JP4204107B2 - Ophthalmic equipment - Google Patents

Description

[0001]
[Industrial application fields]
The present invention relates to an improvement in an ophthalmologic apparatus provided with a bactericidal light generating means in a measuring unit that is moved away from an eye to be examined.
[0002]
[Prior art]
Conventionally, as an ophthalmologic apparatus provided with a germicidal light generating means in a measuring part that is separated and approached to an eye to be examined, those disclosed in JP-A-1-250220 and JP-A-3-68335 are known. Yes.
[0003]
Japanese Laid-Open Patent Publication No. 1-250220 discloses a non-contact tonometer as an ophthalmologic apparatus, in which a detachable cap is provided on a nozzle portion of the measurement unit and a light source as a sterilizing light generating means is provided and a pressure sensor is provided. The attachment of the cap to the nozzle portion is detected by a pressure-sensitive sensor, and a light source is emitted to generate a germicidal beam.
[0004]
Japanese Patent Laid-Open No. 3-68335 discloses a non-contact tonometer as an ophthalmologic apparatus, and a sterilizing light optical system of the measuring unit is provided with a light source as a sterilizing light generating means, and a cap is attached to the nozzle unit. Is detected by a pressure-sensitive sensor to emit light and generate germicidal light.
[0005]
[Problems to be solved by the invention]
However, the conventional ophthalmologic apparatus disclosed in Japanese Patent Application Laid-Open No. 1-250220 is provided with a sterilizing light generating means in the measuring unit and irradiates the nozzle part of the measuring unit with the sterilizing light from the inside to the outside. Because the idea that germicidal rays are irradiated to the eye to be examined when the eye to be examined is opposed to the nozzle part is undesirable from the viewpoint of safety, the nozzle part of the measuring part is directed from outside to inside It is configured to irradiate sterilizing light, and it is a structure that sterilizes the measurement part by operating the sterilizing light generating means by mounting the cap.If you forget to attach the cap, inconvenience that sterilization cannot be performed, measurement of If it is decided to perform sterilization frequently every time between intervals, the cap must be frequently attached and detached, which is extremely burdensome for the examiner and frequently sterilized every time between measurements. Inconvenience Ukoto can not easily also, since it is configured to detect the mounting of the cap by the pressure sensor, correspondingly, the mechanical structure of the sterilizing beam generating means is disadvantageously complicated.
[0006]
The present invention has been made in view of the above circumstances, and the object of the present invention is to sterilize frequently each time between measurements without complicating the mechanical structure of the sterilizing light generating means. An object of the present invention is to provide an ophthalmologic apparatus that can sterilize a measuring part easily and while maintaining safety even when it is configured to be performed.
[0007]
[Means for Solving the Problems]
In order to achieve the above object, the ophthalmologic apparatus according to claim 1 is an ophthalmologic apparatus provided with a bactericidal light generating means in a measurement unit that is moved away from the eye to be examined.
It is characterized by comprising detection means for detecting reflected light of the light beam projected from the measurement section, and determination means for determining whether or not to activate the germicidal light beam based on information of the detection means.
[0008]
The ophthalmologic apparatus according to claim 2 is characterized in that the detection unit also serves as a corneal deformation detection unit that detects a deformation of the cornea.
[0009]
According to the first and second aspects of the invention, the measuring section can be sterilized without complicating the mechanical structure of the sterilizing light generating means.
[0014]
DETAILED DESCRIPTION OF THE INVENTION
Hereinafter, embodiments of the present invention will be described with reference to the drawings.
(Embodiment 1)
1 and 2, the measuring unit S according to the present invention uses an anterior ocular segment observation system 10 for observing the anterior segment of the eye E to be examined, and index light for detecting alignment in the XY directions and detecting corneal deformation. XY alignment index projection optical system 20 that projects the cornea C of the eye E from the front, bactericidal light projection optical system 30 that irradiates the eye E with the bactericidal light, and the light reflected by the cornea C of the XY alignment index light is received and measured. XY alignment detection optical system 40 for detecting the positional relationship between the part S and the cornea C in the XY direction, the corneal deformation detection optical system 50 for receiving the reflected light of the XY alignment index light from the cornea C and detecting the deformation amount of the cornea C, the cornea The Z alignment index projection optical system 60 that projects the alignment index light in the Z direction obliquely onto C, and the reflected light from the cornea C of the Z alignment index light on the optical axis of the anterior ocular segment observation optical system 10 And a Z alignment detection optical system 70 for detecting the Z-direction positional relationship of the received measuring unit S and the cornea C from the direction symmetric with.
[0015]
The anterior ocular segment observation optical system 10 includes a plurality of anterior ocular segment illumination light sources 11 that are positioned on the left and right sides of the eye E and directly illuminate the anterior segment, an air blowing nozzle 12, an anterior segment window glass 13, and a chamber window. A glass 14, a half mirror 15, an objective lens 16, half mirrors 17 and 18, and a CCD camera 19 are provided, and O1 is an optical axis thereof.
[0016]
The anterior segment image of the subject eye E illuminated by the anterior segment illumination light source 11 passes through the inside and outside of the airflow spray nozzle 12, passes through the anterior segment window glass 13, the chamber window glass 14, and the half mirror 15, and the objective lens. 16 is formed on the CCD camera 19 through the half mirrors 17 and 18 while being focused by the camera 16.
[0017]
The XY alignment index projection optical system 20 is configured to make the focal point coincide with the XY alignment light source 21 that emits infrared light, the condenser lens 22, the aperture stop 23, the pinhole plate 24, the dichroic mirror 25, and the pinhole plate 24. A projection lens 26, a half mirror 15, a chamber window glass 14, and an airflow blowing nozzle 12 are disposed on the optical path.
[0018]
Infrared light emitted from the light source 21 for XY alignment passes through the aperture stop 23 while being focused by the condenser lens 22 and is guided to the pinhole plate 24. Then, the light beam that has passed through the pinhole plate 24 is reflected by the dichroic mirror 25, converted into a parallel light beam by the projection lens 26, reflected by the half mirror 15, and then transmitted through the chamber window glass 14 to the airflow blowing nozzle 12. Passing through the interior, XY alignment index light K is formed as shown in FIG. In FIG. 3, the XY alignment index light K is reflected on the corneal surface T so as to form a bright spot image R at an intermediate position between the apex P of the cornea C and the center of curvature of the cornea C. The aperture stop 23 is provided at a position conjugate with the corneal apex P with respect to the projection lens 26.
[0019]
As shown in FIG. 7, the germicidal light optical system 30 includes a germicidal light source 31 that emits ultraviolet light, a pinhole plate 32, a dichroic mirror 25, a projection lens 26, a half mirror 15, a chamber window glass 14, an air blowing nozzle 12, An anterior window glass 13 is provided.
[0020]
The bactericidal light emitted from the bactericidal light source 31 passes through the pinhole plate 32 and the dichroic mirror 25, becomes a light beam having a predetermined spread by the projection lens 26, is reflected by the half mirror 15, and then passes through the chamber window glass 14. The light passes through and passes through the inside and outside of the airflow spray nozzle 12 and the anterior ocular window glass 13.
[0021]
The XY alignment detection optical system 40 includes an airflow spray nozzle 12, a chamber window glass 14, a half mirror 15, an objective lens 16, half mirrors 17 and 18, a sensor 41, and an XY alignment detection circuit 42.
[0022]
The reflected light beam projected onto the cornea C by the XY alignment index projection optical system 20 and reflected by the cornea surface T passes through the nozzle 12, passes through the chamber window glass 14 and the half mirror 15, and is focused by the objective lens 16. A part of the light is transmitted by the half mirror 17 and a part of the light is reflected by the half mirror 18. The light beam reflected by the half mirror 18 forms a bright spot image R ′ 1 on the sensor 41. The sensor 41 is a light receiving sensor capable of detecting a position such as a PSD. The XY alignment detection circuit 42 calculates the positional relationship (XY direction) between the measurement unit S and the cornea C based on the output of the sensor 41 by a known means, and the calculation result is a Z alignment detection correction circuit 74 and a control circuit. Output to 80.
[0023]
On the other hand, the light flux reflected by the cornea C that has passed through the half mirror 18 forms a bright spot image R ′ 2 on the CCD camera 19. The CCD camera 19 outputs an image signal to the monitor device, and as shown in FIG. 4, the anterior segment image E ′ of the eye E and the bright spot image R′2 of the XY alignment index light are displayed on the screen G of the monitor device. Is done. H is an alignment auxiliary mark generated by an image generation means (not shown).
[0024]
Further, a part of the light beam reflected by the half mirror 17 is guided to the corneal deformation detection optical system 50, passes through the pinhole plate 51, and is guided to the sensor 52. The sensor 52 is a light receiving sensor capable of detecting the amount of light such as a photodiode.
[0025]
The Z alignment index projection optical system 60 is arranged on the optical path so as to be in focus with the Z alignment light source 61 that emits infrared light, the condenser lens 62, the aperture stop 63, the pinhole plate 64, and the pinhole plate 64. Projection lens 65, and O2 is its optical axis.
[0026]
Infrared light emitted from the Z alignment light source 61 passes through the aperture stop 63 while being condensed by the condenser lens 62 and is guided to the pinhole plate 64. The light beam that has passed through the pinhole plate 64 is converted into parallel light by the projection lens 65, guided to the cornea C, and reflected on the cornea surface T so as to form a bright spot image Q as shown in FIG. The aperture stop 63 is provided at a position conjugate with the corneal apex P with respect to the projection lens 65.
[0027]
The Z alignment detection optical system 70 includes an imaging lens 71, a cylindrical lens 72 having power in the Y direction, a sensor 73, and a Z alignment detection correction circuit 74, and O3 is the optical axis thereof.
[0028]
The reflected light beam on the cornea surface T of the index light projected by the Z alignment index projection optical system 60 forms a bright spot image Q ′ on the sensor 73 via the cylindrical lens 72 while being focused by the imaging lens 71. The sensor 73 is a light receiving sensor capable of detecting a position, such as a line sensor or PSD. Information from the sensor 73 is guided to the Z alignment detection correction circuit 74.
[0029]
In the XZ plane, the bright spot image Q and the sensor 73 are conjugated with respect to the imaging lens 71, and the corneal apex P and the sensor 73 are conjugated with respect to the imaging lens 71 and the cylindrical lens 72 in the YZ plane. Are in a good positional relationship. That is, the sensor 73 is in a conjugate relationship with the aperture stop 63 (the magnification at this time is selected so that the image of the aperture stop 63 is smaller than the size of the sensor 73), and the cornea C even if the cornea C is displaced in the Y direction. The reflected light beam on the surface T enters the sensor 73 efficiently. Also, a similar effect can be obtained by projecting long slit light in the Y direction, although the efficiency is lowered.
[0030]
By the way, in the present embodiment, as shown in FIG. 1, the projection system and the light receiving system for detecting the alignment in the Z direction are the Z alignment index projection optical system 60 and the Z alignment detection optical system 70. It is provided one by one. In such a configuration, the XY alignment information from the XY alignment detection circuit 42 is input to the Z alignment detection correction circuit 74 in order to accurately detect the alignment in the Z direction without being affected by the alignment deviation in the XY direction. I have to.
[0031]
That is, as shown in FIG. 6A, when the position of the cornea C is shifted by ΔZ in the Z direction, the position of the bright spot image Q ′ moves on the sensor 73 by ΔZ × sin θ × m. Here, θ is an angle formed by the axis O1 and the axis O2, and the axis O1 and the axis O3, and m is an imaging magnification of the Z alignment optical system 70. If the cornea C is only shifted in the Z direction, the shift amount of the cornea C can be easily calculated from the movement amount of the bright spot image Q ′ on the sensor 73.
[0032]
However, as shown in FIG. 6B, even when the position of the cornea C is shifted by ΔX in the X direction, the position of the bright spot image Q ′ moves on the sensor 73 by ΔX × cos θ × m. Therefore, when there is a shift in the Z direction and the X direction, the Z alignment detection correction circuit 74 causes the shift amount ΔQ ′ from the reference position of the bright spot image Q ′ on the sensor 73 and the shift amount from the XY alignment detection circuit 42. Based on ΔX, the positional relationship (deviation amount ΔZ) between the measurement unit S and the cornea C in the Z direction is calculated based on the following equation 1, and the calculation result is output to the control circuit 80.
[0033]
ΔZ = (ΔQ′−ΔX × cos θ × m) / (sin θ × m) (1)
Then, the examiner observes the anterior segment image E ′ on the monitor screen shown in FIG. 4 and moves the measurement unit S so that the bright spot image R′2 enters the alignment auxiliary mark H and is in focus. It is moved manually in the XYZ directions to adjust the alignment. At this time, when the outputs of the XY alignment detection circuit 42 and the Z alignment detection correction circuit 74 fall within a predetermined range, the control circuit 80 operates an air blowing means (not shown) from the air blowing nozzle 12 toward the cornea C. An airflow is blown, and the corneal deformation amount at that time is detected by the corneal deformation detection optical system 50. Then, the intraocular pressure value of the eye E is obtained from the airflow blowing pressure when the predetermined deformation amount is reached.
[0034]
The alignment state between the measurement unit S and the eye E is detected based on the XY alignment information output from the XY alignment detection circuit 42 and the Z alignment information output from the Z alignment detection correction circuit 74, and the detection result is obtained. It can also be configured to display on a CRT or the like.
[0035]
Next, when sterilizing light is irradiated when the measurement of one day is completed, a protective cap 91 is attached to the hardware mounting portion 92 of the airflow spray nozzle 12 as shown in FIG. The hardware mounting portion 92 is finished in a shape in which the protective cap 91 is fitted. On the inner surface of the protective cap 91, a planar reflecting portion 93 corresponding to the shape of the cornea when the cornea is flat is formed.
[0036]
After attaching the protective cap 91 to the hardware mounting portion 92, the examiner operates a mode switching switch (not shown) to switch the mode from the measurement mode to the germicidal beam irradiation mode.
[0037]
Then, as shown in FIG. 8, the XY alignment light source 21 emits light, and the XY alignment index light K is guided to the flat reflecting portion 93 of the protective cap 91, and the reflected light is the nozzle 12, the chamber window glass 14, and the half mirror. 15 is guided to the objective lens 16, is reflected by the half mirror 17 while being focused by the objective lens 16, and is guided to the sensor 52 as the detection means via the pinhole plate 51. The sensor 52 is also used for corneal deformation detection, and the detection signal of the sensor 52 is input to the determination means 50A of the corneal deformation detection means 50. The determination means 50A is also used for determination of corneal deformation and sterilization light irradiation stop. When reflected light having a light amount greater than or equal to a predetermined value is incident on the sensor 52, the sensor 52 outputs a detection signal greater than or equal to the predetermined value, whereby the determination means 50A determines that the output of the detection signal is greater than or equal to the predetermined value, The sterilizing light source 31 of the projection optical system 30 is turned on, and the sterilizing light is intensely applied to the inside and outside of the chamber window glass 14, the anterior ocular window glass 13, and the nozzle 12, thereby sterilizing these optical members.
[0038]
When the protective cap 91 is removed, the amount of reflected light incident on the sensor 52 is attenuated, and the detection signal of the sensor 52 becomes less than a predetermined value, whereby the germicidal light source 31 of the germicidal light projection optical system 30 is turned off. At the same time, the examiner is informed that the light source 31 for bactericidal light 31 is turned off by a notification means such as a buzzer.
[0039]
Note that a timer may be provided so that the germicidal light source 31 is automatically turned off after being turned on for a certain time.
[0040]
Further, even in the normal measurement mode, the positional relationship between the eye cornea to be examined and the measurement unit S is detected based on information from the Z alignment detection correction circuit 74 as a measuring unit, and sterilized according to the distance from the eye cornea S to be examined. If it is set as the structure which irradiates and stops the germicidal light source 31 of the light projection optical system 30, a high germicidal effect can be acquired. Further, a light amount changing means for changing the lighting amount of the germicidal light source 31 in accordance with the distance between the eye cornea to be examined and the apparatus main body S may be provided. For example, when it is configured to increase the amount of germicidal light as the distance between the cornea of the eye to be examined and the apparatus main body S increases, the sterilizing effect can be enhanced while ensuring safety.
[0041]
A microswitch mechanism is provided in a so-called well-known gantry unit (not shown) that allows the measurement unit S to be moved back and forth, up, down, left and right with respect to the eye to be examined. It is good also as a structure which detects by a microswitch mechanism and maximizes the irradiation light quantity of germicidal light.
(Embodiment 2)
Next, a second embodiment of the present invention will be described. In the first embodiment described above, the examiner manually adjusts the measurement unit S in the XYZ directions to perform alignment adjustment. On the other hand, in the present embodiment, an automatic movement mechanism for driving the measurement unit S in the XYZ directions is provided, and the alignment adjustment is automatically performed.
[0042]
FIG. 9 is a side view showing the overall configuration of the ophthalmologic apparatus of the present invention, and 100 is a base with a built-in power supply. A gantry 101 is provided on the upper part of the base 100 so as to be movable back and forth and left and right by operating a control lever 102. The control lever 102 is provided with a manual switch 103, and this manual switch 103 is used in the manual mode. A motor 104 and a support column 105 are provided on the top of the gantry 101. The motor 104 and the column 105 are coupled by a pinion rack (not shown), and the column 105 is moved in the vertical direction (Y direction) by the motor 104. A table 106 is provided at the upper end of the column 105.
[0043]
The table 106 is provided with a column 107 and a motor 108. A table 109 is slidably provided at the upper end of the support column 107. A rack 110 is provided at the rear end of the table 109 as shown in FIG. A pinion 111 is provided on the output shaft of the motor 108, and the pinion 111 is meshed with the rack 110. In addition, a motor 112 and a support column 113 are provided on the top of the table 109. A pinion 114 is provided on the output shaft of the motor 112. An apparatus main body case 115 is slidably provided on the upper portion of the column 113. A rack 116 is provided on the side of the apparatus main body case 115. The rack 116 is engaged with the pinion 114. Note that the optical system shown in FIGS. 1 and 2 is housed inside the apparatus main body case 115.
[0044]
The motors 104, 108 and 112 are controlled by a control signal output from the control circuit 80 described above. The apparatus body case 115 is moved in the Y direction when a control signal is output to the motor 104, moved in the X direction when a control signal is output to the motor 108, and the control signal is output to the motor 112. In some cases, the movement in the Z direction is controlled, whereby the alignment adjustment is performed automatically.
[0045]
In this device, after the measurement unit S is automatically aligned and measured, the measurement unit S is automatically moved away from the eye cornea to be examined, and the germicidal light source 31 of the germicidal light projection optical system 30 is turned on for a predetermined time.
[0046]
If a rotation mechanism is provided so that the apparatus main body case 115 automatically faces downward with respect to the eye when the measuring unit S is automatically moved away, unnecessary germicidal rays are emitted to the eye to be examined. It is preferable in terms of safety without irradiation.
[0047]
【The invention's effect】
As described above, according to the present invention, the mechanical structure of the sterilizing light generating means is not complicated, and it is easy even if it is configured to perform sterilization frequently each time between measurements. In addition, the measurement unit can be sterilized while maintaining safety.
[Brief description of the drawings]
FIG. 1 is a configuration diagram of a main part of an optical system of an ophthalmologic apparatus according to the present invention, and a plan layout view thereof.
FIG. 2 is a main part configuration diagram of an optical system of an ophthalmologic apparatus according to the present invention, and is a side layout view thereof.
FIG. 3 is an explanatory diagram of the reflection of the alignment light beam irradiated on the cornea from the front.
FIG. 4 is a diagram showing an anterior segment image displayed on a monitor screen.
FIG. 5 is an explanatory diagram of the reflection of the alignment light beam irradiated on the cornea from an oblique direction.
FIGS. 6A and 6B are diagrams showing an incident / reflection relationship of a light beam when the position of the cornea is shifted, where FIG. 6A is an explanatory diagram when the cornea is shifted in the Z direction, and FIG. FIG.
FIG. 7 is a side view showing a germicidal light generating means of the ophthalmic apparatus according to the present invention.
FIG. 8 is a view showing a state in which a protective cap is attached to the ophthalmologic apparatus according to the present invention.
FIG. 9 is a side view showing the overall arrangement of the ophthalmic apparatus according to the present invention.
FIG. 10 is a plan view showing a main part of an ophthalmologic apparatus according to the present invention.
[Explanation of symbols]
DESCRIPTION OF SYMBOLS 10 Anterior ocular segment observation optical system 20 XY alignment index projection optical system 30 Sterilization light generation means 40 XY alignment detection optical system 52 Sensor (detection means)
80 Control circuit C Cornea E Eye to be examined S Measuring unit

Claims (2)

In an ophthalmologic apparatus provided with a bactericidal light generating means in a measurement part that is separated and approached to the eye to be examined,
An ophthalmology comprising: a detecting unit that detects reflected light of a light beam projected from the measuring unit; and a determining unit that determines whether or not to activate the bactericidal beam based on information of the detecting unit apparatus.   The ophthalmologic apparatus according to claim 1, wherein the detection unit also serves as a corneal deformation detection unit that detects a deformation of the cornea.

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