JPH06105863A - Intraocular operation apparatus - Google Patents

Abstract

PURPOSE:To ensure safety by forming the apex part of a fiber end probe for cutting an irradiating objective by application of infrared rays with a sapphire rod, coating the peripheral part with a coating layer and avoiding thereby exposure of the fiber part to the intraocular structure. CONSTITUTION:An intraocular probe 21 is formed in a hand piece 2 and a fiber end probe 22 the apex part of which is exposed to a perfusate injecting hole 211 at the apex part of the intraocular probe 21 is inserted therein. The intraocular probe 21 is communicated with a cylinder 4 through a flexible tube 3 to discharge the perfusate from the injecting hole 211 and the fiber end probe 22 is communicated with an infrared laser source 6 through a fiber 5 to perform round dissection of a lenticular front capsule by means or irradiation or a laser light. In addition, this fiber end probe 22 is formed of an apex protective member consisting of a sapphire rod and a coating part 222 coating the peripheral part of this protective member 221 not so as to expose the fiber part in the intraocular structure.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an intraocular surgery apparatus used for cataract surgery or the like, and in particular, the front end portion from which laser light is emitted to cut an irradiation target is destroyed by a failure accident or the like. The present invention also relates to an intraocular surgery device configured so that the fiber portion and the intraocular tissue do not come into contact with each other even when the surgical operation is performed.

[0002]

2. Description of the Prior Art For cataract patients whose lenses are turbid, there is currently no effective therapeutic agent to make the lenses transparent, and surgery is performed to restore the loss of visual acuity. There must be.

In recent years, ultrasonic emulsification / suction has been widely practiced as a surgical method for cataracts. Although this ultrasonic emulsion suction is limited to soft lens nuclei, a lens nucleus segmentation method has been proposed, and ultrasonic emulsion suction is also performed on hard lens nuclei.

That is, the lens nucleus segmentation method is to inject a constant amount of perfusate between the layers of the laminated lens nucleus before the ultrasonic emulsification suction operation to separate the layers and soften the lens nucleus. It is intended. In the ultrasonic emulsification suction method, ultrasonic waves of about 27 to 55 KHz are applied and vibrated while injecting a perfusate to generate cavitation, and the mechanical destruction action destroys the cataract lens tissue to be emulsified. The lens nucleus tissue and the perfusate are aspirated.

For a relatively soft lens nucleus, first, the anterior lens capsule is incised, and the cataract lens tissue is destroyed by the ultrasonic emulsification suction method. Then, surgery is performed to insert an artificial lens into the remaining lens capsule. A circular incision method is widely used as a method of incising the anterior lens capsule. This is because the opening is symmetric in this method, cracks are less likely to occur at the anterior capsule margin, and there is less damage to the eye tissue.

[0006] For a lens nucleus that has become relatively harder due to further cataract, conventionally, an intracapsular resection (total encapsulation) is performed without performing an incision of the anterior lens capsule or ultrasonic emulsification suction method. Plucking surgery) was performed. However, the intracapsular resection has a problem that the artificial lens cannot be fixed in the eye in a stable state because the lens capsule does not remain. Therefore, the tip of the thin wire is vibrated by ultrasonic waves, and the perfusate BSS (BALANCED SA) is applied from the tip.
LT SOLUTION) is injected to separate the layers of the lens nucleus from each other by a hydrodynamic separation method (HYDRODELINEA).
TION) has been implemented.

Handpieces using laser light have been developed to remove cataractous lens tissue in the eye. (JP-A-1-299546) This handpiece comprises a handpiece body, a means for transmitting a laser beam having a wavelength corresponding to an absorption peak of water, a perfusion means for perfusing a perfusate, and a laser beam. And suction means for sucking the evaporated tissue.

[0008]

However, the success or failure of the conventional circular incision depends on how close the incision part is to a perfect circle, and how to clean the incision part and prevent invasion of other eye tissues. This depends largely on the experience and skill of the operator. If this circular incision is not performed satisfactorily, damage to the Chin's band, damage to the lens capsule, etc. may occur, and it is also suitable for surgery by ultrasonic emulsification suction method and insertion of intraocular lens. There was a problem that it had an adverse effect.

That is, if the technique of the operator is immature, the capsule may crack when the anterior capsule is incised, and the shape of the incision does not become circular, or even if it is circular, the opening edge is jagged. Then, there is a concern that the capsular bag will be cracked and the Chin's band will be damaged during the operation by the ultrasonic emulsification suction method, which will be performed later, due to uneven stress on the capsular bag. When the anterior capsule incision is asymmetric, the inserted intraocular lens cannot maintain the optical center and becomes unstable after the operation.

For a lens nucleus that has become relatively hard due to the progress of cataract, a hydrodynamic separation method (HYDRODE) is used.
LINEATION) is performed, but in this case, a hydrodynamic separation method (HYDRODELIN) is used from a special scalpel with a bent tip of the injection needle for performing anterior lens capsule incision.
There is a problem in that the probe of the device for performing EATION) has to be replaced with the instrument to be inserted into the eye of the patient. The replacement of the instrument to be inserted into the eye not only prolongs the operation time, but also has a problem that the corneal endothelium may be damaged if careful attention is paid. Further, there is a problem that corneal endothelium damage is caused by the generated cavitation when ultrasonic vibration is applied for a long time.

In the above handpiece using laser light, a zirconium fluoride fiber is used as a light guiding means for infrared laser light having a wavelength of about 2.9 μm. A sapphire window is formed at the tip of the fiber end probe for the purpose of protecting the fiber end face.However, not only is laser light leaked from the outer periphery of this sapphire window and laser energy is lost, but the sapphire window There is a problem that the sapphire window may be destroyed by being converted into heat energy at the boundary with the holder fixing the window. Further, the zirconium-based fluoride fiber is not harmless to the human body, and there is a problem that the fiber may come into contact with living tissue in the eye.

[0012]

SUMMARY OF THE INVENTION The present invention has been devised in view of the above-mentioned problems, and corresponds to an absorption peak of water in an intraocular surgery device having a handpiece provided with a probe to be inserted into the eye. A fiber portion for guiding light from a laser light source of a wavelength to the handpiece, a covering portion for preventing the fiber portion from being exposed when the probe is inserted into the eye, and an end of the fiber portion. Part, connect either the anhydrous silica fiber or a sapphire rod that is coated with a metal coating having a high reflectance in the vicinity of the wavelength inside the handpiece, and emit the laser light to cut the irradiation target. And a tip portion formed, the tip portion, even when destroyed by the light of the laser light source due to a failure accident, the fiber portion and the intraocular tissue And it is configured so as not to touch.

In the present invention, the laser light source has a wavelength of 2.9 μm.
An infrared laser light source near m may be used, and the fiber portion may be made of a zirconium-based fluoride glass fiber.

Further, in the present invention, the laser light source is an infrared laser light source having a wavelength of about 2.9 μm, the fiber portion has an inner surface covered with a metal having a high reflectance at a wavelength of about 2.9 μm, and an outer surface made of a resin. It can also be composed of a quartz tube coated with.

In the present invention, the probe may have a perfusion part for injecting a liquid and exfoliating an object in a wound part formed by irradiating the laser beam from the fiber part. .

Further, according to the present invention, in an intraocular surgery apparatus having a handpiece provided with a probe to be inserted into the eye, a light source for emitting a laser beam having a wavelength corresponding to the absorption peak of water, and a laser from the laser light source. An incident optical system that makes light enter one end of the fiber portion, a cooling unit that blows a cooled gas to one end of the fiber portion where laser light enters, and the fiber portion is not exposed when the probe is inserted into the eye. In the same manner, the covering portion for covering this and the end portion of the fiber portion are connected to either the anhydrous silica fiber or the sapphire rod coated with the metal coating having a high reflectance in the vicinity of the wavelength inside the handpiece. ,
It has a tip portion formed so as to emit the laser light for cutting an irradiation target, and the tip portion, even when destroyed by the light of the laser light source due to a failure accident or the like, and the fiber portion. It can also be configured so that it does not come into contact with the intraocular tissue.

[0017]

The present invention configured as described above is an intraocular surgery apparatus having a handpiece provided with a probe to be inserted into the eye, wherein the fiber portion has a wavelength corresponding to the absorption peak of water. The light from the light source is guided to the handpiece, and the covering portion prevents the fiber portion from being exposed when the probe is inserted into the eye. In order to cut the irradiation target, the tip part is connected to the end of the fiber part, either the anhydrous silica fiber or the sapphire rod which is coated with a metal having high reflectance in the vicinity of the wavelength, inside the handpiece. It is designed to emit laser light.
The tip portion is designed so that the fiber portion does not come into contact with the intraocular tissue even when the tip portion is destroyed by the light of the laser light source due to a failure accident or the like.

In the present invention, the laser light source has a wavelength of 2.9 μm.
An infrared laser light source near m may be used, and the fiber portion may be a zirconium-based fluoride glass fiber.

Further, in the present invention, the fiber portion may be a quartz tube having an inner surface covered with a metal having a high reflectance at a wavelength of about 2.9 μm and an outer surface coated with a resin.

The probe of the present invention may be provided with a perfusion portion for injecting a liquid and peeling an object into the wound portion formed by irradiating the laser light from the fiber portion.

According to the present invention, the light source emits laser light having a wavelength corresponding to the absorption peak of water, the incident optical system makes the laser light from the laser light source incident on one end of the fiber portion, and the cooling portion makes the laser light. It is also possible to blow the cooled gas to one end of the fiber portion on which is incident.

[0022]

【Example】

An embodiment of the present invention will be described with reference to the drawings.

As shown in FIG. 1, the intraocular surgery device 1 of the present embodiment.
Is composed of a handpiece 2, a flexible tube 3, a cylinder 4, a fiber 5, and an infrared laser light source 6.

An intraocular probe 21 is formed on the handpiece 2, and a fiber end probe 22 is inserted inside the intraocular probe 21. A perfusion solution ejection port 211 is formed at the tip of the intraocular probe 21, and the tip of the fiber end probe 22 is exposed at the perfusion solution ejection port 211. The intraocular probe 21 is in communication with the cylinder 4 via the flexible tube 3 and is configured so that the perfusate pumped from the cylinder 4 can be discharged from the perfusate outlet 211. The intraocular probe 21 of this embodiment is made of a stainless tube, but a tube made of another material may be used. The fiber end probe 22 is connected to the infrared laser light source 6 via the fiber 5, and the infrared laser light generated by the infrared laser light source 6 is exposed to the perfusion solution outlet 211. It is designed to lead to the tip of the. Then, an anterior lens capsule circular incision can be performed by the laser light emitted from the tip of the fiber end probe 22. The circular incision corresponds to a wound.

The cylinder 4 is for pumping the perfusate, and any pump means can be adopted as long as the perfusate can be pumped to the intraocular probe 21 through the flexible tube 3. it can. Perfusate is BS
S (BALANCED SALT SOLUTION)
Is a liquid to be injected into the lens, which is for carrying out a hydrodynamic separation method. The cylinder 4, the flexible tube 3, and the intraocular probe 21 correspond to the perfusion part.

The infrared laser light source 6 emits an infrared laser having a wavelength near 2.9 μm. In this embodiment, an ErYAG (erbium yttrium aluminum garnet) laser light source is used, but other laser generating light sources can be used.

Here, the infrared laser light for the living tissue will be described in detail.

The laser light exerts different actions on the living body depending on the wavelength, the intensity of energy and power, the difference of continuous wave or pulse wave, and the like. From these characteristics of action, PHOTOCHEMICAL, TH
ERMAL, PHOTOABLIVE, ELECT
It is the THERMAL region that is classified into 4 regions of RO-MECHANICAL and is used as a laser knife.

The temperature of the living tissue irradiated with the laser rises because the temperature of the molecule rapidly rises when the rotational vibration band of the molecule which absorbs photons and becomes in a low excited state does not spontaneously emit. Is. The combination of laser light wavelength, irradiation time, and irradiation area determines the energy reaching depth and tissue reaching temperature, and thus controls from cell activity suppression to protein melting, coagulation, carbonization, and evaporation. be able to.

For example, the Ar laser can raise the temperature of the retina choroid to 60 to 70 ° C. and coagulate it by irradiation of several tens of msec, and the continuous wave carbon dioxide laser is
Since the temperature of the living tissue is raised to 100 ° C. or higher and the tissue evaporates while forming a carbonized layer around it, it is used for incision surgery where a hemostatic effect is expected.

Further, when a laser having a wavelength matching the absorption peak of water, which is a main constituent of the living tissue, is operated with a high peak power and an ultrashort pulse width, the living tissue is ablated with almost no thermal damage. can do. Water has a strong absorption peak near a wavelength of 2.9 μm, and an HF laser (multispectral 2.74 to 2.96 μm) that oscillates at a wavelength near this wavelength or an Er / YAG laser (wavelength of 2.936 μm) ), The living tissue can be excised with almost no thermal damage.

A wavelength around 2.9 μm is set as a condition under which only the target living tissue can be evaporated without giving remarkable thermal damage such as protein denaturation or coagulation to the tissue adjacent to the excised part. In the infrared laser light of, the EXPOSUREDURATION TIME
Is known to be 1.7 μSEC or less.

Therefore, if an infrared laser beam having a wavelength near 2.9 μm and a pulse width of 1.7 μSEC or less is used,
It is possible to perform an incision process similar to the incision using a conventional metal knife. Particularly in the intraocular surgery device 1 as in this embodiment,
By making the emission diameter of the infrared laser emitted from the tip portion of the fiber end probe 22 as small as possible, it is possible to cope with precision surgery.

Next, the handpiece 2 will be described in detail with reference to FIG. FIG. 2 is a sectional view of the handpiece 2,
An intraocular probe 21 is inserted through a substantially central portion inside the handpiece 2, and a flexible tube 3 is connected to the intraocular probe 21. This intraocular probe 2
The perfusion solution (BSS) supplied from the flexible tube 3 flows into the inside of the tube 1. Further, a fiber end probe 22 is arranged in the intraocular probe 21. The fiber end probe 22 includes a fiber tip protection member 221 and a coating portion 222 for coating the outer peripheral portion of the fiber tip protection member 221. The fiber tip protection member 221 and the fiber 5 are coupled inside the covering portion 222 and inside the handpiece 2, and the infrared laser from the infrared laser light source 6 is coupled to the fiber tip protection member 2.
The light is guided to the tip of 21. The covering portion 222 of this embodiment is made of a stainless tube, but may be made of other materials.

The fiber tip protection member 221 corresponds to the tip.

Next, a case where the fiber 5 is a zirconium-based fluoride glass fiber 51 will be described with reference to FIGS. 3 and 4. FIG. 3 shows a cross-sectional view of the fiber end probe 22, and a sapphire rod 221a is adopted as the fiber tip protection member 221. On the outer peripheral surface of the sapphire rod 221a,
A reflective layer 2211 is formed by vapor-depositing gold, silver, aluminum or the like and applying a protective coating. The reflective layer 2211 is configured to efficiently reflect light near the wavelength of 2.9 μm. Furthermore, the sapphire rod 221
The reflection layer 2211 formed on a and the covering portion 222 are
It is fixed with an appropriate adhesive 2212.

The sapphire rod 221a has a wavelength of 2.9.
It is made of sapphire, which has an extremely good transmittance of infrared laser light in the vicinity of μm, has a length of 10 mm or more in the axial direction, and the zirconium-based fluoride glass fiber 51 is equivalent to that of the handpiece 2. Internally connected. Because the zirconium-based fluoride glass fiber is not harmless to the human body, it is necessary to avoid contact with living tissue even when it is destroyed due to a failure accident or the like. Therefore, the sapphire rod 2
This is because 21a requires a sufficient axial length.
The zirconium-based fluoride glass fiber 51
Is composed of a core portion 511 and a clad portion 512.

Since the sapphire rod 221a is formed with a reflection layer 2211 for light having a wavelength of about 2.9 μm, a wavelength of about 2.9 μm absorbed by the adhesive 2212 or the like existing on the outer peripheral portion of the sapphire rod 221a. The energy of the infrared laser light is suppressed to the minimum, and the heat generated in the sapphire rod 221a and its outer peripheral portion is reduced. As a result, the sapphire rod 221a can be prevented from being damaged, and the effect of heat on the eyeball can be minimized.

The fiber 5 corresponds to the fiber portion.

In order to minimize the effect of shock waves on the corneal endothelium, a wavelength of 2.9 μm is used.
When irradiating the infrared laser light in the vicinity of m in a pulse shape, it is desirable to minimize the energy irradiated by one pulse. However, the wavelength is 2.9μ
The energy density required to evaporate the biological tissue by the infrared laser light near m is ² J / cm ^2, and incision cannot be performed below this energy density. Therefore, in order to evaporate living tissue and minimize the effect of shock waves (shock waves),
It is necessary to make the irradiation area of the infrared laser light as small as possible.

In this embodiment, the sapphire rod 221a is used.
Has a diameter of about 80 μm to 250 μm, the thermal effect on the eyeball due to laser irradiation in this case will be theoretically considered.

Cross-sectional area Ar of the sapphire rod 221a
Is

Π * (80/2 * 10 ⁻⁴ ) ² ≦ Ar ≦ π * (250/2 * 10 ⁻⁴ ) ² 5 * 10 ⁻⁵ ≦ Ar ≦ 4.9 * 10 ⁻⁴ (cm ² ).

It becomes

Therefore, the energy density required to evaporate the living tissue is ² J / cm ² , and the applied energy E is ² J / cm ² * Ar.

0.1 mJ≤E≤1.0 mJ

It becomes

Further, if the diameter of the eyeball is 24 mm, the volume of the eyeball is 7.2 cm ³ , and if a circular incision of 5 mm in diameter is made on the anterior lens capsule, the incision length S is

S = 5 * π = 15.7 mm

The number of pulses required for this circular incision is

(15.7 / (80 * 10 ⁻³ )) = 196 (when the diameter of the sapphire rod 221 a is 80 μm)

(15.7 / (250 * 10 ⁻³ )) = 63 (when the diameter of the sapphire rod 221 a is 250 μm)

It becomes And the temperature rise of the whole eyeball in this case is

((0.1 * 10 ⁻³ * 4.2) cal * 196) /7.2=0.011° C. (when the diameter of the sapphire rod 221 a is 80 μm)

((1.0 * 10 ⁻³ * 4.2) cal * 63) /7.2=0.037° C. (when the diameter of the sapphire rod 221 a is 250 μm)

Therefore, in the circular incision of the anterior lens capsule by the intraocular surgery apparatus 1 of this embodiment, the adverse effect of heat on the eyeball can be almost ignored.

Similarly, even if the treatment for subdividing the hardened lens nucleus is continuously performed, the adverse effect of heat on the eyeball is extremely small. Since the energy per pulse when irradiating the infrared laser light is extremely small, the effect on the shock wave can be almost ignored.

Next, based on FIG. 4, the fiber 5 is a zirconium-based fluoride glass fiber 51, and the sapphire rod 22 is provided on the fiber tip protection member 221.
A modification in which anhydrous silica fiber 221b is used instead of 1a will be described. The anhydrous silica fiber 221b includes a core portion 2213 and a clad portion 2214,
The covering portion 222 is fixed with an appropriate adhesive 2212. The rest of the configuration is similar to that of the embodiment shown in FIG.

Next, based on FIGS. 5 and 6, the fiber 5 was replaced with a zirconium-based fluoride glass fiber 51, the inner surface was covered with a metal having a high reflectance at a wavelength of about 2.9 μm, and the outer surface was covered with a resin. A modified example using the coated quartz tube 52 will be described. As shown in FIG. 5, in this modification, a sapphire rod 221a is adopted as the fiber tip protection member 221.
A quartz tube 52 is connected to 21a. The quartz tube 52 has a metal reflection layer 521 formed by vapor deposition of gold, silver, aluminum or the like on the inner surface. The reflective layer 2211 is configured to efficiently reflect light near the wavelength of 2.9 μm. Further, the outer surface of the quartz tube 52 is coated with an appropriate resin.

In this modified example, since the fiber 5 uses the quartz tube 52 which has little influence on the human body, the axial length of the sapphire rod 221a is 10 m.
It may be m or less. The rest of the configuration is the same as that of the embodiment shown in FIG.

Further, in FIG. 6, a quartz tube 52 is adopted for the fiber 5, and the fiber tip protection member 221 is replaced with the sapphire rod 221a, and the anhydrous silica fiber 2 is used.
It is a modification using 21b. Anhydrous quartz fiber 2
The configuration of 21b is the same as the configuration of the modification of FIG. 4, and other configurations are the same as the embodiment of FIG.

Next, FIG. 7 is a diagram showing the infrared laser incident end of the zirconium-based fluoride glass fiber 51. Zirconium fluoride glass fiber 51
Is composed of a core part 511, a clad part 512, and a coating part 513. The pulsed infrared laser light is a zirconium-based fluoride glass fiber 51.
It is condensed on the core part 511 by the incident optical system which is incident on one end of the. Therefore, the temperature of the core portion 511 rises as the pulsed infrared laser light enters. Since the melting point of zirconium-based fluoride glass is relatively low,
There is a problem that the core portion 511 will melt if left unattended. Therefore, it is possible to blow dry air or dry nitrogen from an appropriate nozzle means 7 toward the infrared laser incident end of the zirconium-based fluoride glass fiber 51 to cool the core portion 511.

As a result, the core portion 511 is cooled, and the zirconium fluoride glass fiber 51 is not melted.

Not only the zirconium-based fluoride glass fiber 51 but also the quartz tube 52 having the metal reflection layer 521 formed thereon is similarly sprayed with dry air or dry nitrogen from the appropriate nozzle means 7. Can be cooled. The nozzle means 7 corresponds to a cooling unit.

A method of using the intraocular surgery device 1 of the present embodiment configured as described above will be described. In this example, the case of application to cataract surgery will be described. The intraocular probe 21 is inserted into the anterior chamber through the incision in the sclera or sclera, and the infrared laser light is emitted in pulses while the tip of the fiber end probe 22 is lightly contacted with the anterior lens capsule. . While maintaining this state, if the tip of the fiber end probe 22 is moved on the anterior lens capsule so as to draw a ring, the anterior lens capsule is obtained by pulse irradiation of infrared laser light each time. The pinholes thus formed are continuously formed in an annular shape. Then, by removing the inner capsule surrounded by the ring, a circular opening is completed in the anterior lens capsule. The incision of this circular opening is made into CCC (CONTINUOUS CI
RCULAR CAPSULOR HEXIS).

If the lens nucleus is relatively soft, then the lens nucleus is subjected to emulsification suction with an ultrasonic probe.

In case of advanced cataract and the lens nucleus is hardened, the intraocular probe 21 is inserted into the lens nucleus through the circular opening of the anterior lens capsule prepared by CCC. Then, a pulsed infrared laser light is emitted from the tip of the fiber end probe 22 to make a minute incision in the lens nucleus. Furthermore, the perfusion liquid (BSS) can be pressed into the minute incision from the perfusion liquid injection port 211 to perform interlayer separation of the lens nucleus. It is also possible to subdivide the cured lens nucleus by repeating irradiation with pulsed infrared laser light.

Next, the subdivided lens nucleus can be removed from the anterior capsule of the lens by emulsifying suction for a short time using an ultrasonic probe, or by performing suction only.

When the fiber portion is formed of a stepping fiber having sapphire as the core, sapphire is harmless to the human body. Therefore, without connecting anhydrous silica fiber or the like to this end, extend it to the tip. And use it.

[0071]

[Effects] The present invention configured as described above, when inserting the fiber portion for guiding the light from the laser light source of the wavelength corresponding to the absorption peak of water to the handpiece and the probe into the eye The coating part for preventing the fiber part from being exposed, and the end of the fiber part is made of either anhydrous silica fiber or a sapphire rod provided with a metal coating having a high reflectance in the vicinity of the wavelength. It has a tip connected to the inside of the piece and formed to emit the laser light for cutting the irradiation target, and the tip is broken by the light of the laser light source due to a failure accident or the like. Also, since the fiber part and the intraocular tissue are configured so as not to come into contact with each other, the hydraulic separation from the special scalpel with the tip of the injection needle for performing the anterior capsule circular incision is performed. (HYDRODELINEATI
There is no need to replace the instrument inserted into the patient's eye with the probe of the device performing ON). It also has the outstanding effect of minimizing damage to the eyeballs. Further, even if the tip portion is broken due to a failure accident or the like, the fiber portion and the intraocular tissue do not come into contact with each other, so that there is an effect of high safety.

If a perfusion unit for injecting a liquid is provided, C
CC (CONTINUOUS CIRCULAR CA
(PSULORHEXIS) and delamination of the hardened lens nucleus in advanced cataract eyes and surgery for segmentation can be performed in a short time.

The present invention may also include an incident optical system for making the laser light from the laser light source incident on one end of the fiber portion, and a cooling portion for blowing the cooled gas to the one end of the fiber portion on which the laser light is incident. Therefore, there is an effect that it is possible to prevent the fiber portion from melting due to the laser energy.

[0072]

[Brief description of drawings]

FIG. 1 is a diagram showing a configuration of an intraocular surgery device 1 which is an embodiment of the present invention.

FIG. 2 is a sectional view of a handpiece 2 of this embodiment.

FIG. 3 is a sectional view of a fiber end probe 22 of this embodiment.

FIG. 4 is a diagram illustrating a modified example using anhydrous silica fiber 221b.

FIG. 5 is a diagram illustrating a modified example using a quartz tube 52.

FIG. 6 is an anhydrous quartz fiber 221b and a quartz tube 5.
It is a figure explaining the modification which used 2.

FIG. 7 is a diagram illustrating a cooling unit according to the present exemplary embodiment.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Intraocular surgery device 2 Handpiece 21 Intraocular probe 211 Perfusion solution injection port 22 Fiber end probe 221 Fiber tip protection member 221a Sapphire rod 221b Anhydrous silica fiber 2211 Reflective layer 2212 Adhesive 2213 Core part 2214 Clad part 222 Cover part 3 Flexible Tube 4 Cylinder 5 Fiber 51 Zirconium-based fluoride glass fiber 52 Quartz tube 521 Metal reflective layer 6 Infrared laser light source

Claims (5)

[Claims] 1. An intraocular surgery apparatus having a handpiece provided with a probe to be inserted into the eye, and a fiber part for guiding light from a laser light source having a wavelength corresponding to an absorption peak of water to the handpiece. , When the probe is inserted into the eye, a coating portion for preventing the fiber portion from being exposed, and an end portion of the fiber portion is an anhydrous silica fiber or a metal coating having a high reflectance in the vicinity of the wavelength. One of the applied sapphire rods is connected inside the handpiece, and the tip portion is formed so as to emit the laser beam for cutting the irradiation target. The intraocular surgery device is configured so that the fiber portion and the intraocular tissue do not come into contact with each other even when they are destroyed by the light of the laser light source. 2. The intraocular surgery device according to claim 1, wherein the laser light source is an infrared laser light source having a wavelength of about 2.9 μm, and the fiber portion is made of a zirconium-based fluoride glass fiber. 3. The laser light source is an infrared laser light source having a wavelength of about 2.9 μm, and the fiber portion has an inner surface covered with a metal having a high reflectance at a wavelength of about 2.9 μm and an outer surface coated with a resin. The intraocular surgery device according to claim 1, wherein the intraocular surgery device comprises a quartz tube. 4. The intraocular surgery device according to claim 1, wherein the probe has an irrigation section for injecting a liquid into the wound section formed by irradiating the laser beam from the fiber section to separate the object. . 5. In an intraocular surgery device having a handpiece provided with a probe to be inserted into the eye, a light source for emitting a laser beam having a wavelength corresponding to an absorption peak of water, and a fiber for connecting the laser beam from the laser source. An incident optical system to be incident on one end of the section, a cooling section for blowing a cooled gas to one end of the fiber section on which laser light is incident, so that the fiber section is not exposed when the probe is inserted into the eye, The covering part for covering this and the end of the fiber part are connected to either the anhydrous silica fiber or the sapphire rod on which the metal coating having a high reflectance in the vicinity of the wavelength is applied inside the handpiece to be irradiated. Has a tip portion formed so as to emit the laser beam for cutting the laser beam, and the tip portion is broken by the light of the laser light source due to a failure accident or the like. The intraocular surgery device is configured so that the fiber portion and the intraocular tissue do not come into contact with each other even when the intraocular surgery is performed.