JP3199779B2 - Intraocular photocoagulation device - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to the use of heat of light.
The present invention relates to an intraocular photocoagulation device for coagulating an affected part in an eye .

[0002]

2. Description of the Related Art A treatment light from a light source for photocoagulation is supplied to a light cage.
2. Description of the Related Art There is known an apparatus for guiding photocoagulation by guiding light to a probe through a probe and radiating the guided therapeutic light from a tip attached to the tip of the probe. In an ophthalmic apparatus, a probe is inserted into a surgical eye and irradiated from the probe tip toward an affected area to coagulate an affected area such as a retina. In this device, when the visible light is used as the treatment light, the reduced treatment light is used as the guide light, and when the invisible light is used as the treatment light, the visible light is coaxial with the treatment light and used as the aiming light. are doing. The illumination light is separately guided to a light cable to illuminate the eye.

[0003]

However, in the above-mentioned apparatus, it is necessary to separately provide a wound in order to insert a light cable for illumination into the eye. Further, in order to illuminate the entire area requiring observation, it is necessary to change the illumination position, which requires an extremely cumbersome operation. further,
Generally, red light such as a He-Ne laser is used as the aiming light. However, when observing a red portion such as the fundus, there is a problem that the red light is difficult to observe.

The present invention has been made in view of the above circumstances, and it is an object of the present invention to provide a photocoagulation apparatus that provides aiming light that can be easily observed without providing a new opening for illumination.

[0005]

To achieve the above object, the apparatus of the present invention has the following features. (1) The treatment light from the light source for photocoagulation is guided to the probe via the light cable, and the guided treatment light is emitted from the tip attached to the probe tip to perform photocoagulation. Eye to do
In the inner photocoagulation apparatus, the illumination light from the illumination light source Rights
Illuminate the aperture from behind to change the size of the luminous flux in rows
Illumination light beam adjusting means, and the illumination light beam passing through the aperture
A synthetic optical member for coaxially synthesizing the therapeutic light, and the synthetic optical member;
The treatment light and the illumination light synthesized by the members are transmitted to the light case.
And a condenser lens to make the light incident on the
The feature is that there is no need to establish a new wound .

(2) The composite optical member of (1) is a dichroic
It is characterized by being an Ick Mirror.

(3) The therapeutic light of (1) is visible Amin.
It is characterized by being coaxial with the
You.

(4) In the illumination light flux adjusting means of (1)
The stop can change the angle of incidence on the probe.
And changing the emission angle radiated from the chip by
Features.

(5) The illumination light flux adjusting means of (1)
Features a reference mark for specifying the launch position
And

(6) Synthetic optical member and illumination light of (1)
The bundle adjusting means is separated from the main body containing the light source for photocoagulation.
The treatment light is placed in a light cable.
The light is guided to the adapter.

[0011]

[0012]

[0013]

[0014]

Embodiments of the present invention will be described below with reference to the drawings. FIG. 1 is an external perspective view showing a main body of the ophthalmologic photocoagulation apparatus of the present embodiment. Reference numeral 1 denotes a coagulation apparatus main body in which a semiconductor laser (800 nm) or a He-Ne laser (632.8 nm) as a light source for coagulation is housed. Although the He-Ne laser is not indispensable, it may be used as aiming light when the solidified portion is not red, or may be arranged in consideration of safety when the semiconductor laser leaks outside. I have. Since the optical system of the main body may have a known configuration, a detailed description thereof will be omitted (for example, Japanese Patent Application No. 63-62227). Light emitted from a semiconductor laser which is a coagulation laser light source disposed in the body is converted into a parallel light beam through a collimating lens and a cylindrical lens, and then combined with aiming light by a dichroic mirror. (The aiming light is incident on the dichroic mirror at a predetermined angle so that the beam emitted from the fiber is coaxial between the aiming light and the semiconductor laser). Thereafter, the light is condensed and incident on one end of the light cable 11 via the fiber connector 6.

Various switches for operation are provided on the front panel of the coagulation apparatus main body 1. A key switch 2 activates the apparatus. Reference numeral 3 denotes a coagulation switch, which is one of the safety devices. When the coagulation switch 3 is turned on, a safety shutter (not shown) on the optical path moves out of the optical path. 4 is a coagulation time display section. Reference numeral 5 denotes a laser emission indicator, which is always illuminated red while the laser can be emitted, and the waiting time from when the key switch 2 is turned on to when the apparatus is in the initial state. Blinks when an error occurs in the device. Reference numeral 6 denotes a fiber connector, which guides laser light from the apparatus main body 1 to the outside by inserting a write cable. Reference numeral 7 denotes a coagulation output display unit, and reference numeral 8 denotes a coagulation output knob for setting a coagulation output. 9
Reference numeral denotes an aiming brightness display section of an aiming generator incorporated in the main body, and reference numeral 10 denotes an aiming brightness adjustment switch on the main body side.

Reference numerals 11, 12, and 13 denote write cables. Reference numeral 14 denotes a lighting power supply box for storing a halogen lamp (not shown), reference numeral 15 denotes a power switch, and reference numeral 16 denotes a brightness adjustment volume. The light beam emitted from the halogen lamp 14 enters one end of the light cable 12 and is guided to the adapter 17. Reference numeral 18 denotes an aperture switching knob for operating an aperture for adjusting a light flux width of illumination light, which will be described later. 19 is a probe for operation.

Next, the optical system in the adapter 17 will be described with reference to the layout of the optical system shown in FIG. Reference numeral 20 denotes a lens having a front focal length at the exit end of the write cable 11, and converts the semiconductor laser light and the He-Ne laser light emitted from the exit end of the write cable 11 into parallel light beams. Reference numeral 21 denotes a dichroic mirror having a property of transmitting light having a wavelength of about 600 nm or more and reflecting light having a wavelength smaller than 600 nm. 22
Is a lens having a rear focal length at the incident end of the light cable 13 and focuses a parallel light beam incident on the lens 22 to the incident end of the light cable 13. 23 is a light cable 12
Is a lens having a front focal length at the exit end of the light cable 12, and converts the halogen light emitted from the exit end of the light cable 12 into a parallel light flux. Reference numeral 24 denotes a diaphragm having a variable aperture, which is switched by operating a diaphragm switching knob 18. The iris 24 may be mechanically connected to the iris switching knob 18 or may be electrically driven. Generally, when halogen light is used for illumination, the luminous flux is made larger than the laser light, and the divergence angle emitted from the tip of the probe 19 is made larger than that of the laser. When halogen light is used as the aiming light, the size of the light should be substantially the same as that of the laser light. However, the present invention is not necessarily limited to this, and switching may be performed in multiple stages in connection with necessary adjustment of luminance and light amount.

Next, the operation of the apparatus of this embodiment will be described. First, the key switch 2 is turned on, and the coagulation conditions are set by operating the switches on the panel. Subsequently, the power switch 15 and the volume 16 of the lighting power supply box 14 are operated to emit the light of the halogen lamp . Aperture switching knob 1
Reference numeral 8 denotes the position of the lighting mode. Light from the halogen lamp enters the adapter 17 through the light cable 12.
The halogen lamp emitted from the emission end of the light cable 12
After the light of the pump is converted into a parallel light beam by the lens 23 , the light is stopped by the stop 24 for illumination. Thereafter, the light is reflected by the dichroic mirror 21 and condensed by the lens 22 to enter the light cable 13 and is emitted from the tip of the probe 13 to illuminate the fundus of the surgical eye. When the coagulation switch is turned on and a safety shutter (not shown) is moved out of the optical path, laser irradiation can be performed.

When the affected part is found, the diaphragm 24 is driven by the diaphragm switch 18 to reduce the spread angle of the illumination light and use it as aiming light. By stepping on a foot switch (not shown) connected to the coagulation apparatus main body 1, the coagulation shutter is moved out of the optical path, and the laser light is emitted to the light cage.
Optical system of cable 11, adapter 17, light cable 13
Irradiates the affected area through the coagulation.

In the above embodiment, the adapter 17 is provided,
Here, the laser and the illuminating light are made coaxial to improve the operability. However, a laser incorporated in the main body can also be used. Aperture 2
4 can be modified by providing a plurality of spots to clarify the irradiation position, and it is needless to say that these modifications are included in the present invention as long as the technical idea is the same.

[0021]

According to the present invention, the treatment light and the illumination light beam are
In order to use one light cable coaxially synthesized,
There is no need to create new openings for lighting .

[Brief description of the drawings]

FIG. 1 is an external perspective view of a photocoagulation device according to an embodiment.

FIG. 2 is an optical system layout diagram of an adapter.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Coagulation apparatus main body 11, 12, 13 Light cable 14 Lighting power supply box 17 Adapter 19 Probe 20, 22, 23 Lens 21 Dichroic mirror 24 Aperture

Claims (6)

(57) [Claims] A treatment light from a photocoagulation light source is guided to a probe through a light cable, and the guided treatment light is emitted from a tip attached to the probe tip to perform photocoagulation. Illumination light from an illumination light source in an intraocular photocoagulation device
Behind an aperture that changes the size of the light beam by making the beam parallel
Light flux adjusting means for illuminating the illumination light, and illumination light passing through the aperture
A synthetic optical member for coaxially synthesizing the bundle with the treatment light;
The treatment light and the illumination light synthesized by the
And a condenser lens for entering the cable.
It is not necessary to establish a new opening for
Intraocular photocoagulation device. 2. The composite optical member according to claim 1, wherein
An intraocular photocoagulation device, which is a cumilla. 3. The treatment light according to claim 1, wherein said treatment light is visible aiming light.
Intraocular light coagulation characterized by being made coaxial with
Fixing device. 4. The illumination light beam adjusting means according to claim 1,
The diaphragm changes the angle of incidence on the probe.
It is characterized by changing the emission angle radiated from the chip
Intraocular photocoagulation device. 5. An illumination light flux adjusting means according to claim 1, wherein
A reference mark for specifying the location.
Intraocular photocoagulation device. 6. A composite optical member according to claim 1, wherein the illumination light flux is adjusted.
The adjusting means is separated from the main body containing the light source for photocoagulation.
The treatment light is placed in the adapter
Intraocular photocoagulation characterized by being guided by the adapter
apparatus.