JPH07250862A - Laser probe - Google Patents

Abstract

PURPOSE:To prevent the diffusion of laser beam in a laser probe for medical treatment and to condense the energy of the laser beam to a desired position. CONSTITUTION:The leading end 5 of a light guide fiber 4 is embedded in an optical glass part 3 and laser beam is emitted from the light guide fiber 4. This laser beam is reflected by a mirror surface 6 to form a focus f1 at the position separated from the end surface of the optical glass part 3 by a focal distance (a).

Description

Detailed Description of the Invention

[0001]

This invention relates to a laser probe,
Particularly, it relates to a laser probe suitable for a laser coagulation apparatus for ophthalmology.

[0002]

2. Description of the Related Art In recent years, laser coagulation devices have come to be widely used for ophthalmic surgery, for example, coagulation surgery of the posterior segment of the eye. An example of a laser probe used in such a laser coagulation apparatus is shown in FIGS.

7 and 8 show a hook-shaped laser probe 40. In this hook-shaped laser probe 40, as shown in FIG. 7, the tip portion 42 of the hook-shaped hand piece 41 is inserted into the posterior segment 43, and the surgical site of the posterior segment 43 is heated by irradiation of laser light. It solidifies with. Details of the tip portion 42 (arrow portion) are shown in FIG. In the configuration of FIG. 8, the laser probe 4
Reference numeral 0 is formed of a stainless pipe, and an opening 45 is formed at the tip 44 thereof, and a fixing piece 46 is attached to the opening 45. Then, a light guide fiber 47 (optical fiber) is guided into the laser probe 40 and fixed by the above-mentioned fixing piece 46. Light guide fiber 4
The laser beam L01 emitted from 7 is diffused as shown in FIG.

FIG. 9 shows a straight type laser probe 48. This straight type laser probe 4
Reference numeral 8 denotes a distal end portion 50 of the handpiece 49, which is inserted through the vitreous body 52 in the eyeball portion 51 to be positioned near the posterior segment 43 so that the laser light supplied from the light guide fiber 47 is applied to the posterior segment 4.
Irradiation is performed on the surgical site No. 3, and the surgical site is coagulated by the heating effect of laser light irradiation. Incidentally, 53 is a sclera.

[0005]

However, each of the above-mentioned various laser probes 40 and 48 has a problem, and improvement has been desired.

In the case of the hook-shaped laser probe 40,
Although the laser light L01 is directly irradiated from the light guide fiber 47, the sclera 53 has a problem that scattering and diffusion are intense and energy per unit area is small, and coagulation action is weakened. In particular, a semiconductor laser having a large diffusion angle has a problem that this influence is great. Moreover, when the energy level of the laser beam is increased to enhance the coagulation action, there is a problem that the surface of the sclera portion in contact with the fixing piece 46 is damaged.

In the case of the straight type laser probe 48, the tip of the light guide fiber 47 is exposed at the tip of the stainless steel pipe 54 of the handpiece 49, so that the diffusion angle of the semiconductor laser is different. There is a problem that large ones cannot be used. On the other hand, in the case of a thin beam such as a gas laser, there is a problem in that a part of the end face is heated, so that it may come in contact with the surface layer of the body tissue (for example, the retina).

Therefore, an object of the present invention is to provide a laser probe which can prevent the diffusion of laser light and concentrate the energy of laser light at a desired position.

[0009]

SUMMARY OF THE INVENTION The present invention relates to a hook type laser probe for irradiating an object with a predetermined laser beam, the end portion of which is fixedly held in the probe, and a laser beam from a laser source is used. It is composed of an optical fiber 4 for transmitting L11 and a mirror surface 6 for reflecting the laser light L11 transmitted by the optical fiber 4. The laser light L11 reflected by the mirror surface 6 is focused at a position apart from the tip of the probe by a predetermined distance. It is a laser probe that is tied.

[0010]

The laser light passes through the lens system and is focused at a position separated from the tip of the probe by a predetermined distance.
Therefore, the energy of the laser beam can be concentrated at a desired position to selectively heat a specific portion. Even a laser beam having a large diffusion angle such as a semiconductor laser can be prevented from being diffused, and the energy of the laser beam can be selectively and efficiently concentrated at a desired position.

[0011]

Embodiments of the present invention will be described below with reference to the drawings. In this embodiment, the present invention is applied to a probe for ophthalmic surgery as shown in FIGS. The description of this embodiment will be given in the following order. (A) About 1st Example (B) About 2nd Example (C) About 3rd Example

(A) First Embodiment In the first embodiment, the present invention is applied to a hook-shaped [Hook Type] laser probe. 1 and 2 show the tip of a hook-shaped laser probe.

In the configuration of FIG. 1, the laser probe 1
Is formed of a stainless pipe, and an optical glass portion 3 is attached to the tip portion 2 thereof. Optical glass part 3
The tip 5 of the light guide fiber 4 is embedded therein, and a mirror surface 6 corresponding to a concave mirror is formed by metal deposition.
The laser light L11 that enters the optical glass portion 3 from the light guide fiber 4 is reflected by the mirror surface 6 and emitted from the end surface 7 of the optical glass portion 3 as shown in FIG. At that time, the focal point f1 is formed at the position of the focal distance a from the end face 7.

FIG. 2 shows a modification of the first embodiment. Figure 2
In the above configuration, the laser probe 10 is formed of a stainless pipe, and an opening 11 is formed in the tip portion 2 thereof. A light guide fiber 4 is guided into the laser probe 10 and fixed by a fixing piece 12 at a position near the tip 2. A mirror 13 is fixed in the tip portion 2 of the laser probe 10, and an opening 1 is formed from the mirror 13.
A cylindrical lens, for example, a SELFOC lens 1 between 1
4 is fixed so that the reflected light from the mirror 13 can be received. The laser light L12 emitted from the light guide fiber 4 is reflected by the mirror 13 and is incident on the SELFOC lens 14 as shown in FIG. The laser light L12 is collimated by the SELFOC lens 14 and emitted. The laser light L12 is focused at the position of the focal length b from the end face 15 of the SELFOC lens 14.
It is designed to connect f2. The position of the focal point f2 is, for example, within the eyeball 17 beyond the sclera 16. The other contents are the same as the contents of FIG. 1 described above.

According to the first embodiment and the modified example, it is possible to prevent the diffusion of a laser beam having a large diffusion angle such as a semiconductor laser and to concentrate the energy of the laser beam at a desired position. Therefore, the scleral part 18
It is possible to selectively heat and solidify a specific portion inside the. As a result, the energy per unit area can be increased, and the laser light L11, L12 is unnecessarily increased.
It is not necessary to increase the output level of and the damage of the sclera part can be prevented.

(B) Second Embodiment In the second embodiment, the present invention is applied to a straight type laser probe. 3 and 4
Shows the tip of a straight type laser probe.

In the configuration of FIG. 3, the laser probe 2
1 is formed of, for example, a stainless steel pipe having a diameter of 20 G (gauge), and an opening 23 is formed at a tip 22 thereof. A light guide fiber 24 is introduced into the laser probe 21, and the fixing piece 2 is placed at a position near the tip 22.
It is fixed at 5. A SELFOC lens 26 is fixed in the tip portion 22 of the laser probe 21. Laser light L2 emitted from the light guide fiber 24
Enters the SELFOC lens 26 as shown in FIG. The laser light L2 is emitted from the SELFOC lens 26.
Is collimated into parallel light and emitted from the SELFOC lens 26. The laser light L2 is emitted from the SELFOC lens 26.
The focal point f3 is formed at the position of the focal length c from the end face 27 of the.

In this case, since the focal length c is comparatively short, the angle θ21 becomes large, and the energy concentration range can be narrowed. Therefore, only a limited depth [range] can be heated.

FIG. 4 shows a modification of the second embodiment. The configuration of FIG. 4 is different from the configuration of FIG. 3 in that the SELFOC lens 26 is moved toward the light guide fiber 24 side and fixed. Other configurations are the same as those in FIG. 3 described above. In this case, the focal length d is relatively
Since it becomes longer, the angle θ22 becomes smaller, and the range where energy is concentrated can be widened. Therefore, a rather wide range can be heated.

According to the second embodiment and the modified example, by changing the position of the SELFOC lens 26, the energy of the laser beam can be concentrated at a desired position to selectively heat a specific portion. it can. In addition, since the SELFOC lens 26 is not exposed at the opening 23, laser light having a large diffusion angle, such as a semiconductor laser, can be used while preventing diffusion, which may damage the surface layer of the body tissue. Can be made smaller.

The tip 22 of the laser probe 21
Can be attached to and detached from the main body of the handpiece 28.

(C) Third Embodiment In the third embodiment, the present invention is applied to a laser probe of wedge type. 5 and 6 show the tip of the wedge-shaped laser probe.

In the configuration of FIG. 5, the laser probe 3
1 is formed of, for example, a stainless pipe having a diameter of 20 G (gauge), and an optical chip 33 is attached to the tip portion 32 thereof. The tip 35 of the light guide fiber 34 is embedded in the optical chip 33, and the tip 36 of the optical chip 33 is rounded to obtain a lens effect. The optical chip 33 is formed of an artificial jewel. The laser light L31 entering the optical chip 33 from the light guide fiber 34 is repeatedly reflected in the optical chip 33 as shown in FIG. In this case, the reflection angle θ3
1, θ32, ──, θ3n increase, but since the tip 36 is rounded to have a lens effect, the focal length e from the tip 36
The focus f4 is formed at the position of.

Details of the reference example are shown in FIG. Figure 6
5 is different from the configuration of FIG. 5 described above in that the optical chip 3
That is, the tip 36 of 3 is not rounded but formed in a wedge shape. Incidentally, L32 is a laser beam. Other configurations are the same as the configurations of FIG. 5 described above.

As is clear from a comparison of the configuration of FIG. 5 with the reference example of FIG. 6, since the tip 36 of the optical chip 33 has a lens effect, the position of a short focal length e from this tip 36. Focus f4 can be fixed at. Therefore,
Even a laser beam having a large diffusion angle such as a semiconductor laser can be used while being prevented from being diffused, and the energy of the laser beam L31 can be concentrated and heated only at a desired position, for example, the surface layer of body tissue. . For this reason,
It is possible to prevent the heating action from being applied to the inside of the eyeball. Further, the tip 36 of the optical chip 33 can be prevented from being soiled and damaged, and the heated portion can be easily seen because the tip 36 is small.

Although the laser probe for ophthalmic surgery is described in this embodiment, it is needless to say that the present invention can be similarly applied to laser probes for other purposes.

[0027]

According to the laser probe of the present invention, since the laser light passes through the lens system, it can be focused at a position apart from the probe tip by a predetermined distance, and can be efficiently positioned at a desired position. This has the effect of concentrating the energy of laser light and selectively heating a specific part. Therefore, there is an effect that a laser beam having a large diffusion angle such as a semiconductor laser can also be used. Since the semiconductor laser has a cheap light source and low power consumption, there is an effect that the laser coagulation apparatus can be made compact and inexpensive.

According to the embodiment, in the case of a hook-shaped laser probe, even a laser beam having a large diffusion angle such as a semiconductor laser can be prevented from diffusing, and the energy per unit area can be increased. The energy of the laser light can be concentrated at the position of, and it can be heated to enhance the coagulation action, and as a result, it is possible to prevent damage to the posterior segment of the eye without increasing the output level of the laser light more than necessary. . And in the case of a straight type laser probe, the energy of the laser beam can be concentrated at a desired position and heated to strengthen the coagulation action, and since the optical fiber is not exposed as in the conventional semiconductor, A laser having a large divergence angle such as a laser can be used. On the other hand, even in the case of a thin beam such as a gas laser, it is possible to prevent the laser light from sticking to the surface layer (for example, retina) of body tissue.

Further, in the case of the wedge type laser probe, since the tip of the optical tip portion has a lens effect, it is possible to focus at a position at a slight distance from the tip, and the body tissue can be focused. It is easier to concentrate the energy of the laser light only on the surface layer, and it is possible to prevent the heating action from being applied to the inside of the eyeball, to prevent the tip and tip of the optical tip from being soiled and damaged, making it easier to see the heated portion. There is an effect.

[Brief description of drawings]

FIG. 1 is a partial cross-sectional view showing a first embodiment.

FIG. 2 is a partial cross-sectional view showing a modified example of FIG.

FIG. 3 is a partial sectional view showing a second embodiment.

FIG. 4 is a partial cross-sectional view showing a modified example of FIG.

FIG. 5 is a partial sectional view showing a third embodiment.

6 is a partial cross-sectional view showing the reference example of FIG.

FIG. 7 is a perspective view showing a conventional hook-shaped laser probe.

FIG. 8 is a partial cross-sectional view showing an arrow portion in FIG.

FIG. 9 is a perspective view showing a straight type laser probe.

[Explanation of symbols]

 1, 10, 21, 31, 40, 48 Laser probe 3 Optical glass part 4, 24, 34, 47 Light guide fiber 5, 35 Tip 6 Mirror surface 13 Mirror 14, 26 Selfoc lens 33 Optical chip L01, L11, L12, L2 , L31, L32 laser light a, b, c, d, e focal length f1, f2, f3, f4 focus

Claims (3)

[Claims] 1. A hook-type hook type laser probe for irradiating an object with a predetermined laser beam, an optical fiber having an end fixedly held in the probe and transmitting laser light from a laser light source; And a laser light reflected by the reflecting means, wherein the laser light reflected by the reflecting means is focused at a position apart from the tip of the probe by a predetermined distance. 2. The laser probe according to claim 1, wherein the reflecting means is a concave mirror. 3. The laser probe according to claim 1, wherein the reflecting means is a plane mirror, and the laser beam reflected by the plane mirror is focused at a position apart from the tip of the probe by a predetermined distance. Laser probe equipped with Fock lens.