JPH06205745A - Ophthalmological measuring device - Google Patents

Abstract

PURPOSE:To provide a noncontact tonometer capable of easily and accurately measuring the ocular tension by itself. CONSTITUTION:A concave mirror 11 and a light source 12 are arranged on the optical axis L in the visual line direction of a subject eye E, and the concave mirror 11 is provided with a center hole 11a for seeing the light source 12 and a nozzle hole 11b for inserting a nozzle 13. The nozzle 13 is fixed to a three-dimensionally movable alignment driving means 15 via a chamber 14, and a cylinder 18 is connected to the chamber 14 via a flexible pipe 17. The subject eye E is aligned by seeing the light source 12 through the center hole 11a, the alignment driving means 15 is driven by the signal of a four-leaf sensor not shown in the figure, and the nozzle 13 is aligned with the subject eye E.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ophthalmic measuring device used in an ophthalmological clinic or the like.

[0002]

[Prior art]

(1) Conventionally, the tonometer is often operated by an examiner, but the examinee may operate it by himself.

(2) On the other hand, when measuring the refractive power of a soft contact lens, a lens holder 1 as shown in FIG.
The lens receiver 1 is provided with an opening 1a for transmitting the measurement light, and the soft contact lens S is placed so as to cover the opening 1a. Further, as shown in FIG. 12, a lens receiver 2 having a plurality of holes 2a may be used.

[0004]

[Problems to be Solved by the Invention]

(A) However, in the conventional example of the tonometer described above, there is a problem that it is difficult to perform delicate alignment because the subject's eye is reflected in the mirror and aligned when the subject operates it.

(B) On the other hand, in the conventional lens receiver 1 shown in FIG. 11, since the soft contact lens S is placed so as to cover the opening 1a, the center of the soft contact lens S bends into the opening 1a. However, the problem that measurement light is disturbed occurs. Further, in the conventional lens receiver 2 shown in FIG. 12, the water adhering to the soft contact lens S has holes 2a.
And the measurement light is disturbed.

The first object of the present invention is to solve the above-mentioned problems.
It is an object of the present invention to solve the problem (a) and to provide an ophthalmic measurement device which has a simple structure and can easily measure the intraocular pressure by itself.

A second object is to solve the above-mentioned problem (b) and to provide an ophthalmic measuring apparatus capable of accurately measuring the refractive power of a soft contact lens.

[0008]

A first ophthalmic measuring apparatus for achieving the above object deforms the cornea by blowing air from a nozzle, and the deformation is detected by photoelectric detection means to detect intraocular pressure. An apparatus for measuring, an observation system having an optical member for enlarging an eye to be inspected, which has a hole through which the nozzle is inserted, and a measurement system including the nozzle, the photoelectric detection unit, and alignment monitoring photoelectric unit, And an alignment driving unit for driving the measurement system three-dimensionally by the signal of the alignment monitoring photoelectric unit to perform alignment.

The second ophthalmic measuring device is a device for measuring the refracting power of the lens based on the light flux transmitted through the lens, and is light transmissive without convergence and divergence for mounting the lens. A mounting member is provided, and the mounting member is provided with a contact surface having a curvature that substantially matches the curvature of the cornea.

[0010]

The first ophthalmic measuring device having the above-mentioned structure is
The eye to be inspected is magnified and aligned by the optical member of the observation system, and the alignment monitoring photoelectric device drives the alignment driving device to align the measurement system.

Further, in the second ophthalmic measuring apparatus, since the mounting member is provided with the contact surface having a curvature substantially equal to that of the cornea, when the lens is mounted on the contact surface, the lens is gravitationally applied to the contact surface. follow.

[0012]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The present invention will be described in detail with reference to the embodiments shown in FIGS. FIG. 1 is a configuration diagram of a first embodiment relating to a non-contact tonometer, and a concave mirror 11 and a light source 12 as a self-eye observation system are arranged on an optical axis L in the line-of-sight direction of an eye E to be examined. The concave mirror 11 has a characteristic of reflecting visible light and transmitting infrared light, and the infrared light is used for alignment and deformation detection. A center hole 11a is provided at the center of the concave mirror 11, and the eye E to be inspected can observe the light source 12 through the center hole 11a. A nozzle hole 11b is provided in the lower portion of the concave mirror 11, and the eye E
A nozzle 13 for injecting air is inserted into.
The nozzle 13 is attached to the alignment driving means 15 via the chamber 14, and the chamber 14 is provided with a pressure sensor 16 for measuring intraocular pressure. A cylinder 18 is connected to the chamber 14 via a flexible tube 17, and a piston 19 is fitted in the cylinder 18.
The piston 19 is connected to a solenoid 21 via a link 20, and the movement of the solenoid 21 drives the piston 19. The alignment driving means 15 is three-dimensionally driven by a step motor or solenoid as indicated by the arrow.

FIG. 2 is a block diagram of the measuring optical system. A lens 22, a half mirror 23, a half mirror 24, and a four-leaf sensor 25 are sequentially arranged on one optical axis LL with the nozzle 13 in between. , The light source 2 in the incident direction of the half mirror 23
6 is arranged, and the photoelectric sensor 27 is arranged in the reflection direction of the half mirror 24. A lens 22, a half mirror 23, and a four-leaf sensor 25 are arranged on the other optical axis LR, and a light source 26 is arranged in the incident direction of the half mirror 23. Here, the four-leaf sensor 25 is composed of four elements 25a to 25d as shown in FIG. 3, and the reflection image R of the cornea Ec is obtained.
The position of can be detected three-dimensionally. Further, the light source 26 is arranged conjugate with the focal position of the lens 22.

With such a structure, when the subject himself / herself measures the intraocular pressure, the light source 12 is moved to the center of the central hole 11a while moving the subject's eye E reflected on the concave mirror 11 as shown in FIG. To reach. Here, the concave mirror 1 having a large curvature
When 1 is used, the light source 12 becomes visible only when the subject's eye E is close to the predetermined position. After the eye E to be inspected is aligned, the light flux of the light source 26 is reflected by the half mirror 23, collimated by the lens 22, and projected onto the cornea Ec. The light source image R generated on the cornea Ec is imaged on the four-leaf sensor 25, and the three-dimensional position of the light source image R is detected. By this signal, the alignment driving means 15
Are driven three-dimensionally, and the nozzle 13 is aligned so that the air axis of the nozzle 13 is perpendicular to the cornea Ec and has a predetermined distance.

When the nozzle 13 is thus aligned, the solenoid 21 is energized to drive the piston 19, and compressed air is jetted from the nozzle 13 to the cornea Ec. The cornea Ec is flattened by this compressed air, and the light source image R
Is conjugated with the photoelectric sensor 27, and the output becomes maximum. This maximum value is detected by the pressure sensor 16 and the intraocular pressure is obtained.

Here, when the light source image R deviates from the four-leaf sensor 25, the nozzle 13 is not aligned, but the eye E to be inspected is positioned in the center by looking at the light source 12 through the central hole 11a in advance. 1mm from the center
If located within, a signal is obtained and the nozzle 13
Are well aligned. Further, the nozzle hole 11b provided in the concave mirror 11 is formed larger than the diameter of the nozzle 13, the concave mirror 11 and the light source 12 are fixed independently of the alignment driving means 15, and the cylinder 18 is also the flexible tube 1.
Since it is connected to the alignment driving means 15 via 7, the position of the nozzle 13 for ejecting air can be freely driven three-dimensionally by the alignment driving means 15.

FIG. 5 is a block diagram of the alignment detection system and the deformation detection system of the second embodiment. A lens 31 having the nozzle 13 inserted therein, a transparent window 32 provided in the chamber 14, a half mirror 33, a half mirror 34, a cylindrical lens 35, and a four-leaf sensor 36 are sequentially arranged in the line-of-sight direction of the eye E to be inspected. . A light source 37 is provided in the incident direction of the half mirror 33.
Is arranged, and the photoelectric sensor 38 is arranged in the reflection direction of the half mirror 34. Here, the light source image R1 is formed on the four-leaf sensor 36 via the cylindrical lens 35. In addition, the generatrix direction of the cylindrical lens 35 is directed at 45 ° with respect to the dividing line of the four leaves so that a three-dimensional signal can be obtained.

With such a structure, the light flux of the light source 37 is reflected by the half mirror 33, and the transparent window 32 and the nozzle 13 are provided.
Is projected through the cornea Ec. The light source image R1 is the lens 31,
An image is formed on the four-leaf sensor 36 through the cylindrical lens 35, and the nozzle 13 is aligned as in the first embodiment.
In this state, when compressed air is jetted from the nozzle 13,
The cornea Ec is flattened and the light source image R1 moves to the light source image R2, and the light source image R2 is conjugated with the photoelectric sensor 38 and the output becomes maximum. This maximum value is detected as in the first embodiment, and the intraocular pressure value is obtained.

FIG. 6 is a block diagram of the self-eye observation system of the third embodiment, in which the lens 41, the half mirror 42, and the television camera 43 are sequentially arranged in the line-of-sight direction of the eye E to be examined. A TV monitor 44 is arranged in the reflection direction. The lens 41 has the nozzle 1 of the above-described embodiment.
A nozzle hole 41a through which 3 is inserted is provided. The other structure is the same as that of the first embodiment.

At the time of measurement, the eye E to be examined is photographed by the television camera 43 and displayed on the television monitor 44. The image on the television monitor 44 is reflected by the half mirror 42, magnified by the lens 41, and projected on the eye E to be inspected. Eye E
The effect after the alignment is similar to that of the first embodiment.

FIG. 7 is a block diagram of a lens refracting power measuring apparatus according to the fourth embodiment, in which a lens 52 and a soft contact lens S are mounted on an optical axis M which extends vertically downward from a light source 51. The contact member 53, the fixing member 54, the ring aperture stop 55, and the area CCD 56 are sequentially arranged, and a computer 58 having a push button 57 is connected to the area CCD 56. The contact member 53 is formed of glass, synthetic resin, or the like having a light-transmitting property so as to have the same curvature as the cornea Ec of the eye E, so that the measurement light flux N is not refracted when the soft contact lens S is not placed. Has been formed. As shown in FIG. 8, the ring aperture stop 55 is provided with a ring-shaped aperture 55a at the center. Area CC
D56 is four dividing lines 56a to 56d as shown in FIG.
The lens refracting power at the intersection of the ring light flux P and the ring light flux P is detected.

With this configuration, when measuring the lens refractive power of the soft contact lens S, the soft contact lens S is placed on the contact member 53. At this time, since the soft contact lens S contains water, a water layer is formed between the soft contact lens S and the contact member 53. The curvature of the soft contact lens S and the curvature of the contact member 53 are not necessarily the same, but since the soft contact lens S has flexibility, gravity may follow the contact member 53 and the water layer may generate a refractive power. Disappear. When the measurement light flux N is cast on the soft contact lens S in this state, a ring light flux P is projected on the area CCD 56 as shown in FIG. Area CCD 56
Then, from the intersection of the ring light flux P and the dividing lines 56a to 56d, the ring light flux P is detected, the signal is sent to the calculator 58 to calculate the refractive power including astigmatism, and the average value thereof is given by the command of the push button 57. It is calculated. Further, if the number of dividing lines is increased and the average value is calculated from many intersection points, the measurement accuracy is improved.

Instead of the ring aperture stop 55, 4 or 6 holes provided on the circumference may be used. In this case, the lens refracting power is obtained from the position of the point light flux. Further, the contact member 53, the fixing member 54, the ring aperture stop 55
May be detachably integrated with the apparatus main body so that the soft contact lens S can be replaced according to the type. Alternatively, the contact member 53 and the fixing member 54 may be integrally molded from a synthetic resin material, and the ring aperture stop 55 may be formed on the surface of the contact member 53 by vapor deposition. Further, the ring aperture stop 55 may be provided at a conjugate position in the device. Also,
Although the measurement light flux N is measured by the area CCD 56, any method may be used as the photoelectric measurement method, and the measurement may be performed while visually observing the transmitted light flux.

FIG. 10 shows a contact member 63 for measuring a hard contact lens, showing a case of measuring a soft contact lens S. The contact member 63 is fixed to the fixing member 64, and the ring aperture stop 6 is attached to the contact member 63.
5 is attached. Here, the contact member 63 is rotationally driven by a rotating device (not shown), and the area C
As for the dividing line of the CD 56, only two orthogonal lines 56a and 56c are used.

When the soft contact lens S is placed on the contact member 63, the soft contact lens S is partially uneven, but the difference in lens refracting power due to such unevenness is due to the contact member 63. Are averaged by rotating.

Instead of the ring light flux P, it is also possible to measure with three or four peripheral light fluxes. In this case, if the ring aperture stop 55 is fixed to the fixing member 64, the same position will be measured even if it is rotated, so it is necessary to provide the ring aperture stop 65 at a conjugate position in the apparatus. . Further, several types of contact members 63, fixing members 64, ring aperture diaphragms 65 and the like having different curvatures are prepared, and the cornea of the eye E to be inspected is prepared.
You may select and use it according to Ec.

[0027]

As described above, in the first ophthalmic measurement apparatus, the eye E to be inspected can be aligned in a predetermined manner by the optical member, and the alignment drive means is driven by the signal of the alignment monitoring photoelectric means to align the nozzle in a predetermined manner. Therefore, the intraocular pressure can be accurately measured even if the range of the alignment detection system and the alignment driving means is narrow, and the configuration is simple. Further, since the air is jetted obliquely to the eye to be inspected, the subject's anxiety is eliminated.

On the other hand, in the second ophthalmic measuring apparatus, since the lens follows the contact surface and matches the curvature of the cornea, the measuring light flux is not disturbed and the accuracy is improved.

[Brief description of drawings]

FIG. 1 is a side view of the configuration of a first embodiment.

FIG. 2 is a configuration diagram of a measurement optical system.

FIG. 3 is a cross-sectional view of a 4-leaf sensor.

FIG. 4 is an explanatory diagram of a usage state.

FIG. 5 is a configuration diagram of a second embodiment.

FIG. 6 is a configuration diagram of a third embodiment.

FIG. 7 is a configuration diagram of a fourth embodiment.

FIG. 8 is a front view of a ring aperture stop.

FIG. 9 is a front view of an area CCD.

FIG. 10 is a cross-sectional view of a contact member.

FIG. 11 is a cross-sectional view of a contact member of a conventional example.

FIG. 12 is a cross-sectional view of a conventional contact member.

[Explanation of symbols]

 11 concave mirror 13 nozzle 15 alignment drive means 25, 36 4-leaf sensor 27, 38 photoelectric sensor 53, 63 contact member 54, 64 ring aperture stop 55, 65 fixing member 56 area CCD

Claims (2)

[Claims] 1. An apparatus for measuring eye pressure by blowing air from a nozzle to deform the cornea and detecting the deformation by photoelectric detection means, and enlarging an eye to be inspected having a hole through which the nozzle is inserted. An observation system including an optical member, a measurement system including the nozzle, the photoelectric detection unit, and an alignment monitoring photoelectric unit, and a signal from the alignment monitoring photoelectric unit to drive the measurement system three-dimensionally to perform alignment. An ophthalmologic measuring device, comprising: an alignment driving means for performing. 2. An apparatus for measuring the refracting power of a lens based on a light flux transmitted through the lens, wherein a light-transmissive mounting member having no convergence / divergence for mounting the lens is provided, An ophthalmic measuring apparatus, wherein the placing member is provided with a contact surface having a curvature that substantially matches the curvature of the cornea.