JPH06105864A - Cataract operation apparatus - Google Patents

Abstract

PURPOSE:To obtain a cataract operation apparatus wherein emulsifying suction of a soft nucleus lentis and grinding of a hard nucleus lentis can be done by generating ultrasonic wave while a hollow ultrasonic chip is reciprocally moved and applying a laser light from a fiber part inserted in the ultrasonic chip. CONSTITUTION:A hollow ultrasonic chip 23 is penetrated into the outside tube 21 formed in a hand piece 2 and a fiber end probe 22 is penetrated into the chip 23. A perfusate is made flow in the outside tube 21 and a gap between the ultrasonic chip 23 and the probe 22 is made to be a suction port 24 for sucking the perfusate, a ground nucleus lentis, etc. The ultrasonic chip 23 is reciprocally movable by an ultrasonic oscillation generated by means of a piezoelectric element 231 to emulsify a relatively soft nucleus lentis by means of the generated ultrasonic wave. In addition, the probe 22 is connected with an infrared laser light source through the fiber 321 and round dissection of a lenticular front capsule and grinding of a nucleus lentis are performed by means of the laser light irradiated from the apex.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a cataract surgery device used for cataract surgery or the like, and particularly, for comparatively soft lens nucleus, ultrasonic emulsification suction is applied to hard lens nucleus. The present invention relates to a cataract surgery device that can be destroyed by a laser.

[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 method is performed in which the lens capsule is completely removed without performing an incision of the anterior lens capsule or ultrasonic emulsification suction method. Enucleation) was being 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 capsular bag, 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.

Further, when cataract develops in this handpiece and the hardened lens nucleus is crushed, a considerably large amount of laser energy must be irradiated, which may adversely affect the eye tissue other than the intended one. It was

[0013]

SUMMARY OF THE INVENTION The present invention has been devised in view of the above problems, and in a cataract surgery device for inserting an ultrasonic tip into the eye, a hollow ultrasonic tip and the ultrasonic tip A vibrating section that reciprocates the tip to generate ultrasonic waves, a fiber section that guides light from a laser light source having a wavelength corresponding to the absorption peak of water, and a fiber section that is formed inside the ultrasonic tip and is supplied from the laser light source. And a tip portion for emitting a laser beam capable of cutting the living tissue toward the irradiation target.

The present invention also provides a laser light source having a wavelength of 2.9 μm.
An infrared laser light source in the vicinity of m is adopted, the fiber portion is formed of a zirconium-based fluoride glass fiber, and the tip portion is an anhydrous silica fiber at the end portion on the irradiation target side or a reflectance near the wavelength. It can also be formed from sapphire fiber with a high metal coating.

Further, in the present invention, an infrared laser light source having a wavelength of about 2.9 μm is adopted as the laser light source, 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. It is also possible to form a quartz tube coated with resin.

In the cataract surgery device for inserting an ultrasonic tip into the eye, the present invention provides a hollow ultrasonic tip, a vibrating section for reciprocating the ultrasonic tip to generate ultrasonic waves, and a water A light source that emits laser light having a wavelength corresponding to the absorption peak of the laser beam, an incident optical system that makes the laser light from the laser light source enter one end of the fiber portion, and a gas that is cooled at one end of the fiber portion where the laser light enters. The cooling unit to be sprayed and a tip portion for emitting a laser beam from the laser light source capable of cutting the biological tissue toward the irradiation target are configured inside the ultrasonic chip.

[0017]

The present invention configured as described above is a cataract surgery device for inserting an ultrasonic tip into the eye, wherein the vibrating section is
The hollow ultrasonic tip is moved back and forth to generate ultrasonic waves, and the fiber portion guides the light from the laser light source of the wavelength corresponding to the absorption peak of water, and the tip formed inside the ultrasonic tip. The unit emits laser light, which is supplied from a laser light source and is capable of cutting the biological tissue, toward the irradiation target.

The present invention also provides a laser light source having a wavelength of 2.9 μm.
An infrared laser light source in the vicinity of m is adopted, the fiber part is formed of a zirconium-based fluoride glass fiber, and the tip part has a high reflectance in the vicinity of the wavelength of the anhydrous silica fiber or the end on the irradiation target side. It can also be formed from sapphire fiber with a metal coating.

Further, according to the present invention, the fiber portion may be formed of 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.

According to the present invention, the light source generates 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 incident. The cooled gas is blown onto one end of the fiber portion where the light enters.

[0021]

【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 this embodiment.
Is composed of a handpiece 2 and a control device body 3.

An outer tube 21 is formed on the handpiece 2, and a hollow ultrasonic tip 23 is inserted into the outer tube 21. The fiber end probe 22 is inserted into the inside of the ultrasonic tip 23, and the fiber end probe 22 is independently fixed to the ultrasonic tip 23, and the ultrasonic tip 23 vibrates. Also, the fiber end probe 22 is configured so as not to vibrate. The perfusate flows inside the outer tube 21, and the perfusate is discharged from the discharge port 211 and the gap 212 formed in the outer tube 21.
Then, the ultrasonic tip 23 and the fiber end probe 2
The gap 2 serves as a suction port 24 for sucking the perfusate and the crushed lens nucleus.

The control device body 3 includes a suction / perfusion device 31.
, An infrared laser light source 32, and a vibration drive unit 33.

The perfusion means of the suction / perfusion device 31 is connected to the outer tube 21 via the first tube 311, and the perfusion solution is discharged from the outlet 2 formed in the outer tube 21.
11 and the gap 212 can be discharged. The perfusate is also discharged from the gap between the outer tube 21 and the ultrasonic tip 23. The suction means of the suction / perfusion device 31 is connected to the suction port 24 via the second tube 312, and sucks the perfusate, the crushed lens nucleus, and the like. Appropriate pump means is adopted as the suction / perfusion device 31. And the perfusate is BSS (BALA
It is a liquid called NCED SALT SOLUTION) that is injected into the crystalline lens and is for maintaining an appropriate intraocular pressure.

The infrared laser light source 32 corresponds to a light source, generates laser light having a wavelength corresponding to the absorption peak of water, and the laser light is guided to the fiber end probe 22 via the fiber 321. .

The vibration driving unit 33 is a piezo electric driving device, and the piezo electric element 23 for vibrating the ultrasonic chip 23 via the cable 331.
Connected with 1. The piezo electric element 231
Ultrasonic vibration of about 40 KHz and an amplitude of about 0.1 mm is performed, and this vibration is transmitted to the ultrasonic chip 23, and the ultrasonic chip 23 reciprocates.

Next, the handpiece 2 will be described in detail with reference to FIG.

A piezoelectric electric element 231 is connected to the ultrasonic chip 23, and an output signal of the vibration driving section 33 is supplied to the piezoelectric electric element 231 via a cable 331. The ultrasonic chip 23 penetrates the hollow portion 2311 of the piezoelectric element 231 and is connected to the second tube 312. The second tube 312 is connected to the suction means of the suction / perfusion device 31. There is.

Then, the outer tube 21 and the ultrasonic tip 2
The gap between the perforated liquid and the third perforation 3 is connected to the first tube 311 so that the perfusion liquid is supplied from the perfusion means of the suction / perfusion device 31. And the perfusate is the outer tube 2
The gas is emitted from the discharge port 211 formed in No. 1 and the gap portion 212 of the outer tube 21 and the ultrasonic tip 23.

A fiber end probe 22 is inserted inside the ultrasonic chip 23, and the fiber end probe 22 is connected to an infrared laser light source 32 via a fiber 321. Then, the fiber end probe 22 includes a piezoelectric element 231.
Is fixed to the outer tube 21 or the handpiece 2 at the rear of the. Then, the laser light emitted from the tip of the fiber end probe 22 can perform an incision of the anterior capsule of the lens and fragmentation of the lens nucleus.

The infrared laser light source 32 has a wavelength of 2.9 μm.
It generates an infrared laser in the vicinity. 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 increases when the rotational vibration band of the molecule which absorbs photons and is 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.
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 corresponding to the absorption peak of water, which is a main constituent of the biological tissue, is operated with a high peak power and an ultrashort pulse width, the biological 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 of about 2.9 μm is set as a condition under which only the target living tissue can be evaporated without causing significant 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 around 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 structure of the fiber end probe 22 will be described with reference to FIG. The fiber end probe 22 includes a sapphire fiber 221a, which is a fiber tip protection member, and the sapphire fiber 221.
and a covering portion 222 for covering the outer peripheral portion of a. Then, the sapphire fiber 221a and the fiber 321 are disposed in the covering portion 222 and the handpiece 2
Is coupled inside the infrared laser light source 32
Infrared laser from Sapphire fiber 221a
The light is guided to the tip of the. The covering portion 222 of this embodiment is made of a stainless tube, but may be made of other materials. Further, the fiber 321 of the present embodiment is a zirconium-based fluoride glass fiber.

The fiber tip protection member corresponds to the tip. This sapphire fiber 221
On the outer peripheral surface of a, 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. Further, a reflective layer 2211 formed on the sapphire fiber 221a,
The covering portion 222 is fixed with an appropriate adhesive 2212.

The sapphire fiber 221a is made of sapphire, which has a very good transmittance of infrared laser light near the wavelength of 2.9 μm, and has a length of 10 in the axial direction.
mm or more, and the fiber 321 is connected inside the handpiece 2. 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 by a failure accident or the like. Therefore, the sapphire fiber 221a has a sufficient axis. This is because the length in the direction is required.

Since the sapphire fiber 221a is provided 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 fiber 221a. The energy of the infrared laser light is suppressed to the minimum, and the heat generated in the sapphire fiber 221a and its outer peripheral portion is reduced. As a result, the sapphire fiber 221a can be prevented from being damaged, and the effect of heat on the eyeball can be minimized.

The fiber 231 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 fiber 22 is used.
Since the diameter of 1a is about 80 μm to 250 μm, the thermal effect on the eyeball due to the laser irradiation in this case will be theoretically considered.

Cross-sectional area A of sapphire fiber 221a
r 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

Furthermore, 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 fiber 221 a is 80 μm)

(15.7 / (250 * 10 ⁻³ )) = 63 (when the diameter of the sapphire fiber 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 fiber 221 a is 80 μm)

((1.0 * 10 ⁻³ * 4.2) cal * 63) /7.2=0.037° C. (when the diameter of the sapphire fiber 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 process of 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, with reference to FIG. 4, a modified example in which the fiber 321 is a zirconium-based fluoride glass fiber 51, and anhydrous silica fiber 221b is used instead of the sapphire fiber 221a for the fiber tip protection member will be described. . Anhydrous quartz fiber 221b
Is composed of a core portion 2213 and a clad portion 2214, and is fixed to the covering portion 222 with an appropriate adhesive 2212. The rest of the configuration is similar to that of the embodiment shown in FIG.

Next, referring to FIGS. 5 and 6, the fiber 321 is replaced by a zirconium-based fluoride glass fiber 5.
Instead of No. 1, a modified example will be described in which a quartz tube 52 is used in which the inner surface is covered with a metal having a high reflectance around a wavelength of 2.9 μm and the outer surface is coated with a resin. As shown in FIG. 5, in this modification, a sapphire fiber 221a is used as the fiber tip protection member, and a quartz tube 52 is connected to this sapphire fiber 221a.
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 modification, since the fiber 321 is made of the quartz tube 52, which has less influence on the human body, the axial length of the sapphire fiber 221a may be 10 mm or less. In addition, other configurations are
The description is omitted because it is the same as the embodiment of FIG.

Further, in FIG. 6, the quartz tube 52 is adopted as the fiber 321, and the fiber end protection member is replaced with the sapphire rod 221a, and the anhydrous silica fiber 22
It is a modification using 1b. Anhydrous quartz fiber 22
The configuration of 1b is the same as that of the modification of FIG. 4, and the other configurations are the same as those of the embodiment of FIG.

Next, FIG. 7 is a view 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 a quartz tube having a metal reflective layer formed thereon is similarly cooled by spraying dry air or dry nitrogen from an appropriate nozzle means 7. be able to. 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. An ultrasonic tip 23 is inserted into the anterior chamber through an incision in the sclera or sclera, and infrared laser light is emitted in pulses while the tip of the fiber end probe 22 is lightly contacting 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 tip is emulsified and sucked by the ultrasonic tip 23.

In the case of advanced cataract and the lens nucleus is hardened, the ultrasonic tip 23 is inserted into the lens nucleus through the circular opening of the anterior lens capsule made by CCC. Then, pulsed infrared laser light is emitted from the tip of the fiber end probe 22 to make an incision in the lens nucleus. The cured lens nucleus is subdivided by repeating pulsed infrared laser light irradiation.

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

If the fiber portion is formed of a stepping fiber having sapphire as the core, the fiber tip protecting member may be omitted.

[Effect] The present invention configured as described above has a hollow ultrasonic chip, a vibrating section for reciprocating the ultrasonic chip to generate ultrasonic waves, and a wavelength corresponding to the absorption peak of water. A fiber portion that guides light from a laser light source, and a tip portion that is formed inside the ultrasonic chip and that emits laser light that can cut the biological tissue supplied from the laser light source toward an irradiation target. Since it is composed of and, it is possible to provide a cataract surgery device capable of performing ultrasonic emulsification and suction on a relatively soft lens nucleus and crushing with a laser on a hard lens nucleus. It has an outstanding effect.

The present invention may also include an incident optical system for making laser light from the laser light source incident on one end of the fiber portion, and a cooling portion for blowing a cooled gas to 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.

[0077]

[Brief description of drawings]

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

FIG. 2 is a perspective view illustrating 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]

 1 Cataract Surgery Device 2 Handpiece 21 Outer Tube 211 Ejection Port 22 Fiber End Probe 24 Suction Port 221a Sapphire Rod 221b Anhydrous Silica Fiber 2211 Reflective Layer 2212 Adhesive 2213 Core Part 2214 Clad Part 222 Cover Part 23 Ultrasonic Tip 231 Piezoelectric Element 3 Control Device Main Body 31 Suction / Perfusion Device 311 First Tube 312 Second Tube 32 Infrared Laser Light Source 321 Fiber 33 Vibration Driver 331 Cable 51 Zirconium Fluoride Glass Fiber 52 Quartz Tube 521 Metal Reflective Layer 7 Nozzle Means

Claims (4)

[Claims] 1. In a cataract surgery device for inserting an ultrasonic tip into the eye, a hollow ultrasonic tip, a vibrating section for reciprocating the ultrasonic tip to generate ultrasonic waves, and a water absorption peak. A fiber portion that guides light from a laser light source having a wavelength corresponding to, and a laser light that is formed inside the ultrasonic chip and that can cut the biological tissue supplied from the laser light source toward the irradiation target. A cataract surgery device comprising: 2. The laser light source is an infrared laser light source having a wavelength near 2.9 μm, the fiber portion is formed of a zirconium-based fluoride glass fiber, and the tip portion is an end portion on the irradiation target side. 2. The cataract surgery device according to claim 1, wherein is formed of anhydrous silica fiber or sapphire fiber coated with a metal coating having a high reflectance around the wavelength. 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. A quartz tube that is formed by:
The cataract surgery device described. 4. In a cataract surgery device for inserting an ultrasonic tip into the eye, a hollow ultrasonic tip, a vibrating section for reciprocating the ultrasonic tip to generate ultrasonic waves, and a water absorption peak. A light source that emits a laser beam having a wavelength corresponding to, an incident optical system that causes the laser beam from the laser source to enter one end of the fiber section, and a cooling section that blows a cooled gas to one end of the fiber section where the laser beam enters And a tip portion for emitting a laser beam capable of incising a biological tissue from a laser light source toward an irradiation target, inside the ultrasonic chip.