JPH04212342A - Intraocular illuminating device - Google Patents

Abstract

PURPOSE:To facilitate the observation of the vitreous body and to allow optimum observation without having a need for bringing the tip of a probe near to the retina by using a light source which emits luminous fluxes contg. the short wavelength side of a visible region at a relatively high rate and forming a freely attachable and detachable attenuation filter and conversion filter of wavelength spectral characteristics. CONSTITUTION:The light emitted from a xenon lamp 11 fixed in a lamp house is reflected by an elliptical mirror 12 and is converted to a spot diaphragm 13. A collimator lens 14 having a front side focal position exists in the position of the spot diaphragm 13 and the light past the spot diaphragm 13 is collimated to collimated luminous fluxes. Turrets 15, 16 which can attach and detach the filter for light control are disposed in the filter case 4.

Description

[Detailed description of the invention]

0001

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an apparatus for directly guiding illumination light from a light source into the eye via an optical fiber to illuminate the inside of the eye, which is used in vitrectomy and the like.

0002

BACKGROUND OF THE INVENTION It goes without saying that in ophthalmic surgery, lighting is essential to ensure an appropriate surgical field. Therefore, in order to avoid deterioration in visibility due to interface reflections between the cornea and crystalline lens, intraocular illumination devices have become popular, in which the illumination light from a light source is first input into an optical fiber, and the illumination light is directly guided into the eye via the optical fiber. are doing. Intraocular illumination devices that are currently in widespread use use halogen lamps as light sources, taking into consideration the harmful effects of ultraviolet rays and blue light on the fundus of the eye.

0003

[Problems to be Solved by the Invention] However, the above-mentioned conventional apparatus is extremely difficult to use, as the amount of illumination light is lowered than necessary due to concerns about the effects of phototoxicity. In particular, the vitreous body has the problem of being difficult to observe because it transmits most of the light in the visible range unless it is opaque.

Furthermore, it has been pointed out that even though the amount of illumination itself is low, with intraocular illumination devices, if the tip of the probe is placed too close to the retina, the amount of irradiation per unit tissue becomes high, which poses a problem of phototoxicity. has been done.

Furthermore, conventional devices attempt to observe various intraocular tissues using a single type of illumination. However, it is known that the intraocular tissue is not made up of uniform tissue, and that each region exhibits special optical characteristics. A monochromatic fundus photographing method is known as an examination method that utilizes such differences in optical properties of tissues. For diseases discovered through such special observation, the surgeon has no choice but to perform surgery based on his or her memory after identifying the disease location through preoperative examination and determining the surgical site. There was an inconvenience that it could not be confirmed.

In view of the above-mentioned drawbacks of the prior art, a first object of the present invention is to provide an intraocular illumination device that allows easy observation of the vitreous body and does not require the tip of the probe to be brought close to the retina. be. A second purpose is to provide an intraocular illumination device that allows optimal observation depending on the characteristics of the observation site.

[0007]

Means for Solving the Problems In order to achieve the above object, the intraocular illumination device of the present invention has the following features. (1) In an intraocular illumination device that illuminates the inside of the eye by directly inserting light from a light source into the eye via an optical fiber, the light source is a light source that emits a light beam that contains a relatively large amount of light on the short wavelength side of the visible range. In addition, it is characterized in that the neutral density filter and the conversion filter for wavelength spectral characteristics are detachable.

(2) The wavelength spectral characteristic conversion filter of (1) is characterized in that it is an ultraviolet cut filter.

(3) The wavelength spectral characteristic conversion filter of (1) is characterized in that it includes a yellow filter.

(4) The wavelength spectral characteristic conversion filter of (1) is characterized in that it includes a red filter and a green filter.

(5) The wavelength spectral characteristic conversion filter of (1) is characterized in that it includes a fluorescence filter.

(6) The light source in (1) is characterized in that it is a xenon lamp light source.

[0013]

[Operations and Effects] The present invention focuses on the fact that the vitreous body is inherently highly transparent and only reflects visible light in a slightly short wavelength range.
Since a light source that emits a considerable amount of light in the visible range on the short wavelength side is selected as the illumination light source, it is possible to perform appropriate surgery in a short time while easily observing the vitreous body without bringing the probe tip close to the fundus of the eye. can. In addition, since a high-intensity illumination light source is used, it is possible to obtain sufficient illumination for observation even if a conversion filter with wavelength spectral characteristics is installed, so it can be used appropriately according to the characteristics of the observation site.
It is effective in surgery for early stage diseases. Furthermore, there is no need to use a neutral density filter to irradiate the surgical eye with unnecessarily strong light for a long period of time.

Furthermore, phototoxicity can be suppressed by providing an ultraviolet cut filter.

[0015] Further, by making the yellow filter removable and suppressing light on the short wavelength side of the visible range, observation of the fundus becomes easier.

Furthermore, since a light source that emits a considerable amount of light in the visible range on the short wavelength side is selected as the illumination light source, fluorescence observation of the fundus of the eye is made possible by providing a fluorescence filter.
Fundus surgery can be performed while observing fluorescence.

[0017]

[Embodiment] An embodiment of the present invention will be explained based on the drawings. FIG. 1 is an external view of one embodiment of the present invention, and FIG. 2 is a layout diagram of the optical system of the apparatus shown in FIG.

In FIG. 1, 1 is a lamp house;
It is supported by the lamp stand 2. The lamp house 1 supports a filter case 4 that holds a filter to be described later. Reference numeral 5 denotes a connector for placing the illumination light transmitted through the filter case 4 and the optical axis of the light cable 7 in a predetermined positional relationship, and for efficiently inputting the illumination light into the light cable 7. In this embodiment, Super Esca SK-30 manufactured by Mitsubishi Rayon is used as the light cable. In the case of a xenon lamp, due to its structure, by making the illumination light enter the light cable 7 at a slight angle,
It is possible to provide almost uniform illumination without hollow areas. Reference numeral 6 denotes a probe, the tip of which is inserted into the eye as a stainless steel pipe. In addition, with this device, sufficient brightness can be obtained on the retinal surface even when illuminated from 20 mm above, so a flange-like object is attached to the part inserted into the eye, although it is not shown in the figure. By fixing the flange and sclera with thread, a fixed illumination fiber can be created, making the surgery easier. 3 is a control unit for adjusting the output of the device and selecting a filter.

The optical system layout of this embodiment is shown in FIG. 2, and a xenon lamp 11 as a light source is fixed inside the lamp house 1. In this embodiment, UXL-301D-0 manufactured by Ushio Inc. is used as a xenon light source. The light emitted from this light source is reflected by an elliptical mirror 12 and converged on a spot aperture 13. Reference numeral 14 denotes a collimator lens whose front focal point is located at the spot diaphragm 13, and the light passing through the spot diaphragm 13 becomes a parallel beam of light. Two turrets for attaching and detaching the dimming filter are arranged within the filter case 4. 1 turret 15
1/2, which changes the light intensity without changing the wavelength characteristics,
ND filters of 1/4, 1/8, 1/16, etc. and simple apertures are arranged. The other turrets 16 include conversion filters for wavelength spectral characteristics, i.e., an ultraviolet cut filter that cuts ultraviolet rays, a yellow filter that makes the spectral characteristics similar to a halogen light source, an excitation light filter for fluorescence contrast, and a filter that reduces reflected light at the fundus. A filter or the like is arranged to relatively increase the amount of light on the short wavelength side. Note that in intraocular illumination, it is desirable to block ultraviolet rays with a wavelength of 400 nm or less, so in devices that do not use ultraviolet rays for observation, applying a UV blocking coating to the collimator lens 14 and condensing lens 18 can block ultraviolet rays. The cut filter may be fixedly arranged. Note that it is not essential that these filters be placed on the turret. 17 is a heat ray absorption filter, and 18 is a condensing lens.

The optical characteristics of the illumination light obtained from the intraocular illumination device configured as described above will be explained. As mentioned above, when UXL-301D-0 manufactured by Ushio Inc. is used as the xenon light source and Super Esca SK-30 manufactured by Mitsubishi Rayon is used as the light cable, the illuminance obtained at a position 10 mm from the tip of the cable is 58600. In terms of lux, approximately 16 times the illuminance was obtained compared to halogen. I changed the type of light cable and measured the illuminance in the same way, but
Almost the same high illuminance was obtained. The solid line in FIG. 3 shows the relative spectral characteristics without the ND filter. The peak wavelength at this time is 470 nm. The dotted line in Figure 3 is ND
In the relative spectral characteristics without a filter, it can be seen that compared to xenon light, there are characteristics on the short wavelength side.

The results observed using the above apparatus are shown below. When the vitreous was observed without a 1/2, 1/4, 1/8, 1/16 or ND filter, the vitreous and proliferative membranes were clearly observed, and the border with the retinal tissue was easier to see, making it possible to perform vitreous surgery. has become extremely easy. In addition, it has become possible to observe vitreous surgery using a video system attached to a conventional surgical microscope, making it possible to explain the procedure to trainee doctors and others. This result is due to the fact that the vitreous body only reflects visible light in the short wavelength range, so the xenon light source has a high absolute light intensity in the short wavelength range, and the relative spectral characteristics of the short wavelength range are high. It is understood that this is because it enhances sexuality. Even when the test was conducted without an ND filter, no results that could be considered to be caused by phototoxicity have been obtained so far. Note that in order to emphasize light on the shorter wavelength side, it is also effective to cut off light in a slightly longer wavelength range.

When I observed the fundus of the eye using this device without an ND filter, I found myself rather tired due to the effects of light scattered by the vitreous body and because it was too bright. To observe the retina, I used a yellow filter that suppresses the short wavelength side, and it was easiest to observe when the light intensity was reduced to a 1/4 ND filter.

[0023] Using a fluorescence contrast excitation light filter (a bandpass filter that transmits around 470 nm) of a commercially available fluorescence fundus camera, the eye to be examined to which the fluorescent agent has been administered is observed. I could understand it clearly. However, with a 1/16ND filter or less, it was too dark to confirm fluorescence. Note that if a barrier filter is used for the eye to be examined, it becomes difficult to see the fundus itself, so there is no need to use a barrier filter for observation.

Observation was made using a green filter (No. 58) and a red filter (No. 29) manufactured by Kodak. With the former green filter, it was possible to observe the nerve fiber layer, loss of macular pigment, and the presence of cysts. Furthermore, with the latter red filter, choroidal blood vessels could be clearly observed.

[Brief explanation of the drawing]

FIG. 1 is an external view of an intraocular illumination device according to an embodiment of the present invention.

FIG. 2 is an optical layout diagram.

[Fig. 3] Relative spectral characteristics diagram of xenon lamp, halogen lamp, and vitreous body.

[Explanation of symbols]

11 Light source

Claims (6)

[Claims] 1. An intraocular illumination device that illuminates the inside of the eye by directly inserting light from a light source into the eye via an optical fiber, wherein the light source is a light source that emits a light beam containing a relatively large amount of light on the short wavelength side of the visible range. An intraocular illumination device characterized in that a neutral density filter and a conversion filter for wavelength spectral characteristics are detachable. 2. An intraocular illumination device, wherein the wavelength spectral characteristic conversion filter according to claim 1 includes an ultraviolet cut filter. 3. An intraocular illumination device, wherein the wavelength spectral characteristic conversion filter according to claim 1 includes a yellow filter. 4. An intraocular illumination device, wherein the wavelength spectral characteristic conversion filter according to claim 1 includes a red filter and a green filter. 5. An intraocular illumination device, wherein the wavelength spectral characteristic conversion filter according to claim 1 includes a fluorescence filter. 6. An intraocular illumination device, wherein the light source according to claim 1 is a xenon lamp light source.