometer or the like. The axial length measurement function projects light onto the eye to be examined and detects return light from the fundus while adjusting the position of the optical system in the Z direction (front-rear direction) with respect to the eye to be examined. Alternatively, the axial length of the eye may be measured. The intraocular pressure measurement function is realized by a tonometer or the like. The fundus photographing function is realized by a fundus camera, a scanning ophthalmoscope (SLO), or the like. The anterior segment imaging function is realized by a slit lamp or the like. The OCT function is realized by an optical coherence tomograph or the like. The ultrasonic inspection function is realized by an ultrasonic diagnostic apparatus or the like. In addition, the present invention can be applied to an apparatus (multifunction machine) having two or more of such functions. Therefore, the eye information to be examined according to the embodiment may include the axial length, intraocular pressure, information about the fundus, information about the anterior segment, OCT information acquired by OCT, ultrasound information acquired by ultrasound, and the like. Good.

DESCRIPTION OF SYMBOLS 1 Ophthalmology apparatus 100 Control part 101 Test | inspection control part 102 Display control part 103 Calculation part 103A Identification part 103B Refractive power calculation part 104 Memory | storage part 104A Reference | standard pattern memory | storage part 105 Capture part 110 Inspection part 111 Optical system 111A Projection system 111B Light reception system 111C Optical Member 112 Movement mechanism 130 Display unit 140 Operation unit 150 Communication unit

Claims (6)

A projection system for projecting a pattern light to the fundus of the eye, a light receiving system for detecting return light from the fundus of the pattern light projected by the projection system, based on the return light detected by the light receiving system An optical system including an optical member that changes a focus state of the image;
A display control unit for displaying the image on a display unit;
An operation unit for changing a focus state of the image;
An optical member control unit that controls the optical member based on the operation content of the operation unit;
Look including a calculation unit for output calculation as examined eye information the refractive power of the eye to be examined on the basis of a control content for the optical member and the image,
The display control unit superimposes a reference pattern image representing an image based on the pattern light projected on a predetermined reference examination eye or a predetermined focus state on the eye to be examined on the display unit. to display, ophthalmology equipment. The ophthalmic apparatus according to claim 1, wherein the pattern light is ring pattern light. The operation unit is used for designating three or more positions with respect to an image based on the pattern light displayed on the display means,
The calculation unit includes:
A specifying unit for specifying an approximate ellipse by performing an ellipse approximation process based on the three or more positions designated using the operation unit;
The ophthalmologic apparatus according to claim 2, further comprising: a refractive power calculation unit that calculates the refractive power based on the approximate ellipse specified by the specifying unit and a control content for the optical member. When the position is specified using the operation unit, each time a new position is specified after two or more positions are specified using the operation unit, the specifying unit sets the new position. A new approximate ellipse is specified based on three or more positions including the same, a new refractive power is calculated based on the new approximate ellipse, and the new refractive power is displayed on the display means. The ophthalmic apparatus according to claim 3 . Including a capture section for capturing the image;
The calculating unit according to any one of claim 1 to claim 4, characterized by calculating the subject's eye information based on the control contents captured image by the capture unit relative to the optical member Ophthalmic equipment. The optical member control unit controls the optical member so as to cloud the image,
The ophthalmologic apparatus according to claim 5, wherein the capture unit captures the image in a state where the image is clouded by the optical member.

Images