JP2019208856A - Ophthalmologic measurement apparatus - Google Patents

Abstract

To provide an ophthalmologic measurement apparatus which has a plurality of measurement units vertically and horizontally arranged in parallel to make it possible to excellently obtain distribution information of a cornea shape over a wide range on a cornea.SOLUTION: An ophthalmologic measurement apparatus 1 measures a plurality of eye properties of a subject eye E. The apparatus 1 includes: a first measurement unit 21 for measuring a first eye property different from a cornea shape through a first measurement axis L1; a second measurement unit 22 for measuring a second eye property L2 different from the cornea shape and the first eye property through a second measurement axis that is arranged so as to be parallel to the first measurement axis in vertical and horizontal directions; and a Placido unit 20 that projects a pattern index for measuring the cornea shape onto the cornea of the subject eye E from its front side facing the subject eye E. The Placido unit 20 has, on the front side, windows formed to allow the first measurement axis L1 and the second measurement axis L2 to respectively pass therethrough.SELECTED DRAWING: Figure 1

Description

  The present disclosure relates to an ophthalmologic measurement apparatus that measures a plurality of types of eye characteristics.

  Conventionally, an ophthalmologic measurement apparatus that measures a plurality of types of eye characteristics is known.

As this type of device, for example, a device in which an eye refractive power measurement unit and an intraocular pressure measurement unit are arranged in parallel in the vertical and horizontal directions is known. Patent Document 1 further discloses a device provided with a keratometer. In Patent Document 1, an index projection unit for kerato measurement is formed on the front surface of one unit, whereby a circumferential region with a diameter of 3.3 mm and a circumferential region with a diameter of 2.4 mm on the cornea. And the corneal shape can be measured.
JP-A-2006-214466

  In recent years, information on the asphericity of the cornea has become more important for prescriptions such as IOL prescriptions, contact lens prescriptions, and orthokeratology corrective lenses. For example, in the IOL prescription, it is considered that distribution information of a shape within a diameter of at least 6 mm on the cornea is necessary, and in a contact lens prescription and a correction lens prescription in orthokeratology, a wider range of distribution information is required. It is considered.

  However, in the apparatus described in Patent Document 1, the measurement range on the cornea is insufficient, and further, shape distribution information cannot be obtained.

  The present disclosure has been made in view of the problems of the prior art, and in a device in which a plurality of measurement units are arranged in parallel in the vertical and horizontal directions, the distribution information of the corneal shape in a wide range on the cornea is obtained satisfactorily. This is a technical issue.

  An ophthalmologic measurement apparatus according to a first aspect of the present disclosure is an ophthalmologic measurement apparatus that measures a plurality of eye characteristics of an eye to be examined, and measures a first eye characteristic different from a corneal shape via a first measurement axis. A second measurement characteristic different from any of the first measurement unit and the corneal shape and the first characteristic is measured via a second measurement axis arranged in parallel in the vertical and horizontal directions of the first measurement axis. An index projector for projecting a pattern index for measuring a corneal shape onto a cornea of the eye to be examined from a front surface facing the eye to be examined, the first measuring axis and the A window for passing the second measurement axis includes an index projector formed corresponding to each measurement axis.

  According to the present disclosure, in an apparatus in which a plurality of measurement units are arranged in parallel in the vertical and horizontal directions, distribution information on the corneal shape in a wide range on the cornea can be obtained favorably.

It is the figure which looked at the ophthalmologic measurement apparatus of the Example from the side, Comprising: The apparatus position in the corneal shape measurement mode and the eye refractive power measurement mode is shown. It is the figure which looked at the ophthalmologic measurement apparatus of the Example from the side, Comprising: The apparatus position when it is an intraocular pressure measurement mode is shown. In the corneal shape measurement mode of an Example, it is the front view which looked at the platide board which concerns on an Example from the eye to be examined. In the intraocular pressure measurement mode of an Example, it is the front view which looked at the platide board which concerns on an Example from the to-be-tested eye side. It is the block diagram which showed the electrical structure in the ophthalmic measurement apparatus of an Example. It is a partial front view of the platide unit which concerns on a modification. It is the figure which looked at the platide unit which concerns on a modification in the cornea shape measurement mode from the side. It is the figure which looked at the platide unit which concerns on a modification from the side in the intraocular pressure measurement mode.

"Overview"
Hereinafter, embodiments of the present disclosure will be described with reference to the drawings. The ophthalmologic measurement apparatus according to each embodiment measures a corneal shape and a plurality of other eye characteristics. For convenience, in the following description, the ophthalmic measurement apparatus is referred to as “this apparatus”.

  The apparatus includes at least an index projector and one or more measurement units (see FIGS. 1 to 4). Preferably, the apparatus may have two or more measurement units. In the present embodiment, one measurement unit is used for measuring at least one eye characteristic. The eye characteristic may be measured optically or by a non-optical technique. When a plurality of measurement units are provided, each measurement unit may measure different eye characteristics.

  In the following description, the portion of the apparatus that measures the eye characteristics facing the eye to be examined may be referred to as a measurement unit. The measurement unit includes an index projector and each measurement unit. In each measurement unit, the tip portion on the eye side to be examined is referred to as a tip portion in the following description.

  Hereinafter, unless otherwise specified, this apparatus will be described as having two measurement units, a first measurement unit and a second measurement unit. Each of the first measurement unit and the second measurement unit is provided with an optical system for measuring an eye characteristic different from the corneal shape. However, at least one of the first measurement unit and the second measurement unit may include a part of an optical system that measures the corneal shape.

  Moreover, this apparatus may further have a control part (refer FIG. 5). The control unit is a kind of processor and controls at least the measurement operation in this apparatus. Furthermore, various devices such as various actuators and monitors provided in this apparatus may be controlled.

  Each of the first measurement unit and the second measurement unit has a measurement axis (see FIGS. 1 to 4). The measurement axis is an axis where the eye to be examined is to be arranged at the time of measurement. The measurement axis may be an axis substantially perpendicular to the measurement location (or the imaging surface). For example, the measurement axis may be an axis along the working distance direction of the apparatus. The measurement axis of the first measurement unit (referred to as the first measurement axis) and the measurement axis of the second measurement unit (referred to as the second measurement axis) are arranged in parallel in the vertical and horizontal directions. For example, the first measurement axis and the second measurement axis may be arranged substantially in parallel.

  In this embodiment, the eye characteristic measured by each measurement unit may be any of, for example, eye refractive power, intraocular pressure, corneal thickness, axial length, and others.

  The index projector is used to measure the corneal shape. The front face (front face) of the index projector is arranged to face the eye to be examined. The index projector projects a pattern index suitable for measuring the corneal shape onto the cornea of the eye to be examined from the front of the index projector.

  At this time, the pattern index may be formed by diverging light. In that case, various devices that emit light may be used as the index projector.

  In the embodiment, the index projector may be formed in a plate shape. The plate-shaped index projector may be, for example, a disk type. In the case of a disk type, the surface of the index projector is formed in a planar shape or a bowl shape. A cone type is also known as an index projector, but the cone type is disadvantageous because it can be made smaller, but has a short working distance and a narrow tolerance range for alignment in the working distance direction. The indicator projector that is disk-shaped and emits surface light may include, for example, a platide plate. In addition, a liquid crystal panel, an organic EL panel, or the like can be used instead of the platide plate.

  The pattern index projected from the index projector may be formed by, for example, a multiple ring pattern formed concentrically (see FIGS. 3 and 4). Each ring index may be formed as a continuous ring without breaks. Further, since there are at least three measurement points on the same circumference and curvature information on the circumference can be obtained, a point index having three or more measurement points or an intermittent ring index may be used. . However, the present invention is not limited to this, and the index pattern used for measurement may be a lattice pattern, a spider web pattern, or a dot matrix pattern. It may be a pattern other than that.

  The index projector may be capable of selectively projecting any part of the pattern index. Further, the pattern index does not need to be uniquely defined in the index projector, and for example, a plurality of different pattern indices may be projected.

  The apparatus may further include an anterior ocular segment imaging optical system. The anterior segment imaging optical system captures a front image of the anterior segment. In the present embodiment, information related to the shape of the cornea is acquired based on a front image that is captured in a state where a pattern index is projected. More specifically, information on the shape of the cornea is obtained by analyzing an image of a pattern index included in the front image. The anterior ocular segment imaging optical system may be accommodated in one of the first measurement unit and the second measurement unit, for example. In this case, it is desirable that one of the first measurement axis and the second measurement axis that corresponds to the measurement unit that houses the anterior segment imaging optical system is coaxial with the optical axis of the anterior segment imaging optical system. An anterior ocular segment front image captured by the anterior ocular segment imaging optical system may be used as an observation image in alignment between the measurement unit and the eye to be examined. Note that a corneal bright spot or the like may be further used for alignment. The corneal bright spot may be formed by index light projected from the alignment optical system, for example.

  For example, as shown in FIGS. 3 and 4, a window portion may be formed in front of the index projector. The window is formed corresponding to each of the first measurement axis and the second measurement axis. Each window is passed through a measurement axis corresponding to each window. The window portion forms a path through which the front end portion of each unit itself or the optical axis passes. The window part through which the tip part passes may be formed by at least one of an opening and a notch, for example. The window that allows the optical axis to pass therethrough may be formed of a translucent member in addition to the opening and the notch.

  The distal end portion of each measurement unit may or may be able to protrude from the surface of the index projector through the window portion toward the eye to be examined (see FIGS. 1 and 2). At this time, the protruding amount of the tip may be changeable. For this purpose, for example, a moving unit that moves (displaces) the front end of at least one of the measurement units in the front-rear direction with respect to the surface of the index projector may be provided. Although details will be described later, when a certain measurement unit is not used, the distal end portion of the measurement unit is retracted, so that the distal end portion is unlikely to interfere with measurement of other eye characteristics or movement of the apparatus.

  Hereinafter, the window portion corresponding to the first measurement axis is referred to as a first window portion, and the window portion corresponding to the second measurement axis is referred to as a second window portion. Either one of the first window portion and the second window portion may be formed in a region corresponding to the corneal apex in the index projector (for example, the central portion of the index projector). As described above, since the gradient in the vicinity of the corneal apex can be considered to be known (substantially zero), even if the window portion is arranged, there is little influence in obtaining the shape information of the cornea.

  Eye measurement by each measurement unit is performed via the measurement axis that has passed through the index projector. It should be noted that the measurement axis used for corneal shape measurement may be coaxial with either the first measurement axis or the second measurement axis, or may be a third measurement axis different from both.

  The apparatus may further include a drive unit. The drive unit adjusts the positional relationship between the measurement unit and the eye to be examined in the vertical and horizontal directions. Thereby, the eye to be examined can be selectively arranged on each measurement axis. The drive unit is used to change the eye characteristics measured in the measurement unit. The drive unit may also be used for alignment adjustment with respect to the eye to be examined.

  Here, in the present embodiment, it is also conceivable to arrange each measurement unit so that at least one of the first measurement axis and the second measurement axis is arranged outside the index projector. In such an arrangement, the size of the index projector is likely to be limited. On the other hand, in the present embodiment, both the first measurement axis and the second measurement axis pass through the index projector. This makes it easy to increase the size of the index projector. As a result, a wider range of corneal shapes can be measured satisfactorily. Moreover, it becomes easy to reduce the size of the drive unit and the like. That is, it is advantageous for space saving of the apparatus.

<Interpolation of pattern index>
However, it is conceivable that the pattern index is missing due to the two windows formed on the index projector. A region lacking a pattern index is disadvantageous in obtaining corneal shape information. In the present embodiment, either one of the first measurement axis and the second measurement axis is always separated from the area corresponding to the corneal apex (for example, the center of the index projector) in the index projector. It will pass through the position. Such lack of pattern indices due to the measurement axis can be particularly disadvantageous. Therefore, in this embodiment, the lack of pattern index may be interpolated.

  In the following, means for interpolation will be exemplified.

<Interpolation index projector>
For example, the apparatus may include an interpolation index projector. The interpolation index projector projects a portion of the pattern index that is missing by the window portion onto the cornea. The interpolation index projector may be, for example, a partial platide. Moreover, a liquid crystal panel, an organic EL panel, etc. may be sufficient. Like the index projector, the interpolation index projector is preferably a device that forms part of the pattern index by planar light emission.

  The interpolation index projector may be a member that is inserted into and removed from the window (see FIGS. 3 and 4). In this case, the control unit of the present apparatus may execute insertion / removal control of the interpolation index projector with respect to the window unit. The insertion / removal control may be linked with the selection of the measurement mode. For example, the control unit may select a measurement mode between a corneal shape measurement mode for measuring the corneal shape and a second measurement mode for measuring the first eye characteristic or the second eye characteristic. At this time, the control unit may insert the interpolation index projector into the window part in the corneal shape measurement mode and retract from the window part in the second measurement mode.

  The interpolation index projector has a plane that intersects the surface of the index projector near the window, and projects a portion of the pattern index that is missing by the window from the plane onto the cornea. (See FIGS. 6A, 6B, and 6C). The surface of the interpolation index projector is formed so as not to intersect the measurement axes of the first measurement unit and the second measurement unit. For example, it may be formed parallel to the measurement axis. Furthermore, it is desirable that the surface of the interpolation index projector is formed in a range that does not hinder the projection of the pattern index from the index projector.

  Further, the interpolation index projector may be provided in either the first measurement unit or the second measurement unit. For example, an interpolation index projector may be provided at the tip of each unit exposed from the window. Further, an interpolation index projector may be provided as a part of the optical system arranged inside the housing of each unit.

<Switching the area where the pattern index is projected on the cornea>
In addition, in order to interpolate a part of the pattern index that is missing due to the window portion, the pattern index may be projected from the index projector by switching the area where the pattern index is projected on the cornea. For example, the direction of the line of sight with respect to the index projector may be switched between the first direction and the second direction, the pattern index is projected in each direction, and the corneal shape measurement may be performed. The cornea region corresponding to a missing pattern index in one direction is projected in the other direction, so the measurement result corresponding to the missing pattern index in one direction is interpolated from the measurement result in the other direction. it can. If the first direction and the second direction are known, interpolation is easier.

<Small window>
The index projector projects a plurality of indices onto the cornea from each of the plurality of index projection locations to form a pattern index. For example, in the platide plate, the ring-shaped light transmitting portions and the light shielding portions are alternately formed concentrically on the front surface of the plate, but the ring-shaped light transmitting portions correspond to the index projection locations.

  The window corresponding to each of the first measurement axis and the second measurement axis may be formed in a gap between a certain index projection location and an index projection location adjacent to that location. For example, in the case of the above-described platide plate, the window portion may be formed in a size that can be accommodated in the light shielding portion. In this case, chipping of the pattern index is suppressed. Moreover, when the size of the window part required in one measurement unit is larger than one gap, the window part may be divided into a plurality of gaps. For example, in the case of an intraocular pressure measurement unit, a corneal applanation window and an applanation detection window may be formed in separate gaps.

<Switching the measurement area on the cornea>
In this apparatus, the measurement region on the cornea may be changed according to the pattern index projected from the index projector by changing the pattern index projected from the index projector.

<Switching between topo mode and kerato mode>
For example, the measurement mode in the corneal shape measurement may be selected by the control unit between the kerato mode and the topo mode. The control unit may select the first topo mode and the second topo mode according to an operation input by the examiner. In the kerato mode, the corneal shape in a single circumferential region on the cornea may be measured. The index projector projects the index onto at least three points in the circumferential area. Of course, a ring-shaped index may be projected. As an analysis result (measurement result) of the index image detected from the front image of the anterior segment in that state, for example, the radius of curvature of the cornea, the refraction value, the main meridian of the cornea, and the amount of corneal astigmatism in the circumferential region of a predetermined radius Etc. are acquired. For example, one or both of a circumferential region having a diameter of 3.3 mm and a circumferential region having a diameter of 2.4 mm may be measured. In this case, the control unit projects the index from the index projector onto one or both of the two circumferential regions.

  In topo mode, corneal topography is measured. For example, the measurement region may be a region on the cornea having a diameter of at least 6 mm. In this case, for example, three or more indices (of course, ring indices may be used) are projected on at least four or more circumferential areas having different diameters from an area within a diameter of 6 mm. As an analysis result of the index image detected from the front image of the anterior segment in that state, for example, distribution information of the corneal shape in the measurement region is obtained. As the distribution information, any one of elevation, curvature, and corneal refractive power may be acquired.

  The kerato mode is a mode more suitable for screening for abnormal corneal shape. For example, since the measurement region is limited as compared with the topo mode, the analysis result can be obtained in a shorter time. Moreover, when the pattern index is visible light, the subject feels less glare by projecting the pattern index, and the burden is low. On the other hand, in the topo mode, detailed shape information of the cornea is obtained, so that it has high utility value in situations such as corneal shape abnormality diagnosis, IOL prescription, refractive correction, and the like.

  Therefore, the examiner can selectively use the two measurement modes of the topo mode and the kerato mode according to the purpose of use.

  In addition, the apparatus may be capable of performing continuous measurement in which measurement in the kerato mode and measurement in the topo mode are continuously performed under a predetermined condition. In continuous measurement, first, measurement in the kerato mode is performed. Next, whether or not topo measurement should be performed is determined based on the measurement result of kerato measurement. For example, in the determination process, a measurement result in the kerato mode (for example, a reliability coefficient, a radius of curvature, etc.) is compared with a threshold value. The threshold may be, for example, a threshold related to corneal shape abnormality. For example, a reliability coefficient indicating a deviation (displacement in each meridian direction) between a recent ellipse with respect to the ring index image detected from the front image of the anterior eye part and the ring index image is obtained, and the reliability coefficient is determined in advance. The determination may be made by comparing with a threshold value. If the value of the reliability coefficient increases as the deviation increases, measurement in the topo mode may be automatically performed when the reliability coefficient exceeds a predetermined threshold. In this case, when the reliability coefficient is equal to or less than a predetermined threshold, the measurement in the topo mode is not executed. When continuous measurement is performed, both the measurement result in the kerato mode and the measurement result in the topo mode may be displayed on the monitor simultaneously or selectively. Only one of them may be output. In the continuous measurement as described above, the measurement in the topo mode is automatically performed as necessary on the premise of the measurement that is quick in the kerato mode and low in burden on the subject, so that the corneal examination can be performed efficiently. it can.

  Further, when the radius of curvature is compared with a threshold value, about 7.8 mm is known as an average value of the radius of curvature, and a value lower than this value may be appropriately set as the threshold value. It is considered that the radius of curvature varies depending on the age of the subject. Therefore, for example, the control unit may acquire age information in advance based on an input operation or the like of the examiner, and the comparison with the measured value may be performed using a threshold value corresponding to age. In this case, when the radius of curvature is less than the threshold value, the measurement in the topo mode is automatically executed, and when the radius of curvature is equal to or greater than the threshold value, the measurement in the topo mode may not be executed.

<Switching between the first topo mode and the second topo mode>
For example, the control unit may select a measurement mode in corneal shape measurement between the first topo mode and the second topo mode. The control unit may select the first topo mode and the second topo mode according to an operation input by the examiner.

  The measurement area is different between the first topo mode and the second topo mode. In the present embodiment, in the second topo mode, an area in the circumference having a larger diameter than the first topo mode is set as a measurement area. For example, the measurement area of the first topo mode is an area within a diameter of 6 mm suitable for IOL prescription, for example, and the measurement area of the second topo mode is an area within a diameter of 10 mm suitable for orthokeratology, contact lens prescription, etc. There may be. The measurement area of the second topo mode includes the measurement area of the first topo mode, but in both modes, the first topo mode is more in terms of analysis time and burden on the subject when the pattern index is visible light. Since it is advantageous, it is preferable that the examiner properly use the two.

  In the case where the window is formed at a position away from the center of the index projector, at least one of the kerato mode and the first topo mode is on the inside (center of the center) of the window in the index projector. The pattern index may be projected from the side), and at least one of the topo mode and the second topo mode may be projected from both the inside and the outside of the window.

  When the pattern index is projected from both the inside and the outside of the window, the control unit may interpolate the lack of the pattern index by the window by the various methods described above. .

<Switching to intraocular pressure measurement mode>
Any one of the measurement units included in the apparatus may be an intraocular pressure measurement unit that measures intraocular pressure as an eye characteristic. In this case, the index projector and the tip of the intraocular pressure measurement unit face the eye to be examined in the same direction. Then, the tip portion is located closer to the center of the index projector than the outermost pattern area (for example, the pattern area indicated by reference numeral 205 in FIG. 3) among the pattern areas for forming the pattern index in the index projector. It may be arranged. In the above, by forming the window on the index projector, the tip is disposed closer to the center of the index projector than the outermost pattern region. However, in order to realize such an arrangement, the window portion does not necessarily have to be formed. For example, when the index projector has a shape extending in one direction, the tip portion may be disposed in the direction intersecting with the one direction and outside the index projector.

  Further, the control unit can switch the measurement mode of the apparatus between a corneal shape measurement mode and an intraocular pressure measurement mode. In the intraocular pressure measurement mode, the intraocular pressure is measured by the intraocular pressure measurement unit, and in the corneal shape measurement mode, the corneal shape is measured based on the pattern index from the index projector.

  The intraocular pressure measurement unit may include an applanation unit and an applanation detection unit. The applanation portion applanates the cornea of the eye to be examined in one direction. The applanation detection unit detects an applanation signal accompanying the applanation operation of the applanation unit. Intraocular pressure is obtained based on the applanation signal.

  The method of measuring intraocular pressure by the intraocular pressure measurement unit may be a non-contact type or a contact type. The non-contact type may be a method in which fluid (for example, compressed air) is sprayed on the cornea to detect deformation of the cornea. Further, a method of irradiating ultrasonic waves in a non-contact manner instead of a fluid may be used.

  Intraocular pressure measurement is easier to shorten the working distance, which is the distance between the device and the eye to be examined, than the corneal shape measurement using the pattern index from the index projector, and the tip of the tonometry part is closer to the cornea It is easy to measure. For this reason, at the time of intraocular pressure measurement, it is considered that the tip of the intraocular pressure measurement unit needs to protrude from the surface of the index projector. However, when the pattern index is projected from the index projector onto the cornea as it is, a part of the pattern index may be blocked by the distal end portion of the intraocular pressure measurement unit.

  Therefore, for example, the present apparatus may include a moving unit that moves (displaces) the distal end portion of the intraocular pressure measurement unit in the front-rear direction with respect to the surface of the index projector. For example, the moving unit may move the entire intraocular pressure measurement unit in the front-rear direction with respect to the index projector. Moreover, when it has another measurement unit other than an intraocular pressure measurement unit, the front-end | tip part of an intraocular pressure measurement unit may be movable to the front-back direction also with respect to another measurement unit by a moving part. In this case, the index projector and the other measurement unit may be fixedly arranged. Of course, other measurement units (more specifically, at least the tip portion) may be movable in the front-rear direction with respect to the surface of the index projector.

  The control unit controls the moving unit according to the measurement mode so that the tip of the intraocular pressure measurement unit is arranged at the first position on the eye side with respect to the surface of the index projector in the intraocular pressure measurement mode. Also good. In the corneal shape measurement mode, the distal end portion of the intraocular pressure measurement unit may be disposed at the second position that is retracted from the first position. Preferably, in the corneal shape measurement mode, the tip of the intraocular pressure measurement unit may be retracted from the surface of the index projector. At the time of corneal shape measurement, the distal end portion of the intraocular pressure measurement unit is retracted, so that the distal end portion can be prevented from interfering with the corneal shape measurement.

  In addition, it is conceivable that the cornea is applanated without contact in the measurement axis direction and the applanation is detected optically by the applanation detection unit. Hereinafter, such an applanation detection unit is referred to as an applanation detection optical system. The applanation detection optical system preferably projects an index light beam along the measurement axis, and obtains an applanation signal based on corneal reflected light from the index light beam.

  In addition, as an applanation detection optical system, a method of projecting an index light beam from an oblique direction with respect to a measurement axis is known, but a method of projecting an index light beam along the measurement axis as described above is more suitable. This is advantageous in that the alignment allowable range in the working distance direction can be secured longer. In addition, in the method of projecting the index beam from an oblique direction, a space for projecting and receiving the index beam is required, so that the window portion formed in the index projector is likely to be enlarged. On the other hand, in the method of projecting and receiving the index beam along the measurement axis, the area required for the window portion can be easily suppressed.

  In addition to intraocular pressure, the device may be capable of measuring corneal thickness. The measured corneal thickness may be used to correct the intraocular pressure measurement value. An optical system (corneal thickness measurement optical system) used for corneal thickness measurement may be provided in the measurement unit. The corneal thickness measurement optical system projects measurement light to the cornea obliquely. Further, the cornea measurement optical system includes a light receiving element that receives reflected light of measurement light from the front and rear surfaces of the cornea. The corneal thickness can be obtained based on the signal from the light receiving element. Such an optical system for measuring the corneal thickness may also be used as an optical system for detecting the deformation of the cornea when the intraocular pressure measurement unit measures the intraocular pressure by deforming the cornea without contact. In this case, the corneal thickness measurement optical system may use slit light as measurement light and capture a cross-sectional image of the cornea as a slit image.

  This apparatus may have an eye refractive power measurement unit in addition to the intraocular pressure measurement unit. In this case, the control unit can further switch to the eye refractive power measurement mode as the measurement mode of the apparatus. The eye refractive power measurement unit has an eye refractive power measurement optical system. Various configurations are known as the eye refractive power measurement optical system, and any of them can be applied as appropriate.

"Example"
Hereinafter, an ophthalmologic measurement apparatus 1 (hereinafter simply referred to as “apparatus 1”) will be described as an embodiment of the present disclosure.

  First, with reference to FIGS. 1-5, the schematic structure of the apparatus 1 is shown. 1 shows a state at the time of measuring eye refractive power and corneal shape, and FIG. 2 shows a state at the time of measuring intraocular pressure.

  As shown in FIGS. 1 and 2, the apparatus 1 has at least a measurement unit 2. In addition, in the present embodiment, the apparatus 1 includes a base 5, a face support unit 6, and a moving base 7.

  A face support unit 6 is attached to the base 5. The face support unit 6 includes a chin rest and a forehead rest. By supporting the subject's face with these members, the position of the eye E is fixed with respect to the apparatus.

  In the present embodiment, the moving table 7 is provided with a moving mechanism (not shown) for moving in the XZ direction on the base 5. The moving mechanism may be a mechanical sliding mechanism, for example.

  In the present embodiment, the moving table 7 is provided with an XYZ driving unit 7a. The XYZ driving unit 7a moves the measurement unit 2 in the X (left and right), Y (up and down), and Z (front and back) directions with respect to the eye E. The XYZ drive unit 7a may be, for example, a combination of a first drive unit that moves in the horizontal (XZ) direction and a second drive unit that moves in the vertical (Y) direction. In this embodiment, the XYZ drive unit 7a is electrically driven based on a signal from the control unit 50 (see FIG. 5).

  The measurement unit 2 includes a platide unit 20, a first measurement unit 21, and a second measurement unit 22. The platide unit 20 is used together with the first measurement unit 21 to measure the corneal shape of the eye to be examined. The first measurement unit 21 is used to measure the eye refractive power as the eye characteristic of the eye E. The second measurement unit 22 is used for measuring intraocular pressure as an eye characteristic of the eye E to be examined.

<Arrangement of each unit>
1-4, the 1st measurement axis which is a measurement axis of the 1st measurement unit 21 is shown with the code | symbol L1, and the 2nd measurement axis which is the measurement axis of the 2nd measurement unit 22 is shown with the code | symbol L2. In the present embodiment, the first measurement axis L1 passes through the central portion of the platide plate 20a and is coaxial with the measurement axis in corneal shape measurement. The second measurement axis L2 passes through a region away from the center in the platide plate 20a. Window portions 20b and 20c are formed in the platide plate 20a as passage paths of the first measurement axis L1 and the second measurement axis L2 (see FIGS. 3 and 4). The window portion 20b corresponds to the first measurement axis L1, and the first measurement axis L1 passes therethrough. The window portion 20c corresponds to the second measurement axis L2, and the second measurement axis L2 passes therethrough.

  In the present embodiment, the platide unit 20 is disposed on the front surface of the measurement unit 2 with the front surface of the platide plate 20a facing the eye E to be examined. In the present embodiment, the first measurement unit 21 and the second measurement unit 22 are arranged so that the measurement axis L1 of the first measurement unit 21 and the measurement axis L2 of the second measurement unit 22 are different in height. ing. As an example, in the present embodiment, the second measurement unit 22 is stacked on the first measurement unit 21.

  The measuring unit 2 is moved in the vertical direction (Y direction shown in FIG. 1) with respect to the eye to be examined by an XYZ driving unit 7a provided on the moving table 7. Further, the XYZ driving unit 7a moves the measuring unit 2 in the Y direction with respect to the eye to be examined, and selectively selects one of the first measuring axis L1 and the second measuring axis L2 so as to be approximately the same height as the eye E to be examined. Driven to match. For this reason, the drive amount of the XYZ drive unit 7a needs to ensure at least the interval between the first measurement axis L1 and the second measurement axis L2. More preferably, in each measurement mode, it is preferable to secure a movable range to the extent that automatic alignment with respect to the eye to be examined can be performed smoothly.

  In the present embodiment, the positional relationship between the first measurement unit 21 and the platide unit 20 is fixed.

  In addition, a second moving unit 8 is provided between the first measuring unit 21 and the second measuring unit 22, and the entire second measuring unit 22 is driven by the second moving unit 8. The measurement unit 21 is moved in the front-rear direction. At this time, the distal end portion (nozzle 22a) of the second measurement unit 22 is moved in the front-rear direction with respect to the surface (front surface) of the platide unit 20. The second drive unit 8 moves the second measurement unit 22 in a direction approaching the eye E during the measurement of intraocular pressure, and moves the second measurement unit 22 from the eye E during the measurement of the corneal shape and the reflex measurement. Used to move away. In the present embodiment, at the time of corneal shape measurement and reflex measurement, the distal end portion of the second measurement unit 22 is retracted at least from the eye E to be separated from the front surface of the platide plate 20a. In the present embodiment, it is desirable that the distal end portion of the second measurement unit 22 is retracted from the back surface of the placido plate 20a when performing corneal shape measurement and reflex measurement.

<Cornea shape measurement part>
In the present embodiment, a corneal shape measurement unit is formed by the platide unit 20 and the anterior segment imaging optical system 211. The corneal shape measuring unit in the present embodiment serves both as a topographer and a keratometer.

  The platide unit 20 is an index projector in the present embodiment. The platide unit 20 projects a pattern index onto the cornea. In the present embodiment, the pattern index is constituted by a ring index by visible light. The platide unit 20 may include at least a light source 201 (referred to as a top light source, see FIG. 5) suitable for forming a pattern index in addition to the platide plate 20a. A plurality of light sources 201 may be provided, and among the plurality of ring patterns formed on the platide plate 20a, some of the ring patterns used for kerato measurement may be independent of the light source 201. . Since the light source is independent, in this embodiment, the ring pattern 204 corresponding to the circumferential region having a diameter of 2.4 mm on the cornea can be turned on independently (see FIG. 3). As shown in FIG. 3, in the platide plate 20a, the ring pattern 204 is formed closer to the center of the platide plate 20a than the window portion 20c.

  In the present embodiment, the pattern index projected from the platide unit 20 can be switched. At the time of kerato measurement, one ring index corresponding to a circumferential area of 2.4 mm on the cornea is projected from the platide unit 20 with respect to the cornea placed at an appropriate working distance on the optical axis L1. .

  In the topo measurement, a plurality of concentric ring indices are projected onto the cornea placed at an appropriate working distance on the optical axis L1. In the present embodiment, a pattern index based on a concentric multiple ring pattern is projected from the platide unit 20 onto a region within a diameter of approximately 10 mm on the cornea.

  In the present embodiment, the surface of the platide plate 20a is flat. Further, the platide plate 20a is formed with a diameter of 200 mm or more. Thereby, the shape distribution in the range of about 10 mm in diameter on the cornea can be measured while ensuring a relatively long working distance.

  In the present embodiment, the platide unit 20 further includes a liquid crystal unit 202 and a liquid crystal moving unit 203. The liquid crystal unit 202 is inserted into and removed from the window 20c corresponding to the second measurement axis L2 by the liquid crystal moving unit 203. The liquid crystal moving unit 203 combines the movement in the up / down / left / right direction and the movement in the front / rear direction so that the front surface of the liquid crystal unit 203 and the front surface of the platide plate 20a are arranged on substantially the same plane. By moving 203, the liquid crystal unit 203 may be inserted into the window portion 20c. However, the front surface of the liquid crystal unit 203 after being inserted into the window portion 20c and the front surface of the platide plate 20a may be arranged so as to be shifted in the front-rear direction. In addition, the liquid crystal unit 202 is disposed with the front side facing the eye to be examined while being disposed on the window 20c.

  The front surface of the liquid crystal unit 202 is a light emitting surface. As the light source, the liquid crystal unit 202 may be provided with a backlight light source. In addition, the top light source 201 may be used as the light source of the liquid crystal unit 202.

  In the present embodiment, since the window portion 20c is formed corresponding to the second measurement axis L2, a part of the pattern index (multiple ring index) formed by the platide plate 20a is missing at the time of topo measurement. Occurs. The lacking part is formed by the liquid crystal unit 202 based on a control signal from the control unit 50. As a result, a part of the ring index missing by the window 20c is optically interpolated.

  The liquid crystal unit 202 is inserted at least during corneal shape measurement and retracted at least during intraocular pressure measurement. After the retreat, the nozzle 22a of the second measurement unit 22 is advanced toward the cornea.

  In the present embodiment, the corneal reflection light of the pattern index projected from the platide plate 20a and the liquid crystal unit 202 is captured as a pattern index image by the anterior segment imaging optical system 211 housed in the first measurement unit 21. By analyzing the pattern index image, the control unit 50 measures the corneal shape. Thus, the optical system used for measuring the corneal shape is formed across the platide unit 20 and the first measurement unit 21.

<Eye refractive power measurement unit>
The first measurement unit 21 is provided with a reflex measurement optical system 212 (see FIG. 5). The optical system 212 is, for example, a projection optical system that projects a spot-like measurement index on the fundus through the center of the pupil of the eye E, and a fundus reflected light reflected from the fundus in a ring shape through the periphery of the pupil. And a light receiving optical system that causes the two-dimensional imaging device to capture a ring-shaped fundus reflection image (none of which is shown).

  The first measurement unit 21 may include various optical systems such as the first alignment optical system 213 and the fixation target presenting optical system 214. The alignment index from the first alignment optical system 213 is projected onto the cornea, for example, through openings 213a and 213b formed in the platide plate 20a (see FIGS. 3 and 4).

<Intraocular pressure measurement unit>
A nozzle 22a is provided at the tip of the second measurement unit 22, and a fluid (for example, compressed air) is sprayed onto the eye cornea through the nozzle 22a. And an intraocular pressure is measured based on the deformation | transformation of the cornea by spraying of a fluid. For example, the second measurement unit 22 may include a fluid compression chamber 221 in addition to the nozzle 22a. The fluid compression chamber 221 has a space for compressing the fluid sprayed to the cornea, and may be configured by, for example, a cylinder and a piston. The second measurement unit 22 includes various optical systems such as a measurement optical system (applanation detection optical system) 221 for detecting a deformed state of the cornea, an alignment optical system 223, and a fixation target presentation optical system (not shown). May be. A detection signal from the applanation detection optical system 222 may be input to the control unit 50 and used to calculate an intraocular pressure value in the control unit 50. The second measurement axis L2 may be the optical axis in the applanation detection optical system described above. For further detailed configuration of the second measurement unit 22, refer to, for example, Japanese Patent Application Laid-Open No. 2007-144128 by the present applicant. Further, instead of the measurement optical system 221, a pressure sensor may be provided. The pressure sensor detects the pressure in the fluid compression chamber. A detection signal from the pressure sensor may be used by the control unit 50 to calculate an intraocular pressure value.

  When measuring intraocular pressure, it is necessary to bring the tip of the second measurement unit 22 (tip of the nozzle 22a) closer to the corneal surface of the eye E to about tens of millimeters. In this embodiment, in order to measure intraocular pressure without bringing the platide plate 20a into contact with the face of the subject, the second measurement unit 22 is moved by the moving unit 8 so that the nozzle 22a protrudes from the front surface of the platide plate 20a. Is moved forward.

  Note that the alignment index from the second alignment optical system 223 is projected onto the cornea through, for example, openings 223a and 223b formed at the nozzle tip (see FIG. 4).

  For further detailed configuration of the optical system of the first measurement unit 21 and the second measurement unit 22, refer to, for example, “JP-A-2006-214466” by the present applicant.

  The apparatus 1 may further include a corneal thickness measurement optical system 230. The corneal thickness measurement optical system 230 is used to measure the corneal thickness of the eye E. For example, light projection optics that projects light for measuring corneal thickness on the cornea Ec to be examined through an examination window serving as a tip of the first measurement unit 21 in the housing of the first measurement unit 21. The system is arranged, and the reflected light from the cornea of the eye to be inspected by the above-mentioned light projecting optical system is disposed below the first measurement unit 21 with respect to the first measurement axis L1 with different optical axes (light reception). A photographing (light-receiving) optical system that receives light using the (optical axis) may be arranged. Further, the corneal thickness measurement optical system 230 may be provided in the housing of the second measurement unit 22.

  The joystick 71 is a part of a UI (User Interface) 70 (see FIG. 5) of the device 1. The joystick 71 is operated by the examiner in order to change the positional relationship between the eye E and the measurement unit 2. In the present embodiment, the moving table 7 is moved in the horizontal direction on the base 5 by operating the joystick 71. Further, when the examiner rotates the rotary knob formed on the joystick 71, the measuring unit 2 is moved in the Y direction by the XYZ driving unit 7a. A measurement start switch may be provided on the top of the joystick 71.

  The monitor 80 displays an observation image during alignment, a measurement result, and the like. The monitor 80 may be a touch panel display. In this case, the monitor 80 may be a part of the UI 70.

<Control system>
Next, with reference to FIG. 5, the control system in the apparatus 1 of this embodiment is demonstrated.

  The control unit 50 is a processor that controls the entire apparatus and calculates measurement results. The control unit 50 is connected to the XYZ driving unit 7a, the memory 51, the UI 70, the monitor 80, and the like in addition to each unit of the measuring unit 2.

  The memory 51 may include a rewritable non-transitory storage medium, and may be a flash memory, a hard disk, or the like, for example. Images and measurement data obtained as a result of photographing and measurement are stored in the memory 51. The program defining the measurement operation and the fixed data may be stored in the memory 51.

<Measurement operation>
The operation of the ophthalmologic measurement apparatus 1 having the above configuration will be described. In the following description, the operation accompanying the switching of the measurement mode will be mainly described. For details of measurement operations for obtaining various eye characteristics, see, for example, Japanese Patent Application Laid-Open No. 2007-144128 by the present applicant.

  For example, the control unit 50 can select three modes: an eye refractive power measurement mode, an intraocular pressure measurement mode, and a corneal shape measurement mode. Each measurement mode may be switched based on an operation input by an examiner or may be switched automatically.

  When the intraocular pressure is continuously measured with other eye characteristics, it is preferable to measure the intraocular pressure after measuring the other eye characteristics. This is because if the intraocular pressure is measured first, there is a possibility that the influence of the spraying of the fluid or the like may remain. The eye refractive power measurement and the corneal shape measurement may be performed in any order.

  In the present embodiment, the measurement may be performed in the state shown in FIGS. 1 and 3 between the eye refractive power measurement mode and the corneal shape measurement mode.

  That is, the control unit 50 drives the XYZ moving unit 7a to adjust the height of the measuring unit 2 and adjusts the first measurement axis L1 to the height of the eye E to be examined. At this time, the 2nd moving part 8 is driven previously, and the front-end | tip part 22a of the 2nd measurement unit 22 is retracted | retreated rather than the front surface of the platide board 20a. This prevents the tip of the nozzle 22a from coming into contact with the subject during height adjustment. Further, the liquid crystal unit 202 may be inserted into the window portion 20c so as to block between the tip of the nozzle 22a and the eye E to be examined. Thereby, the corneal shape measurement can be performed smoothly at the stage where the alignment adjustment is completed.

  Next, alignment in the X, Y, and Z directions of the measurement unit 2 with respect to the eye E is performed. At this time, the control unit 50 may cause the monitor 80 to display a front image of the anterior segment imaged by the anterior segment imaging optical system 211 in the first measurement unit 21 as an observation image. Further, the control unit 50 projects the alignment index from the first alignment optical system 213. The control unit 50 performs alignment by controlling the XYZ driving unit 7a according to the positional relationship between the alignment index image on the observation image and the anterior segment.

  In this embodiment, since the platide plate 20a is formed with a large diameter of 200 mm or more as the index projector, it is easy to secure a working distance at the time of corneal shape measurement, and the ref measurement optical system 212 is also operated in principle. Since it is easy to secure the distance, between the eye refractive power measurement mode and the corneal shape measurement mode, an appropriate working distance (here, the eye E and the front surface of the measurement unit 2 in the proper alignment state (here, It is easy to match the distances to the platide plate 20a). For example, it can be set as the range of about 40 mm-100 mm, for example. In addition, the alignment allowable range in the working distance direction between the eye refractive power measurement mode and the corneal shape measurement mode can be secured relatively long. Therefore, in this embodiment, the corneal shape measurement and the eye refractive power measurement can be performed smoothly and continuously.

  Thereafter, when the alignment is completed, eye refractive power measurement and corneal shape measurement are automatically performed.

  In this embodiment, the corneal shape measurement mode is divided into a kerato mode, a topo mode, and a continuous measurement mode. Each measurement mode can be selected in advance by the examiner via the UI 70. Here, the operation of the apparatus is shown assuming that the continuous measurement mode is selected.

  In the continuous measurement mode, first, the controller 50 performs kerato measurement. In the kerato measurement, the pattern 204 (see FIG. 3) is selectively caused to emit light among the plurality of ring patterns formed on the control unit 50 placido plate 20a. As a result, a ring-shaped pattern index is projected onto a circumferential region having a diameter of 2.4 mm on the cornea. The corneal reflected light of the pattern index image is captured as an index image by the anterior segment imaging optical system. The control unit 50 acquires the curvature radius, refraction, strong main meridian, weak main meridian, and the like in the circumferential region as measurement results by kerato measurement by analyzing the index image.

  Next, the control unit 50 determines whether or not the top measurement is necessary based on the measurement result of the kerato measurement. In the present embodiment, the determination process is performed by comparing a confidence coefficient, which is a kind of measurement result of the kerato measurement, with a threshold value.

  In the present embodiment, when the reliability coefficient is larger than the threshold value, it is determined that the topo measurement is unnecessary, and the corneal shape measurement may be terminated as it is. On the other hand, when the reliability coefficient is equal to or smaller than the threshold value, it is determined that the top measurement is necessary. In this case, in the topo measurement, a pattern index by multiple rings is projected from the placido plate 20a and the liquid crystal unit 202.

  It is preferable that the liquid crystal unit 202 is inserted in advance with respect to the window portion 20c in the continuous measurement so that the top measurement is performed without a gap after the kerato measurement. For example, from the kerato measurement to the topo measurement may be performed in about several seconds.

  At the time of topo measurement, the platide plate 20a and the liquid crystal unit 202 may emit light simultaneously or sequentially. As a result, in this embodiment, a multi-ring pattern index is projected onto an area of the cornea having a diameter within about 10 mm. The corneal reflected light of the pattern index image is captured as an index image by the anterior segment imaging optical system. The control unit 50 acquires corneal shape distribution data by analyzing the index image.

  After completion of the corneal shape measurement, the measurement result may be displayed. In the present embodiment, at least measurement results of kerato measurement (for example, various numerical values) may be displayed. When both kerato measurement and topo measurement are measured, both the measurement result of kerato measurement and the measurement result of topo measurement may be displayed simultaneously. Further, as the first display, information indicating that the measurement of the topo measurement has been performed (that the measurement result of the topo measurement exists) may be displayed together with the measurement result of the kerato measurement. When the display switching operation is accepted through the UI 70 while the operation is being performed, the measurement result of the topo measurement may be displayed as the second display. In the second display, for example, a corneal shape map based on the distribution data may be output to the monitor 80 or the like as a measurement result. The corneal shape map may be, for example, any one of a cornea elevation map, a curvature map, and a corneal refractive power map. At this time, in the cornea shape map, a part of the region interpolated by the light projection from the liquid crystal unit 202 may be displayed in a different mode (for example, different colors) from the other measurement regions. However, it is not always necessary to distinguish display modes.

After completion of the eye refractive power measurement or the corneal shape measurement, the mode shifts to an intraocular pressure measurement mode. At this time, the control unit 50 drives the XYZ drive unit 7a to move the measurement unit 2 downward so that the second measurement axis L2 and the eye E to be examined are approximately the same height (roughly I do not care)
Further, the liquid crystal unit 202 is retracted from the window 20c (from the second measurement axis L2). Thereby, the nozzle 22a can advance. The control unit 50 drives the second drive unit 8 to move the second measurement unit 22 in a direction approaching the eye E. As a result, the nozzle 22a is positioned on the subject side from the front surface of the platide plate 20a. By such an operation, the working distance between the eye E and the device 1 is suitable for measuring intraocular pressure while preventing contact between the front surface of the housing such as the platide plate 20a and the face of the subject (for example, the nose). Adjusted to distance.

  When the second measurement unit 22 is moved toward the eye to be examined, there is a possibility that the tip of the nozzle 22a may come into contact with the eye E. Therefore, preferably, the second drive unit 8 is once driven and controlled to measure the measurement unit. 2 is once moved to a rear position in a direction away from the eye E (for example, after being retracted to a reference position set to the rearmost side), the nozzle 22a is protruded by a certain amount from the front surface of the plate 20a. May be.

  Thereafter, the control unit 50 performs alignment (for example, Z alignment) when measuring intraocular pressure. The alignment at this time may be performed based on, for example, a cornea reflection image or may be performed based on another index. The index projected onto the eye to be examined may be projected from the second alignment optical system 223 included in the second measurement unit 22, for example.

  After the alignment is completed, the controller 50 drives the piston to compress the air in the cylinder, and blows the compressed air from the nozzle toward the cornea to perform intraocular pressure measurement.

  In the present embodiment, the eye characteristics are measured in each measurement mode as described above.

  As described above, the measurement unit 2 has the first measurement unit 21 and the second measurement unit 22 stacked on the back side of the platide unit 20. When switching between the intraocular pressure measurement mode and the other measurement modes, the measurement unit 2 including each unit is moved up and down. Therefore, in this embodiment, the measurement axes L1 and L2 of each measurement unit are not bypassed the platide plate 20a, and the windows 20b and 20c are formed in the platide plate 20a so as to pass through the inside of the platide plate 20a. The first measurement unit 21 and the second measurement unit 22 can be stacked in a compact manner in the vertical direction. Along with this, the driving range in the Y direction of the XYZ driving unit 7a can be suppressed. As a result, the size of the entire apparatus can be easily suppressed. Moreover, since the center of gravity of the apparatus 1 can be further lowered, it is possible to suppress the measurement unit 2 from being displaced in the left-right direction when moved up and down.

  Further, when measuring the corneal shape, the tip portion (nozzle 22a) of the intraocular pressure measurement unit is disposed at a position retracted from the front surface of the platide plate 20a, so that the pattern index for measuring the corneal shape is the nozzle 22a. It is well projected onto the cornea without being blocked by.

  In this case, the lack of pattern index due to the window 20c through which the tip of the intraocular pressure measurement unit enters and exits is interpolated by the projection of a partial pattern from the liquid crystal unit 202. For this reason, a corneal shape can be measured favorably.

  As described above, the description has been given based on the embodiment, but various modifications are allowed in the embodiment.

  For example, in the above embodiment, the liquid crystal unit 202 is inserted into and removed from the window 20c, but the present invention is not necessarily limited thereto. For example, a striped pattern plate 205 which is an example of an interpolation index projector may be fixedly disposed in the vicinity of the window 20c through which the nozzle 22a passes. For example, a more detailed description will be given with reference to FIGS. 6A to 6C. The striped pattern plate 205 may be disposed substantially perpendicular to the front surface of the placido plate 20a. In this case, the light emitting surface of the striped pattern plate 205 is arranged facing the measurement axis L1 having a corneal shape. The light-emitting surface is shielded from light by a striped mask, thereby projecting a striped pattern. The striped pattern corresponds to a portion of the pattern index from the platide plate 20c that is missing by the window portion 20c.

  Further, among the end portions of the window portion 20c, the striped pattern plate 205 is formed at the end portion on the measurement axis L1 side, so that it is difficult to block the index light beam from the platide plate 20a. In this case, the amount of protrusion of the striped pattern plate 205 from the front surface of the platide plate 20a is equal to or less than the amount of protrusion of the nozzle 22a at the time of measuring intraocular pressure, thereby suppressing contact between the subject and the apparatus. This is preferable. The striped pattern plate 205 may be formed integrally with the placido plate 20a, or may use the top light source 201 as a light source. Further, instead of the striped pattern plate 205, a liquid crystal unit as in the above embodiment may be fixedly arranged.

  The striped pattern plate 205 (an example of an interpolation index projector) may be movable in the front-rear direction. In this case, the apparatus 1 may have a moving unit that moves the striped pattern plate 205 in the front-rear direction. The moving unit may be shared with the second driving unit 8 (the moving unit of the second measurement unit 22) or may be a separate body.

  The striped pattern plate 205 is disposed in front of the front surface of the placido plate 20a at least in the corneal shape measurement mode. On the other hand, in the eye refractive power measurement mode and the intraocular pressure measurement mode, the striped pattern plate 205 may be retracted as compared with the measurement in the corneal shape measurement mode. Further, when switching between the corneal shape measurement mode or the eye refractive power measurement mode and the intraocular pressure measurement mode (particularly during the period in which the measurement unit 2 moves up and down), the striped pattern plate 205 is retracted. It is preferable. It becomes difficult for the striped pattern plate 205 to contact the face of the subject.

  Furthermore, the striped pattern plate 205 (an example of an interpolation index projector) that moves in the front-rear direction may be formed on the side surface (the lower surface in this embodiment) of the nozzle of the intraocular pressure measurement unit 22.

  For example, in the above-described embodiment, the pattern index is projected even in the kerato mode from the index projector that can project the pattern index for obtaining the distribution information of the cornea shape. However, the present invention is not necessarily limited to this, and in the kerato mode, curvature information in a single circumferential region may be acquired by projecting a pattern index onto the cornea from an optical system other than the index projector. In this case, the ophthalmologic measurement apparatus may have a kerato index projection optical system independent of the index projector. The measurement axis of the kerato index projection optical system is preferably coaxial with the measurement axis used for corneal shape measurement based on the pattern index from the index projector. However, it is not necessarily limited to this.

  Further, for example, in the above-described embodiment, the case where the first measurement unit 21 and the second measurement unit 22 are stacked is described. However, the first measurement unit 21 and the second measurement unit 22 include the platide plate 20a. Of these radial directions, they may be arranged side by side in one direction, or may be arranged side by side in the left-right direction.

DESCRIPTION OF SYMBOLS 1 Ophthalmological measuring apparatus 20 Platide unit 20a Platide board 20b, 20c Window part 21 1st measurement unit 22 2nd measurement unit E Eye to be examined L1 Measurement axis L2 Measurement axis

Claims (12)

An ophthalmologic measurement apparatus that measures a plurality of eye characteristics of a subject eye,
A first measurement unit for measuring a first eye characteristic different from the corneal shape via a first measurement axis;
A second measurement unit that measures a second eye characteristic different from both the corneal shape and the first eye characteristic via a second measurement axis arranged in parallel in the vertical and horizontal directions of the first measurement axis; ,
An index projector for projecting a pattern index for measuring a corneal shape from a front surface facing the subject's eye onto the cornea of the subject's eye, passing through the first measurement axis and the second measurement axis on the front surface An ophthalmologic measurement apparatus, comprising: an index projector having a window portion for forming the window portion corresponding to each measurement axis.   The ophthalmologic measurement apparatus according to claim 1, further comprising an interpolation unit that interpolates a lack of the pattern index by at least one of the window portions.   The ophthalmic measurement apparatus according to claim 2, wherein the interpolation unit is an interpolation index projector that projects a second pattern index for interpolating a part of the pattern index that is lacking by the window portion onto the cornea.   The ophthalmic measurement apparatus according to claim 3, wherein the interpolation index projector is inserted into and removed from the window portion.   The ophthalmic measurement apparatus according to claim 3, wherein the interpolation index projector has a surface intersecting with the front of the index projector, and projects the second pattern index from the surface onto the cornea.   The ophthalmic measurement apparatus according to claim 5, wherein the interpolation index projector is moved in the front-rear direction with respect to the front surface of the index projector. Control means for selecting a measurement mode between a corneal shape measurement mode for measuring the corneal shape and a second measurement mode for measuring the first eye characteristic or the second eye characteristic;
The ophthalmic measurement apparatus according to claim 4 or 6, wherein the control unit performs movement control of the interpolation index projector according to selection of the measurement mode.   The ophthalmic measurement apparatus according to claim 3, wherein the interpolation index projector is provided in at least one of the first measurement unit and the second measurement unit.   The interpolation means interpolates the lack of the pattern index due to the window by switching the area on the cornea where the pattern index is projected and projecting the pattern index from the index projector. Ophthalmic measuring device. An anterior ocular segment imaging optical system for imaging the eye to be examined in a state in which the pattern index is projected;
A map generation unit that generates a corneal shape map based on an anterior segment image captured by the anterior segment imaging optical system;
The ophthalmic measurement according to any one of claims 2 to 9, wherein the map generation unit displays a part of the corneal shape map interpolated by the interpolation unit in a manner different from other measurement areas. apparatus.   One of the first measurement unit and the second measurement unit has an anterior ocular segment imaging optical system that captures a pattern index image of corneal reflected light of the pattern index, and the first measurement axis and the first measurement axis 11. The ophthalmologic measurement apparatus according to claim 1, wherein an axis corresponding to one of the two measurement axes is coaxial with an optical axis of the anterior ocular segment imaging optical system. The first measurement unit measures eye refractive power as the first eye characteristic,
The ophthalmic measurement apparatus according to claim 1, wherein the second measurement unit measures intraocular pressure as the second eye characteristic.

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