JP5562621B2 - Ophthalmic equipment - Google Patents

Description

  The present invention relates to an ophthalmologic apparatus including an eyeball wavefront aberration measuring optical system that measures the wavefront aberration of an eyeball of a subject's eye, and a corneal aberration measuring optical system that measures an aberration of the cornea of the subject's eye.

  Conventionally, an ophthalmic apparatus that simultaneously measures the wavefront aberration of the eyeball of the eye to be examined and the aberration of the cornea of the eye to be examined has been known (see Patent Document 1).

  Such an ophthalmic apparatus includes a measurement irradiation optical system that irradiates measurement light onto the fundus of a subject eye, a light reception optical system that receives a wavefront of measurement light reflected from the fundus, and a ring pattern projection optical system that projects a placido ring pattern onto the cornea And a ring pattern light receiving optical system that receives the ring pattern reflected by the cornea, and the wavefront aberration of the entire eyeball is obtained based on the light receiving signal received by the light receiving element of the light receiving optical system, and the light received by the ring pattern light receiving optical system The corneal aberration is obtained based on the light reception signal of the element.

  This ophthalmologic apparatus uses the fact that the wavefront aberration increases when the tear film is dried up, so that the wavefront aberration and corneal aberration are obtained and used effectively in clinical practice of dry eye.

  In recent years, an ophthalmologic apparatus has been proposed in which a map indicating wavefront aberration is displayed on a monitor so that the wavefront aberration can be visually perceived.

JP 2004-275697 A

  However, in such an ophthalmologic apparatus, if it is determined that it is not dry eye from wavefront aberration, the monitor only displays a map showing wavefront aberration that hardly changes over time. There was a problem that it was not possible to obtain confirmation.

  An object of the present invention is to provide an ophthalmic apparatus capable of obtaining confirmation that it is not dry eye.

According to the first aspect of the present invention, the wavefront aberration of the eyeball of the eye to be examined is obtained by irradiating the fundus of the eye to be examined with the first measurement light and receiving the wavefront of the first measurement light reflected by the fundus by the first light receiving element. An eyeball wavefront aberration measuring optical system to be measured, and irradiating the cornea of the eye to be examined with the second measuring light and receiving the second measuring light reflected by the cornea with the second light receiving element to measure the wavefront aberration of the cornea A corneal wavefront aberration measuring optical system, an eyeball wavefront aberration calculating means for calculating an eyeball wavefront aberration based on a light receiving signal of a first light receiving element of the eyeball wavefront aberration measuring optical system, and a second light receiving of the corneal wavefront aberration measuring optical system . An ophthalmologic apparatus comprising: a corneal wavefront aberration calculating unit that calculates a wavefront aberration of a cornea based on a light reception signal of an element; and a display unit that displays a map of the eyeball wavefront aberration obtained by the eyeball wavefront aberration calculating unit,
The eyeball wavefront aberration measurement optical system and the corneal wavefront aberration measurement optical system continuously measure the eyeball wavefront aberration and the corneal wavefront aberration multiple times,
Obtain the standard deviation or average value of the plurality of ocular wavefront aberrations obtained by this measurement,
When this standard deviation or average value is below a preset reference value, each map showing a plurality of corneal wavefront aberrations obtained by the measurement is displayed on the display means,
When the standard deviation or the average value is larger than a preset reference value, a map of a plurality of eye wavefront aberrations obtained by the measurement is displayed on the display means.

  According to the present invention, since the map showing the corneal aberration having a large change is displayed on the display means, confirmation that the eye is not dry eye can be obtained.

It is an optical arrangement | positioning figure which showed arrangement | positioning of the optical system of the ophthalmologic apparatus concerning this invention. It is the block diagram which showed the structure of the control system of the ophthalmologic apparatus shown in FIG. It is explanatory drawing which shows typically the placido ring pattern seen by the front from the to-be-tested eye side. It is explanatory drawing which showed the placido ring pattern image imaged on the area sensor (its light-receiving surface). It is explanatory drawing similar to FIG. 4 for demonstrating the state from which Z alignment shifted | deviated. It is explanatory drawing which showed typically the illumination light and reflected light of a fundus. It is the flowchart which showed a part of processing operation of the control calculating part. It is explanatory drawing of the monitor screen which displayed the wavefront aberration of the eye to be examined, the simulated Landolt ring, etc. It is explanatory drawing of the monitor screen which displayed the wavefront aberration etc. of the cornea.

  Hereinafter, an embodiment which is an embodiment of an ophthalmologic apparatus according to the present invention will be described with reference to the drawings.

  The ophthalmologic apparatus 10 shown in FIG. 1 illuminates (irradiates) a measurement light beam (first measurement light) to the fundus oculi Ef of the eye E and receives the wavefront of the measurement light beam reflected by the fundus oculi Ef to receive the eyeball of the eye E to be examined. An eyeball wavefront aberration measuring optical system 100 for measuring the wavefront aberration of the eye, and projecting (irradiating) ring pattern light (second measurement light) to the cornea Ec of the eye E and receiving the ring pattern light reflected by the cornea Ec The corneal wavefront aberration measuring optical system 200 that measures the aberration of the cornea Ec, the anterior segment illumination optical system 50 that illuminates the anterior segment of the eye E, the alignment observation optical system 60, and the eye E to be aligned are aligned. An XY alignment optical system 70 for detection and a fixation optical system 80 for fixing the eye E to be examined are provided.

[Ocular wavefront aberration measurement optical system]
The ocular wavefront aberration measuring optical system 100 includes a measurement illumination optical system 20 that irradiates the fundus oculi Ef of the eye E with spot light as an illuminating light beam (measurement light beam: first measurement light), and an area sensor that reflects the reflected light beam from the fundus oculi Ef. (First light receiving element) 31 and a light receiving optical system 30 that receives light.

[Measurement illumination optical system]
The measurement illumination optical system 20 includes a measurement light source 21, a condenser lens 22, a polarization beam splitter 23, a dichroic mirror 24, a dichroic mirror 25, and an objective lens 26. In the measurement illumination system 20, a polarizing beam splitter 23 and dichroic mirrors 24 and 25 are disposed between the condenser lens 22 and the objective lens 26.

  The polarization beam splitter 23 includes a dichroic mirror that reflects the P-polarized component of the illumination light beam and transmits the S-polarized component of the reflected light beam from the fundus oculi Ef, which will be described later.

  The dichroic mirror 24 is configured by a wavelength selective mirror that reflects an illumination light beam and a reflected light beam and transmits a fixation light beam described later.

  The dichroic mirror 25 is configured by a dichroic mirror that reflects an illumination light beam, a reflected light beam, and a fixation light beam and transmits an observation light beam, which will be described later.

  The measurement light source 21 is an SLD (super luminescence diode) that emits near-infrared light (first measurement light), and can be moved along the optical axis direction by the light source moving means 41. The measurement light source 21 may be a laser or LED.

[Light receiving optical system]
The light receiving optical system 30 includes an area sensor 31, a Hartmann plate 32, a lens 33, a lens 34, a reflecting mirror 35, a polarizing beam splitter 23, dichroic mirrors 24 and 25, and an objective lens 26.

  In the light receiving optical system 30, the optical system from the eye E to the polarization beam splitter 23 is the same as the optical system of the measurement illumination optical system 20.

  The reflecting mirror 35 plays a role of making the optical axis of the reflected light beam from the fundus oculi Ef parallel to the direction of the optical axis of the illumination light beam emitted from the measurement light source 21. That is, in the light receiving optical system 30, the reflected light beam from the retina (fundus) Ef of the eye E to be inspected illuminated by the measurement illumination optical system 20 is reflected by the dichroic mirror 24 and the dichroic mirror 25 through the objective lens 26, and the polarized beam. The light is transmitted through the splitter 23 and reflected by the reflecting mirror 35, thereby leading to the measurement optical axis on which the lens 33, the lens 34, and the Hartmann plate 32 are disposed.

  The lens 33 converts the reflected light beam that has passed through the lens 34 into a parallel light beam and guides it to the Hartmann plate 32.

  The Hartmann plate 32 has a plurality of microlenses such as a micro Fresnel lens disposed in a plane orthogonal to the optical axis, and thereby divides a reflected light beam (parallel reflected light beam) from the fundus oculi Ef into a plurality of divided light beams. Then, the light is condensed on the light receiving surface of the area sensor 31.

  The area sensor 31 receives a plurality of divided light beams and outputs a light reception signal S4 corresponding to the amount of light received by each divided light beam. A wavefront aberration is obtained based on the light reception signal S4 from the area sensor 31. Analysis based on the change of the wavefront aberration (the amount of movement of each bright spot on the light receiving surface of the area sensor 31 with respect to the ideal wavefront) (Zernike analysis is performed based on the tilt angle of the light beam obtained by the area sensor 31). Thus, the optical characteristics (refraction state, aberration amount, etc.) of the eye E are calculated.

  The sensor unit 36 including the Hartmann plate 32 and the area sensor 31 is movable along the optical axis direction and is moved in the optical axis direction by the sensor moving means 42.

  According to the sensor moving means 42 and the light source moving means 41, the measurement light source 21, the retina (fundus) Ef of the eye E to be examined and the area sensor 31 (its light receiving surface) are substantially conjugated according to the refractive power of the eye E to be examined. Each is driven so as to have a positional relationship. As a method for such movement, the interval between bright spots on the area sensor 31 when the eye E of the “0” diopter (hereinafter referred to as “0” D) is measured in advance is stored and actually measured. What is necessary is just to move to the position where the bright spot interval on the area sensor 31 at the time of measuring the eye E to be examined substantially coincides with the stored interval.

  In this embodiment, the measurement illumination optical system 20 and the light receiving optical system 30 are optically configured so that the movement amount of the measurement light source 21 and the movement amount of the sensor unit 36 are equal, and the measurement light source 21, the sensor unit 36, Are linked, and the light source moving means 41 and the sensor moving means 42 are configured as a single optical system moving means (not shown) driven by a single drive source (for example, a motor). Further, as will be described later, the target moving means 43 is also moved by a single optical system moving means. These optical system moving means are driven and controlled by a movement control signal S3 from the drive unit 14 (see FIG. 2).

[Cornea wavefront aberration measurement optical system]
The corneal wavefront aberration measurement optical system 200 includes an anterior ocular segment illumination optical system 50 that illuminates the anterior ocular segment, and a light receiving optical system (alignment observation optical system) 60 that receives reflected light reflected by the anterior ocular segment. Yes.

[Anterior illumination optical system]
The anterior ocular illumination optical system 50 is used for measuring the curvature of the cornea Ec of the eye E and Z alignment for detecting the working distance between the eye E and the device, and includes a placido ring pattern plate 51 and a pair of light sources ( LED) 52 and a pair of collimator lenses 53.

[Placido ring pattern board]
As shown in FIG. 3, the placido ring pattern plate 51 includes a plurality of ring patterns 54 formed concentrically so as to transmit light and surround the objective lens 26 (centering on the optical axis of the objective lens 26). .. And a pair of openings 57.

  The pair of openings 57 are provided on the ring pattern 55 on a straight line passing through the center of the ring pattern 55 (perpendicular to the optical axis of the objective lens 26). The interval between the center positions is set equal.

  A plurality of LEDs (not shown) are arranged along the ring patterns 54, 55, 56... On the back surface (objective lens 26 side) of the placido ring pattern plate 51, and the placido ring pattern plate 51 is formed by the plurality of LEDs. The cornea Ec of the eye E is illuminated with a ring-shaped light emission pattern by a light beam (second measurement light) that is illuminated and transmitted through the ring patterns 54, 55, 56,.

  The light source LED 52 is provided on the back side of the placido ring pattern plate 51 corresponding to each opening 57.

  The collimator lens 53 illuminates the opening 57 of the placido ring pattern plate 51 with the light emitted from the light source LED 52 as a parallel light, and the parallel light that has passed through the opening 57 illuminates the cornea Ec of the eye E.

  As described above, the anterior segment illumination optical system 50 illuminates the cornea Ec as a bright spot by the pair of light source LEDs 52 in addition to the ring-shaped light emission pattern. This light beam is reflected by the cornea Ec (the surface thereof), and the reflected observation light beam passes through the objective lens 26 and the dichroic mirror 25, passes through the alignment observation optical system 60 described later, and is placed on the area sensor 61 on the ring sensor 61. In addition to the projected images 54 ′, 55 ′, 56 ′, etc., a pair of bright spot images 57 ′ are formed by the pair of light source LEDs 52 (see FIG. 4). As described above, in the placido ring pattern plate 51, the pair of openings 57 are provided on the ring pattern 55, and the diameter dimension of the ring pattern 55 and the distance between the center positions of both openings 57 are set equal.

  In the anterior segment illumination optical system 50, the illumination direction with respect to the cornea Ec is inclined with respect to the optical axis direction of the objective lens 26, and is provided on the back surface of the placido ring pattern plate 51 as viewed in the optical axis direction. The emission position of the LED and the emission position of the light source LED 52 are set differently. For this reason, when viewed as an image formed on the area sensor 61 (its light receiving surface) by the anterior segment illumination optical system 50, when the Z alignment matches, the diameter dimension RL of the ring-shaped projection image 55 ' The distance DL between the center positions of the pair of bright spot images 57 'becomes equal (see FIG. 4). Further, when viewed as an image formed on the area sensor 61 (its light receiving surface) by the anterior ocular segment illumination optical system 50, the distance DL between the center positions of the pair of bright spot images 57 ′ is set regardless of the change in the Z alignment. Although it does not change, the diameter dimension RL of the ring-shaped projection image 55 ′ changes according to the change in the Z alignment. From this, on the area sensor 61 (its light receiving surface), when the Z alignment does not match, the diameter dimension RL of the ring-shaped projection image 55 ′ and the distance DL between the center positions of the pair of bright spot images 57 ′ (See FIG. 5). For this reason, the diameter DL of the ring-shaped projection image 55 ′ formed on the area sensor 61 (its light receiving surface) by the anterior segment illumination optical system 50 and the distance DL between the center positions of the pair of bright spot images 57 ′. By moving the position of the apparatus relative to the eye E so as to be equal to each other, Z alignment that keeps the distance between the eye E and the apparatus constant can be executed.

[Alignment observation optical system]
The alignment observation optical system 60 includes an area sensor 61, an imaging lens 62, a relay lens 63, a half mirror 64, a dichroic mirror 25, and an objective lens 26. In the alignment observation optical system 60, as described above, the optical system from the eye E to the dichroic mirror 25 is the same as the optical system of the measurement illumination optical system 20.

  The area sensor 61 is constituted by a CCD, for example. On the light receiving surface of the area sensor 61 (CCD), as described above, the ring-shaped projection images 54 ′, 55 ′, 56 ′ and the pair of bright spot images 57 ′ by the anterior segment illumination optical system 50, A bright spot image 71 ′ for XY alignment is formed by an XY alignment optical system 70 described later.

[XY alignment optical system]
The XY alignment optical system 70 includes an alignment light source 71, a lens 72, a reflecting mirror 73, a half mirror 64, a dichroic mirror 25, and an objective lens 26.

  The XY alignment optical system 70 converts the alignment light emitted from the alignment light source 71 into a parallel light beam by the lens 72, reflects it by the reflecting mirror 73, further reflects it by the half mirror 64, and passes through the dichroic mirror 25 and the objective lens 26. The E cornea Ec is illuminated.

  Here, the area sensor 61 is disposed so as to be substantially conjugate with a virtual image (Purkinje image) formed by the curvature of the cornea Ec, and by illuminating the cornea Ec from the XY alignment optical system 70, the cornea Ec (that The light beam reflected on the surface) (hereinafter referred to as the adjustment light beam) passes through the objective lens 26, the dichroic mirror 25, the half mirror 64, and the relay lens 63 and is focused on the area sensor 61 by the imaging lens 62. Is formed (see FIG. 4).

  In the XY alignment optical system 70, as shown in FIG. 4, when the corneal apex of the eye E coincides with the optical axis of the alignment observation optical system 60, the bright spot image 71 ′ for XY alignment is displayed as an area sensor. 61 (its light receiving surface) is set so as to be located at the center. Here, when the corneal apex of the eye E to be examined moves in a plane orthogonal to the optical axis of the alignment observation optical system 60, the area sensor 61 (its light reception) Plane). Therefore, the XY alignment is executed by moving the apparatus main body with respect to the eye E so that the bright spot image 71 ′ for XY alignment is positioned at the center on the area sensor 61 (its light receiving surface). be able to.

[Fixed optical system]
The fixation optical system 80 is an optical system that projects a fixation target (fixation chart) for fixation or cloud fog on the eye E, and includes a light source 81, a lens 82, and a fixation chart (fixation chart). Standard) 83, lens 84, lens 85, reflecting mirror 86, dichroic mirror 24, dichroic mirror 25, and objective lens 26. As described above, in the fixation optical system 80, the optical system from the eye E to the dichroic mirror 24 is common to the measurement illumination optical system 20.

  The reflecting mirror 86 emits a light beam (hereinafter referred to as a fixation light beam) emitted from the light source 81 and transmitted through the lens 82, the fixation target 83, the lens 84, and the lens 85 from the measurement light source 21 in the measurement illumination optical system 20. It has the role of matching the direction of the optical axis of the light beam and the direction of the optical axis of the reflected light beam toward the area sensor 31 in the light receiving optical system 30. The light source 81 is a light source that emits light having a wavelength in the visible region (hereinafter simply referred to as visible light), and a tungsten lamp or LED is used. The light source 81 has a variable amount of light. As this variable range, at least the brightness equivalent to that in the daytime environment from the amount of light that can irradiate the eye E to observe the fixation target image with the same brightness as that in the nighttime environment. The amount of light that can be irradiated is also included. Therefore, the fixation optical system 80 (its light source 81) functions as a visible light illuminating unit that illuminates the eye E with visible light along the optical axis of the measurement optical system.

  In this embodiment, the light source 81 has four levels of brightness ranging from the amount of light that can irradiate the same brightness as that in a nighttime environment to the amount of light that can irradiate the same brightness as in a daytime environment. Switching is possible.

  Although not shown, the fixation target 83 has a landscape or radiation pattern, and is illuminated from behind by a light beam emitted from the light source 81. In this fixation optical system 80, visible light (hereinafter referred to as fixation light flux) emitted from a light source 81 and transmitted through a fixation target 83 is transmitted through a lens 84 and a lens 85, reflected by a reflecting mirror 86, and dichroic mirrored. 24, reflected by the dichroic mirror 25, and incident on the eye E through the objective lens 26, thereby causing the fixation target 83 to be projected onto the retina (fundus) Ef and the fixation target image on the eye E to be examined. Make it visible. As a result, the line of sight of the eye E is fixed to the fixation target 83.

  The target unit 87 including the light source 81, the lens 82, and the fixation target 83 of the fixation optical system 80 can be moved along the fixation optical axis of the fixation optical system 80 by the target moving means 43. Yes. The target moving means 43 is driven so as to move the fixation optical system 80 to a position where the image of the fixation target 83 can be formed on the retina (fundus) Ef (position where the focus is in focus). In addition, in the scene where the eye E is measured, the target moving means 43 performs cloud fog that moves to a position where the focus cannot be achieved in order to eliminate the influence of the adjustment of the eye E.

  The target moving unit 43 is driven by a single optical system moving unit that drives the sensor moving unit 42 and the light source moving unit 41. That is, the light source moving unit 41, the sensor moving unit 42, and the target moving unit 43 are driven by a single drive source (for example, a motor). The target unit 87 is driven and controlled by a movement control signal S3 to the target moving means 43, that is, the optical system moving means.

[Control system]
FIG. 2 shows the configuration of the control system of the ophthalmologic apparatus 10. In FIG. 2, 11 is a control calculation unit, 12 is an input unit (operation unit), 13 is a display unit (display means: monitor), and 14 is a drive unit.

  The control calculation unit 11 receives a light reception signal S4 from the area sensor 31 of the light reception optical system 30, a light reception signal S7 from the area sensor 61 of the alignment observation optical system 60, and an operation signal from the input unit 12.

  The control calculation unit 11 includes an input information processing unit 11a that appropriately processes the received light reception signals S4 and S7, a signal processed by the input information processing unit 11a, an operation signal from the input unit 12, and the like. Processed by the drive control unit 11b for controlling the lighting of the light sources 21, 52, 71, 81 of 20, 50, 70, and 80, the control of the optical system moving means, and the drive control of the drive unit 14, and the input information processing unit 11a An analysis processing section (eyeball wavefront aberration calculating means: corneal wavefront aberration calculating means: simulation means) 11c for calculating the wavefront aberration and refractive power of the eye E based on the received light signals S4 and S7, an image display control section 11d, It has a storage unit 11e that stores various data and an image forming unit 11f that forms an image such as a wavefront aberration map.

  The analysis processing unit 11c uses the measured wavefront aberration and other measurement data to determine various optical characteristics related to the eye E, such as a point spread coefficient (PSF), an MTF (Modulation Transfer Function) indicating transfer characteristics of the eye, and the pupil. Calculate diameter, contrast sensitivity, etc. And the analysis process part 11c functions as a pupil diameter size measurement means. Further, the analysis processing unit 11c outputs signals or other signals / data corresponding to the calculation results to a drive control unit 11b that controls the optical system and the electric control system, an image display control unit 11d, and a storage unit 11e. Output as appropriate.

  The image display control unit 11d is an image of the cornea Ec of the eye E based on signals from the input information processing unit 11a (light reception signal S4 from the light reception optical system 30, light reception signal S7 from the alignment observation optical system 60, and the like). Alternatively, a signal for displaying an image showing a wavefront or the like is output to the display unit 13. Further, the image display control unit 11d outputs to the display unit 13 a measurement result, a calculation result, an analysis result, and a signal for displaying a window for an operator to input and instruct data.

  The storage unit 11e stores data relating to the eye E, data used for wavefront aberration calculation, setting data for measurement, and the like. That is, information transmitted from the input information processing unit 11a, the drive control unit 11b, and the analysis processing unit 11c is stored as appropriate, and the stored information is stored in the input information processing unit 11a, the drive control unit 11b, the analysis processing unit 11c, and the image. It is appropriately pulled out in response to a request from the display control unit 11d. In addition, the storage unit 11e stores a control program for performing measurement automatically.

  The image forming unit 11f creates a map or a graph from the wavefront aberration obtained by the analysis processing unit 11c.

  The input unit 12 is a switch, a button, a keyboard, or the like for an operator to input various input signals such as predetermined settings, instructions, and data. Here, it is assumed that a pointing device or the like for supporting buttons, icons, positions, areas, and the like displayed on the display unit 13 is included. The input unit 12 outputs an operation signal corresponding to the operation performed by itself to the control calculation unit 11. In the first embodiment, the input unit 12 includes a light amount changeover switch 12a and a measurement start switch 12b. The light amount changeover switch 12a changes the light amount of the light source 81 from a light amount that can irradiate a brightness equivalent to that in a set nighttime environment to a light amount that can irradiate a brightness equivalent to that in a daytime environment. It is for switching to four levels of brightness, and the measurement start switch 12b is for executing various measurements.

  The display unit 13 displays measurement results, calculation results, analysis results, a window for an operator to input and instruct data, an image of the eye E to be examined, and the like. The display unit 13 performs display as appropriate under the control of the control calculation unit 11.

For example, based on the light reception signal S4 from the area sensor 31 input to the control calculation unit 11, the drive unit 14 is based on the measurement light source 21 (light source moving means 41) of the measurement illumination optical system 20 and the sensor unit of the light reception optical system 30. 36 (sensor moving means 42) and an optical system moving means (not shown) for integrally moving the target unit 87 (target moving means 43) of the fixation optical system 80 in the optical axis direction are driven. The drive unit 14 drives the optical system moving unit by outputting a movement control signal S3 to the optical system moving unit.
[Operation]
Next, the operation of the ophthalmologic apparatus 10 of the above embodiment will be described.

  First, the light source 81 of the fixation optical system 80 is caused to emit light to fix the eye E, and the alignment light source 71 of the XY alignment optical system 70 is caused to emit light. The alignment light emitted from the alignment light source 71 is converted into a parallel light beam by the lens 72, reflected by the reflecting mirror 73, further reflected by the half mirror 64, and the cornea Ec of the eye E to be examined via the dichroic mirror 25 and the objective lens 26. Illuminate.

  The adjustment light beam reflected by the cornea Ec (the surface thereof) passes through the objective lens 26, the dichroic mirror 25, the half mirror 64, and the relay lens 63, and is condensed on the area sensor 61 by the imaging lens 62, and the bright spot image 71 is obtained. 'Is formed (see FIG. 4).

  The bright spot image 71 ′ is displayed on the display unit 13 as in FIG. 4, and the bright spot image 71 ′ is the center position on the area sensor 61 (its light receiving surface), that is, the mark position displayed on the display unit 13 (see FIG. XY alignment is performed by moving the apparatus main body with respect to the eye E to be positioned so that it is located at a position not shown.

  Then, the pair of light sources 52 of the anterior segment illumination optical system 50 and a plurality of LEDs (not shown) are caused to emit light. The placido ring pattern plate 51 is illuminated by the light emission of the plurality of LEDs, and a ring-shaped light emission pattern is projected onto the cornea Ec of the eye E to be examined.

  The observation light beam reflected by the cornea Ec passes through the objective lens 26 and the dichroic mirror 25, passes through the alignment observation optical system 60, and is projected onto the area sensor 61 in the form of ring-shaped projection images 54 ', 55', 56 '. In addition to the pair of light source LEDs 52, a pair of bright spot images 57 'are formed. Then, the bright spot image 57 ′ and the ring-shaped projection images 54 ′, 55 ′, 56 ′,... Are displayed on the display unit 13 as in FIG.

  The examiner sets the apparatus main body for the eye E so that the diameter dimension RL of the ring-shaped projection image 55 ′ displayed on the display unit 13 is equal to the distance DL between the center positions of the pair of bright spot images 57 ′. The Z alignment is performed by moving the position back and forth.

  Next, a case where wavefront aberration is measured will be described.

  As shown in FIG. 1, the light source 81 of the fixation optical system 80 is turned on with a predetermined brightness, and the fixation target image is observed by the eye E. In this state, the corneal apex of the eye E to be examined and the measurement optical axis of the apparatus main body (the optical axis of the objective lens 26) are made to coincide with each other by XY alignment, and the distance from the corneal apex of the eye E to the apparatus main body is made by Z alignment. Keep constant. Thereafter, the measurement light source 21 of the measurement illumination optical system 20 is moved to the reference position by the optical system moving means, and the measurement light source 21 is turned on. At this time, the sensor unit 36 of the light receiving optical system 30 and the target unit 87 of the fixation optical system 80 are also moved integrally by the optical system moving means, and thus set as the reference position.

  At this reference position, the refractive state of the eye E is temporarily measured, and the measurement light source 21 and the light receiving optical system 30 of the measurement illumination optical system 20 are positioned at positions where the refractive power of the eye E is canceled based on the result of the temporary measurement. Are moved, and the refractive state of the eye E is measured again at that position. As a result of this re-measurement, when the sensor unit 36 of the light receiving optical system 30 is in a position that substantially cancels the refractive power of the eye E, the target unit 87 of the fixation optical system 80 is moved to the plus side. Cloud the fixation image. In this state, the refractive state and wavefront aberration of the eye E are measured.

  In this measurement, in the measurement illumination optical system 20, the light beam emitted from the measurement light source 21 and transmitted through the condenser lens 22 is reflected by the polarization beam splitter 23, the dichroic mirror 24, and the dichroic mirror 25 and onto the optical axis of the objective lens 26. And the fundus oculi Ef of the eye E is illuminated. If this is an illumination light beam Li, as shown in FIG. 6, it enters the eye E through the objective lens 26 as a light beam having an extremely small diameter, and illuminates a minute region (spot light) of the fundus oculi Ef. Then, at the fundus oculi Ef, the illumination light beam Li is reflected, and the light beam that has passed through the pupil Ep (inward of the iris Ei) of the reflected light beam is directed toward the objective lens 26.

  When this is a reflected light beam Lr, the reflected light beam Lr is guided to the light receiving optical system 30 through the objective lens 26 as shown in FIG. That is, the reflected light beam Lr is reflected by the light receiving optical system 30 through the objective lens 26, the dichroic mirror 24 and the dichroic mirror 25, and transmitted through the polarization beam splitter 23 and reflected by the reflecting mirror 35. The light travels toward the Hartmann plate 32, passes through the Hartmann plate 32, is divided into a plurality of divided light beams, and is condensed on the light receiving surface of the area sensor 31.

  The area sensor 31 receives each divided light beam and photoelectrically converts it, and outputs a received light signal S4 corresponding to the received light amount of each divided light beam to the control calculation unit 11. The control calculation unit 11 can obtain wavefront aberration (eyeball wavefront aberration) from the data acquired by the light reception signal S4 in the analysis processing unit 11c, and changes in the wavefront aberration (for each bright spot on the light receiving surface of the area sensor 31). By analyzing based on the movement amount with respect to the ideal wavefront, it is possible to calculate the optical characteristics (the refraction state, the aberration amount, etc.) of the eye E.

  Here, as shown in FIG. 6, the calculated refraction state is an actual optical state in a region (a hatched region (reference symbol Ar) in FIG. 6) where the reflected light beam Lr is transmitted through the eye E. All elements are included.

  The measurement of the wavefront aberration is performed 10 times per second, the standard deviation of the measured wavefront aberration is obtained, and the standard deviation is compared with a preset reference value as shown in FIG. 7 (step 1). When the standard deviation is larger than the reference value, that is, when it is determined that the eye is dry eye, the process proceeds to step 2.

  For the wavefront aberration of each measurement, one RMS (root mean square) value is calculated for the entire eyeball, and this value is used as the wavefront aberration.

  In step 2, the image forming unit 11f creates maps M1 to M10 of the measured wavefront aberrations, and displays the maps M1 to M10 on the display unit 13 as shown in FIG. Further, the analysis processing unit 11c simulates how the Landolt ring looks to the subject from each wavefront aberration, and displays the simulated Landolt rings K1 to K2 on the display unit 13. The values of wavefront aberration in the maps M1 to M10 are H1 <H2 <H3 <H4. Also, the Landolt ring becomes blurred as the wavefront aberration increases.

  The display unit 13 displays a graph G1 indicating the wavefront aberration (RMS value) with respect to the number of measurements. This graph G1 is also created by the image forming unit (graph creating means) 11f.

  Further, based on the ring-shaped projection images 54 ′, 55 ′, 56 ′,... Formed on the area sensor 61, the analysis processing unit 11c of the calculation control unit 11 obtains the wavefront aberration of the cornea Ec for each measurement. The image forming unit 11f creates a graph G2 indicating the wavefront aberration of the cornea Ec with respect to the number of measurements, and this graph G2 is displayed on the display unit 13 as shown in FIG.

  If NO is determined in step 1, that is, if the standard deviation is equal to or smaller than the reference value, that is, if it is determined that the eye is not dry eye, the process proceeds to step 3.

  In step 3, the image forming unit 11f creates a wavefront aberration map for each measurement based on the wavefront aberration of the cornea Ec obtained by the analysis processing unit 11c of the control calculation unit 11, and the maps M1c to M10c are shown in FIG. Is displayed on the display unit 13 as shown in FIG.

  As described above, when it is determined that the eye is not dry eye, the cornea wavefront aberration maps M1c to M10c whose wavefront aberrations change with time are displayed on the display unit 13, and thus the maps M1c to M10c are displayed. If the change with time of the wavefront aberration is small, it can be recognized more clearly that it is not dry eye. That is, confirmation that it is not dry eye can be obtained. Note that the cornea wavefront aberrations are exaggerated in the maps M5c to M10c shown in FIG.

  In the above embodiment, the standard deviation and the reference value are compared in Step 1, but the average value of the wavefront aberration may be compared with the reference value for determination.

  The present invention is not limited to the above-described embodiments, and design changes and additions are permitted without departing from the spirit of the invention according to the claims.

11c Analysis processing unit (eyeball wavefront aberration calculating means: corneal wavefront aberration calculating means)
13 Display section (display means)
31 Area sensor (first light receiving element)
61 Area sensor (second light receiving element)
100 Ocular wavefront aberration measurement optical system 200 Corneal wavefront aberration measurement optical system

Claims (3)

Optical wavefront aberration measurement optics for irradiating the fundus of the subject's eye with the first measurement light and measuring the wavefront aberration of the eyeball of the subject's eye by receiving the wavefront of the first measurement light reflected by the fundus with the first light receiving element. And a corneal wavefront aberration measuring optical system that irradiates the cornea of the eye to be examined with the second measurement light and receives the second measurement light reflected by the cornea with a second light receiving element and measures the wavefront aberration of the cornea An eyeball wavefront aberration calculating means for calculating an eyeball wavefront aberration based on a light receiving signal of the first light receiving element of the eyeball wavefront aberration measuring optical system, and a light receiving signal of the second light receiving element of the corneal wavefront aberration measuring optical system . An ophthalmologic apparatus comprising: a corneal wavefront aberration calculating unit that calculates a wavefront aberration of the cornea; and a display unit that displays a map of the eyeball wavefront aberration obtained by the eyeball wavefront aberration calculating unit,
The eyeball wavefront aberration measurement optical system and the corneal wavefront aberration measurement optical system continuously measure the eyeball wavefront aberration and the corneal wavefront aberration multiple times,
Obtain the standard deviation or average value of the plurality of ocular wavefront aberrations obtained by this measurement,
When this standard deviation or average value is below a preset reference value, each map showing a plurality of corneal wavefront aberrations obtained by the measurement is displayed on the display means,
When the standard deviation or the average value is larger than a preset reference value, the ophthalmic apparatus displays each map of a plurality of ocular wavefront aberrations obtained by the measurement on the display means.   The ophthalmologic apparatus according to claim 1, wherein the appearance of the subject's Landolt ring is simulated for each eyeball wavefront aberration, and the simulated Landolt ring is displayed on the display unit.   3. The ophthalmologic apparatus according to claim 1, wherein changes in a plurality of ocular wavefront aberrations and corneal wavefront aberrations obtained by the measurement are displayed as graphs on the display unit. 4.