CA2037924A1 - Laser light irradiation apparatus - Google Patents
Laser light irradiation apparatusInfo
- Publication number
- CA2037924A1 CA2037924A1 CA002037924A CA2037924A CA2037924A1 CA 2037924 A1 CA2037924 A1 CA 2037924A1 CA 002037924 A CA002037924 A CA 002037924A CA 2037924 A CA2037924 A CA 2037924A CA 2037924 A1 CA2037924 A1 CA 2037924A1
- Authority
- CA
- Canada
- Prior art keywords
- laser light
- probe
- penetrating member
- irradiation apparatus
- penetrating
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/06—Radiation therapy using light
- A61N5/0601—Apparatus for use inside the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00017—Electrical control of surgical instruments
- A61B2017/00022—Sensing or detecting at the treatment site
- A61B2017/00084—Temperature
- A61B2017/00092—Temperature using thermocouples
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
- A61B2018/2255—Optical elements at the distal end of probe tips
- A61B2018/2261—Optical elements at the distal end of probe tips with scattering, diffusion or dispersion of light
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/06—Radiation therapy using light
- A61N2005/063—Radiation therapy using light comprising light transmitting means, e.g. optical fibres
Abstract
Laser light Irradiation Apparatus Abstract of the Disclosure Laser light irradiation apparatus such as an laser light emitter.
This apparatus irradiates laser light to living tissues of an animal such as a human body to permit an incision, vaporization of the living tissues or a thermal therapy. Further, by this apparatus, a thermal therapy can be carried out efficiently for cancer tissues and the like while its penetrating member is brought into contact with the surface of the living tissues directly or through the intermediary of a surface layer provided on the penetrating member.
This apparatus comprises the penetrating member and a transmitting member such as an optical fiber. The laser light goes through the transmitting member so as to be fed into the penetrating member. Then, the penetrating member contains laser light scattering particles and is fabricated from a laser light penetrating synthetic material.
This apparatus irradiates laser light to living tissues of an animal such as a human body to permit an incision, vaporization of the living tissues or a thermal therapy. Further, by this apparatus, a thermal therapy can be carried out efficiently for cancer tissues and the like while its penetrating member is brought into contact with the surface of the living tissues directly or through the intermediary of a surface layer provided on the penetrating member.
This apparatus comprises the penetrating member and a transmitting member such as an optical fiber. The laser light goes through the transmitting member so as to be fed into the penetrating member. Then, the penetrating member contains laser light scattering particles and is fabricated from a laser light penetrating synthetic material.
Description
2~37~2 Specification Laser Light Irradiation Apparatus Technic~l Field This invention relates to laser light irradiation apparatus such 5 as an laser light emitter, which irradiates laser light to living tissues of an animal such as a human body to permit an incision, vaporization of the living tissues or a thermal therapy and, more particularly, to laser light irradiation apparatus by which a thermal therapy can be carried out efflciently for cancer tissues and the like 10 while the penetrating member of laser light irradiation apparatus is brought into contact with the surface of the living tissues directly or through the intermediary of a surface layer provided on the penetrating member.
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Prior Art Medical treatments such as incisions of living tissues of animal organisms by laser light irradiation are conspicuous due to its ability of hemostasis in these days.
It had been the conventional method that the laser light was irradiated ~om the fore end of an optical fiber which is brought out --2û of contact with the living tisxues. But this method causes severe damage to members of the optical fiber. Therefore, a method which has boen utilized lately is as follows;
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First, laser light is transmitted into an optical ~Iber, whose fore end portion locates adjacent to treated living tissues. Next, the laser light is fed into an emitting probe from the op~ical fiber. This emitting probe is brought into or out of contact with the living 5 tissues. Then, the laser light is emitted from the surface of the probe for irradiating against th~ living tissues. (hereafter "living tissue" is sometimes expressed by "tissue" only).
The inventor developed many kinds of contact probes which are utilized for various purposes.
10Further, lately, localized thermal therapy is drawing special attention as a carcinostatic therapy. According to this method, cancer tissues are destroyed by keeping the cancer tissues at a temperature of about 42-44C for 10-25 minutes by the laser light irradiation. The effectiveness of this method has been reported by ;
15 the inventors in the bulletin of Japan Society of Laser Medicine, vol.
6, No. 3 (January 1986), pp. 71-76 & 347-350.
On the other hand, considerable attention has been paid to laser-chemical therapies including the method reported in 1987 by ~ougherty et al of the United States. According to this method, 48 2 0 hours after an intravenous injection of a hematoporphyrin derivative (HpD), weak laser light such as argon laser or argon pigment laser is irradiated against a target area of the treatment.
Whereupon oxygen of the primaly term which has a strong carcinostatic action is produced by HpD. Since then, there have 2 S been published various reports in this regard, including the one in the buIletin of Japan Society of Laser Medicine, vol. 6, NQ. 3 ; ~(January 1986), pp 113-116. In this connection, it has also been known in the art to use "pheophobide a" as a photo-reactant.
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Further, recently, YAG laser has been pllt into use as a laser light source.
~ n the abave mentioned medical treatment, it is important that the laser light is irradiated uniformly for the cancer tissues and, in S case of the thermal therapy, it is particularly important that the cancer tissues are heated uniformly However, it is difficult to irradiate the laser light uniformly and it is further difficult to irradiate against broad target area.
Therefore, a following method should be carried Ollt;
The laser light is irradiated many times against each small part -of the target area separately so that the whole target area can be irradiated. Accordingly, it takes long time to perform the medical operation.
IJnder these circumstances, laser light irradiation apparatus having a plural number of laser light emitters or probes were studied. With apparatus of this type, each laser light emitted from each probe is irradiated simultaneously against the tissues. Such laser light irradiation apparatus was shown also by the inventor in his Japanese Patent Application No. 62-50723.
2 0 It is sure that the laser light can be irradiated against the tissues uniformly to some degree with these app~rat-ls. However, unifiormity is not enough. On the other hand, the plural number of laser light conduction passages and probes, ~urther, a controller for the passages and the probes are necessary in these apparatus.
2 5~ l'herefore, an increase in cost is produced.
It is there~ore a main object of the pre~ent invention to provicle inexpensive laser light irradiation apparatus by which laser light can be irradiated against living tissues uniformly.
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Disclosure__of_ the Invention In order to solve the above mentioned problems, laser light irradiation apparatus of the present invention comprises a laser light penetrating member and at least one laser light transmitting S member through which laser light goes so as to be fed into the penetrating member. Then, the laser light penetrating member contains laser light scattering particles and is fabricated from a laser light penetrating synthetic material.
In order to heat the tissues efficiently, a lead wire for detecting a temperature shou1d be brought into contact with the treated tissues for temperature control.
Then, for heating the tissues, in laser light irradiation apparatus comprising the laser light penetrating member and at least one laser light transmitting member through which the laser light goes so as to be fed into ~he penetrating member, the 1aser light penetrating member contains laser light scattering particles and is fabricated from a laser lîght penetrating synthetic material, further the lead wire for detecting the temperature is preferably provided. This lead wire is inserted through the penetrating member so as to be projected from the external surface of the fore - -end portion of the penetrating member and whose inserting part is buried in the synthetic materia1 of the penetrating member.
Now, comparing the prior art, the advantages of the present invention will be described.
Almost all of contact probes, which had been invented by the inventor, are fabricated from a ceramic material such as sapphire .. .. .
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and the like. In this case, for the ef~lcient laser light irradiation, there were only following methods; the surface of the probe was roughened or a laser light scattering surface 1ayer was provided on the surface of the probe.
S Since the probe fabricated from the ceramic material is excellent in heat resistance, the probe can be used effectively when the heat resistance is required. However, when the tis~ues are just heated in a thermal therapy and the like as described above, high power level of the laser light is not required. That is to say, the I O probe can be worked sufflciently with low power level of the laser light.
As the result of researches by the inventor, a synthetic material is found to be used for the probe as the penetrating member in the present invention. Then, by fabricating the synthetic material containing laser light scattering particles to be a predetermined shape, the laser light fed into the probe is scattered with the scattering particles in the probe. Therefore, the laser light is emitted in various directions from the surface of the probe. This --produces a large area of laser light irradiation. Further, since the 2 0 probe is fabricated from the synthetic material, the probe has also an advantage that it can be formed to be many types of suitable shapes according to the usage of the probe.
The lead wire for detecting the temperature in the tissues is necessary for controlling the temperature for a suitable medical 2 5 treatment. Therefore, the probe can be formed from the synthetic material so that the lead wire for detecting the temperature such as the lead wire having a thermocouple at its fore end can be inserted throu~h the probe. In this case, the tenlperature is required to be - . . , i ~, . . .
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detected at a position, which exists inside of the tissues and which is adjacent to the fore end of the probe being brought into contact with the surface of the tissues. Then, according to the present invention, detecting the temperature can be carried out precisely due to the suitable location of the lead wire. However, in the prior art, the temperature at the above mentioned position can not be detected by following reasons;
~n the prior art, it has been known that the lead wire is provided separately with a probe or a balloon. Therefore, the thermocouple attached to the fore end of the lead wire is set to be inserted into the tissues at the side part of the probe. That is to say, the thermocouple can not be set the above mentioned position in the tissues due to the unsuitable location of the lead wire.
Accordingly, it is impossible to detect the temperature at the above mentioned precise position. A1ternatively, it has been known that the lead wire is passed around and attached from the side surface to the tip end of the probe and the fore end of the lead wire is attached to the tip end of the probe. By this method, the temperature at a point on the surface of the tissues adjacent to the fore end of the contacted probe can be detected. However, the detected temperature is that of the surface of the tissues or is not that of the inside of the tissues. As a result, by the conventional methods, it is impossible to detect the temperature at the precise position.
2 S However, in the present invention, since the penetrating member or the probe is fabricated from the synthetic material, the probe can be formed so that the lead wire can be inserted through and buried in the synthetic material of the probe. The lead wire : :
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7 2 ~i ~ 7 .9 2 has the thermocouple at its fore end. Further, since the fore end of the lead wire is projected from the external surface of the fore end portion of the probe, when the probe is brought into contact with the tissues, the fore end of the lead wire can be inserted into the S tissues together with the fore end of the probe. Accordingly, by apparatus of the present invention, the temperature at the precise position, which is adjacent to the fore end of the contacted probe and which exists inside of the tissues, can be detected. That is to say, the probe is excel1ent in temperature control for heating the I 0 tissues.
Brief Descript;on of the Dra~win~s ;
Fig. 1 is a longitudinal sectional view of an important part of laser light irradiation apparatus in a f1rst embodiment related to the present invention; Fig. 2 is a side view taken on line II-Il of Fig.
15 l; Fig. 3 is a perspective i11ustration showing an embodiment of local thermal therapy for cancer tissues with laser light irradiation apparatus of the first embodiment and the temperature distribution diagram with this apparatus; Fig. 4 is a longitudinal sectional view of an important part of 1aser 1ight irradiation apparatus in a second 20 embodiment; Fig. S is a side view of apparatus of Fig. 4 from the left side; Fig. 6 is a longitudinal sectional view of 1aser light irradiation apparatus in a third embodiment; Pig. 7 is a longitudinal sectiona1 view of an important part of 1aser 1ight irradiation apparatus in a fourth embodiment; Fig. 8 is a longitudinal sectional view of an 2 5 important part of 1aser light irradiation apparatus in a fifth embodiment; Fig. 9 is a longitudinal sectional view showing an .. ~
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embodiment of forming fl guide in the tissues prior to inserting of laser ligh2 irradiation apparatus of Fig. 8.
The Best Mode to Carrv Out the Invention Now, the present invention is described more particularly with 5 several kinds of embodiments.
Fig. I shows a first embodiment. An optical fiber 1, which serves as a laser light transmitting member, is surrounded by a sheath tube 2, which is fabricated from the resin of tetrafluor-ethylene and the like. The fore end portion of the optical fiber I is 10 inserted through a nipple 3, which is fabricated from a synthetic material such as polyethylene and the 1ike. A lead wire 4 for detecting a temperature has a thermocouple 4a at its fore end.
Then, this lead wire 4 is provided along the optical fiber 1 and is also inserted through the nipple 3.
A flexible protective tube S, which is fabricated from the resin of tetrafluorethylene and the like, is connected to the back end of the nipple 3. The back end of the optical fiber 1 is optically connected to a laser light generator (not shown). The lead wire 4 for detecting tbe temperature is connected to a temperature 20 measuring unit (not shown). Then, according to the result of detecting the temperature, the power level of the laser light, which is fed into the optical fiber 1 from the laser light generator, should be contro11ed. This control is calTied out by, for example, adjusting a timer switch, which is provided between the laser light generator 25 and the back end of the optical fiber 1.
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_ 9 _ On the other hand, the fore end portion of the nipple 3 is -connected to a holder 6 by means of a screw. The holder 6 at itS
fore end portion, holds a probe 7 as a laser light penetrating member.
S The holder 6 comprises a body 6A, which is tapered toward its back end, and a sleeve-like connector 6B, which has a hollow shape and which is projected from the body 6A. The screw of the nipple 3 is adapted to mate with a connecting screw hole 6C of the holder 6 for connection. The optical fiber 1 and the lead wire 4 for detecting ~, -the temperature are inserted through the body 6A. The probe 7 composes a substantial cylindrical part with a fore end circumference being rounded off and another cylindrical part at the back side of the substantial cylindrical part llaving a smaller radius by the thickness of the sleeve-like connector 6B. The smaller cylindrical part of the probe 7 is fitted in the sleeve-like connector 6B, further might be fixed integra11y thereto by using an adhesive between the mating surfaces; a circumferential bottom face of the larger cylindrical part of the probe 7 and the top circumferential face of the sleeve-like connector 6B for high strength in ffxing.
A laser light reflective layer 8 is formed on the mating surfaces -of the probe 7 and the holder 6, in this embodiment, the circu1ar front face of the body 6A and the internal side face of the sleeve-like connector 6B. Although the reflective layer 8 is preferably gold plated to give high heat resistance, it might be aluminum plated and the like in view of the material of the layer. For forming the layer, vapor-deposit as well as plating can be used.
Further, the fore end porlion of the optical fiber 1 is inserted to ~be buried in the synthetic material of the probe 7 and the fore end ,.- -. ~. ~ . ..... . .......... ~ . . . - . , ..
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of the core of the optical fiber I is contacted with the synthetic material of the probe 7 directly without any gap. The fore end portion of the lead wire 4 for detecting the temperature is inserted through the probe 7 so as to be projected from the external surface S of the fore end portion of the probe 7 and has a sharpened tip end for inserting into the tissues easi1y.
The probe of the present invention contains laser light scattering particles and is fabricated from the 1aser light penetrating synthetic material. The material is synthetic resin such 10 as silicone resin, acrylic resin (more preferàbly, methyl metha-acrylate resin), carbonate resin, polyamide resin, polyethylene resin, urethane resin, polyester resin and the like, more preferably, thermoplastic synthetic resin. For the scattering particles, the material, which has a larger refi~active index for the laser light than 15 that of the above mentioned synthetic material of the probe, is used, for example, a natura1 or artificial material such as diamond, sapphire, quartz material, single crystal zirconium oxide, laser light penetrating synthetic resin having heat resistance (it is needless to say that it is different from the above mentioned synthetic resin 20 material of the probe), laser 1ight reflective metal (such as gold, aluminum and the like)9 and these particles on whose surface the above mentioned laser light reflective metal is coated to be a compound material.
On the other hand, if desir~d, when the probe contains laser 2 5 light absorbing particles such as carbon9 graphite, iron oxide, manganese dioxide and the like together with the laser light scattering particles, the laser light is impinged on the absorbing , . . ~ - . . ~ ............... . . .
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particles to generate heat energy while the laser light is scattered in the probe to be emitted from the probe.
The probe 7 of the present invention is made by moulding to be a desired shape from the synthetic material, which is in a molten S state and into which the scattering particles are dispersed. ln the present invention, the fore end portion of the optical fiber 1 is buried in ~he synthetic materia1 of the probe 7 as shown in Fig. 1 and the middle part of the lead wire 4 for detecting the temperature is buried in the synthetic material of the probe 7 so as 10 to be fixed integrally to the probe 7. Accordingly, for fabricating this apparatus, for example, the ho1der 6 is made easily by moulding ~rom one mould to which the material is poured, while the optical fiber 1 and the lead wire 4 are projected from the body 6A of the holder 6. -Laser light irradiation apparatus of this type is used, for example, in a following manner. This apparatus is connected to an endoscope and inserted to a treated target area in a human body.
At the same time, the laser light is generated from the laser light generator. Then, the laser light from the laser light generator is fed 20 into the back end of the optical ~Iber 1 and is transmitted therein to be emitted from the fore end of the optical fiber l. Continuously, the emitted laser light is fed into the probe 7 directly and is penetrated therein to be emitted from its external surface, while the laser light is refracted on the scattering particles many times in 25 the probe 7. Therefore, as shown in Fig. 1, the laser light, after the many refraction, is emitted from the external surface of the probe 7 uniformly against the tissues. In this case, as shown in Fig. l, the - laser light reaching at the internal sur~ace of the holder 6 is ' :' , '' ' ' , ' ' . ' ............... 1, ' , ~ ' ~ ~ , . .-: - : . .
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reflected on the reflection 1ayer 8. Therefore, the metal holder 6 is prevented from being heated and from being damaged, further, the reflected laser light is brought to go forward.
Fig. 3 shows an embodiment where cancer tissues M are 5 treated by a local thermal therapy with the probe 7 of the first embodiment. In this therapy, the external surface of the fore end of the probe 7 is brought into contact with the cancer tissues M.
Then, the fore end portion of the lead wire 4 for detecting the temperature is projected from the external surface of the fore end 10 portion of the probe 7 and is inserted into the tissues M. The temperature of the tissues M is detected with the thermocouple 4a for controlling the power level of the laser light fed into the optical fiber 1. In other words, the power level of the laser light emitted -from the external surface of the probe 7 is controlled as described 15 before. Then, the cancer tissues M are destroyed by keeping its temperature at about 42-44C.
On the other hand, the 1aser light is irradiated against also the lead wire 4 for detecting the temperature in the probe 7.
Therefore, in order to prevent the lead wire 4 from being to be 20 heated and from being to be damaged, the wire 4 is preferably coated with a laser light reflecting layer such as a gold plated layer and a titanium coating layer.
Figs. 4 and 5 show the second embodiment. The side face of a ~ -probe 10 is tapered toward the back end of the probe 10 to be a -2 S ~ substant~ally truncated cone sh~e. Plural number of optical fibers I are provided in the probe 107 while the fore ends of the optical fibers I are buried in the synthetic material of the probe 10. In this embodiment, three optica1 fibers 1 are provided SQ that the --~ : , ., 2. ~ ~ 7 ~
fibers 1 are deflected toward the circumference of the fore end portion of the probe 10 to be apart each other from the back end of the probe 10 and, in a side view, the three fore ends of the fibers I
are disposed circumferentially with the same angular space of 120, 5 as shown in Fig. 5. A holder 11 held by a medical operator directly has a fore end part, which is tapered towards the back end of the probe 10 so that the probe 10 can be fitted in the fore end part of the holder 11. A laser light reflecting layer 12 such as a gold plate 1ayer is provided on the inner side surface of the tapered fore end 10 part of the ho1der 11. A lead wire 13 is provided for detecting a temperature. Laser light irradiation apparatus of this second embodiment is mainly suitable for the laser light irradiation against the skin layer of a human body.
In the present invention, since the probe is fabricated from the 15 synthetic resin material, comparing with a ceramic material, it is much easier to mould the material to be a desired shape.
Therefore, as shown in the third embodiment of Fig. 6, the material can be moulded to be a probe lOA having an elaborated shape suitable for, for example, a treatment for uterin cancers formed 20 adjacent to the cervical os of an uterin U.
In Fig 6 showing the third embodiment and Fig. 7 showing the fourth embodiment, each 1ead wire 4 for detecting the temperature is not ~rojected from the external surface~ of the fore end portion of the probe lOA or a probe 7. That is to say, each fore end portion of 25 each 1ead wire remains to be buried in the synthetic material of the probe lOA or the probe 7. In this case, if the relation of the temperature in the treated tissues and the temperature in the probe IOA or the probe 7 is known, the temperature of the tissues . . ~ . , . , .. .. . , :
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,~ , - 1 4 - ~ ~ ~ 7 can be controlled by detecting the temperature in the probe I OA or in the probe 7, although the degree of accuracy in this control is more or less lowered.
Fig. 8 shows the fifth embodiment. In this embodiment, 5 apparatus is used effectively in a treatment not for the surface of tissues but for inside of the tissues.
At the fore end portion of an optical fiber 20, a clad 20B is removed so that a core 20A is exposed. The tip end of the core 20A
is tapered. A laser light scattering layer is formed on almost all of 10 the external surface of the core 20A. In this figure, this laser light scattering 1ayer is directed by marking dots. For forming this scattering layer, ~Irst, ceramic powders such as silicon dioxide and the like are sprayed and heated to a temperature which is slightly lower than its melting point. Therefore, the original sprayed 15 powders do not become to be homogeneous due to incomplète heating. Then, these incompletely heated ceramic powders are cooled. Accordingly, the laser light scattering layer can be formed - on me core 20A, where the powders pa~tly melt and partly remain.
Due to this scattering 1ayer, when the laser light is emitted from the 20 external surface of the core 20A, the laser light impinges on eacl resulting ceramic powder with refraction to be scattered.
On the other hand, a probe 21 is provided so as to surround the core 20A covered with this scattering layer. The probe 21 is ~abricated from a synthetic material containing scattering particles 2 5 in the same manner as the first embodiment.
The external surface of a lead wire 22 for detecting a temperature is gold p1ated. Then, the fore end of the lead wire 22 fixed to the optical fiber 20 locates adjacent to the back end of the - . . . ,............... . . :
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probe 21. The lead wire 22 together with the optical fiber 20 is surrounded by a flexible sheath 23, which is fabricated from synthetic resin such as polyethylene~ urethane and the like, silicone rubber and so on By moulding, the sheath 23 is ~Ixed integrally to the lead wire 22, the optica1 fiber 20 and the probe 21.
In case of applying this apparatus of the ~1fth embodiment, as shown in Fig. 9, first, a so-called puncture needle 31 together with a guide tube 30 is inserted into the tissues M such as liver tissues.
Next, only the puncture needle 31 is removed. Then, instead of the needle 31, the fore end portion of this laser light irradiation apparatus is inserted into the tissues M so as to go through the guide tube 30. Continuously, the laser light is fed into the optica1 fiber 20 to be emitted from the core 20A provided at the fore end portion of the optica1 fiber 20. Then, the laser light is scattered in the scattering layer covering the core 20A. Then, the scattered and emitted laser light is fed into t~se probe 21 and goes through it, while the laser light is scattered many times with the scattering particles in the probe 21. At 1ast~ the laser light is emitted from the external surface of the probe 21 uniformly. This apparatus is applied for a local thermal therapy for cancer tissues in a liver, encephalic malignant tumors and cancer tissues in a breast.
The scattering particles contained in the scattering layer are in princip1e the same as the above mentioned scattering particles in the probe. However, the particles, which can not make a film when 2 5 they melt, are not suitable, thus, ceramic partic1es are generally used for tbe scattering particles.
Further, if desired, a surface layer might be formed on each surface of the above mentioned several kinds of probes or the .
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above mentioned scattering surface layer covered on the core 20A
to give a high scattering effect. This surface layer contains the light scattering particles, which have the larger refractive index than that of the material of the probe or the above mentioned synthetic S material, such as sapphire, silicon dioxide, aluminum oxide and the like, the laser light absorbing particles, which can be included in the probe as described before, such as carbon and the like and a binder, which sticks the particles to each surface and forms a ~llm on the surface as dçscribed hereinafter.
The laser light is scattered with the laser light scattering particles, further, when the laser light impinges on the laser light absorbing particles, the greater part of the energy of the laser light is converted to heat energy.
Therefore, as the vaporization of the tissues is accelerated, the 15 tissues can be incised with a low energy of the laser light penetrated into the probe. Accordingly, when the tissues are incised, the probe can be moved rapidly. Further, since the required energy of the laser light penetrating into the probe is low, ., .
the medical operation can be carried in short time with a cheap and 2 0 small scaled laser light generator.
On the other hand, referring to the surface layer, if a dispersion containing the laser light absorbing particles and the light scattering particles is coated on the surface of the probe, after a vaporization of a dispersion medium, the contact of the probe having the sur~ace 25 layer with the tissues or other substances causes a damage to the surface layer, because the both kinds of particles are attached to the surface of the probe only by physical adsorptive power.
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Therefore, by the binder which sticks the laser light absorbing particles and the light scattering particles to the surface of the probe, an adhesion of the surface layer to the probe is enhanced. In this case, the binder is preferably made of light penetrating S particles such as synthetic particles or ceramic particles such as quartz particles and the like. For forming the film, when the .-synthetic particles are used as the material of the binder, the particles should be melted, or when the ceramic particles having a higher melting point than that of the probe are used, the surface of .-~'.
the probe should be me1ted. ~-.
Further, by forming a rough surface on the surface of the probe or by forming the above mentioned surface layer on the rough :
surface, the laser light can be irradiated more effectively, because, - ' . ;' the laser light is scattered on the rough surface when the iaser light : l S is~ emitted. If desired, the rough surface is formed on the core 20A, ~ ' ' . further the above mentioned scattering layer might be formed on .' the rough surface.
Although, in each embodiment described before, the fore end of the :optical fiber is buried :in the synthetic mlaterial of the probe, 20~ t he~ fore end of the~optical fiber ~might be 10c~ted so as to be apart from the back end of ~the probe. However, an exception is the émbodiment~of Fig. ~8, becauso the scattering layer in this '' '-embodi~:ment~is~formed on:~the'surface: of the core and the probe is ? ~ ~ ~`set;~to`~:bé~ rovidod so:as to surround the core. Then, în case of 2~5~ providing 'a~ :gap~ betwoen the~ fore end of the optical fiber and the ba~c~k~é~n~d~of tho~probe~:of~tho~:present invention other than the probe in~ ~the~'.ènibodiment of ~ Fig.~ ~8, impuritios ~such ~as~ dusts and the like . ' ';'are:'pmd~uced:in the~gap,:~further, the:impurities are attached to the - 18 - 2~ 2i~
surfaces of the back end of the probe and the ~re end of the optical ~Iber or fibers. Accordingly, since the laser light is impinged on the impurities, the surfaces of the back end of the probe are heated.
That is to say, the power level of the laser light fed into the probe is 5 lowered. Therefore, the fore end of the optical fiber is preferably buried in the synthetic material of the probe.
Industrial Utilization .. . , ._ ~ . . ............................ ...
As a result, by above mentioned laser light irradiation apparatus of the present invention, the penetrating member can be 10 fabricated to be a desired shape easily, decrease in cost for fabricating apparatus is attained and the lead wire for detecting the temperature can be placed so as to be suitable for each medical treatment, further, the laser light can be irradiated against the living tissues uniformly.
.
Prior Art Medical treatments such as incisions of living tissues of animal organisms by laser light irradiation are conspicuous due to its ability of hemostasis in these days.
It had been the conventional method that the laser light was irradiated ~om the fore end of an optical fiber which is brought out --2û of contact with the living tisxues. But this method causes severe damage to members of the optical fiber. Therefore, a method which has boen utilized lately is as follows;
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First, laser light is transmitted into an optical ~Iber, whose fore end portion locates adjacent to treated living tissues. Next, the laser light is fed into an emitting probe from the op~ical fiber. This emitting probe is brought into or out of contact with the living 5 tissues. Then, the laser light is emitted from the surface of the probe for irradiating against th~ living tissues. (hereafter "living tissue" is sometimes expressed by "tissue" only).
The inventor developed many kinds of contact probes which are utilized for various purposes.
10Further, lately, localized thermal therapy is drawing special attention as a carcinostatic therapy. According to this method, cancer tissues are destroyed by keeping the cancer tissues at a temperature of about 42-44C for 10-25 minutes by the laser light irradiation. The effectiveness of this method has been reported by ;
15 the inventors in the bulletin of Japan Society of Laser Medicine, vol.
6, No. 3 (January 1986), pp. 71-76 & 347-350.
On the other hand, considerable attention has been paid to laser-chemical therapies including the method reported in 1987 by ~ougherty et al of the United States. According to this method, 48 2 0 hours after an intravenous injection of a hematoporphyrin derivative (HpD), weak laser light such as argon laser or argon pigment laser is irradiated against a target area of the treatment.
Whereupon oxygen of the primaly term which has a strong carcinostatic action is produced by HpD. Since then, there have 2 S been published various reports in this regard, including the one in the buIletin of Japan Society of Laser Medicine, vol. 6, NQ. 3 ; ~(January 1986), pp 113-116. In this connection, it has also been known in the art to use "pheophobide a" as a photo-reactant.
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Further, recently, YAG laser has been pllt into use as a laser light source.
~ n the abave mentioned medical treatment, it is important that the laser light is irradiated uniformly for the cancer tissues and, in S case of the thermal therapy, it is particularly important that the cancer tissues are heated uniformly However, it is difficult to irradiate the laser light uniformly and it is further difficult to irradiate against broad target area.
Therefore, a following method should be carried Ollt;
The laser light is irradiated many times against each small part -of the target area separately so that the whole target area can be irradiated. Accordingly, it takes long time to perform the medical operation.
IJnder these circumstances, laser light irradiation apparatus having a plural number of laser light emitters or probes were studied. With apparatus of this type, each laser light emitted from each probe is irradiated simultaneously against the tissues. Such laser light irradiation apparatus was shown also by the inventor in his Japanese Patent Application No. 62-50723.
2 0 It is sure that the laser light can be irradiated against the tissues uniformly to some degree with these app~rat-ls. However, unifiormity is not enough. On the other hand, the plural number of laser light conduction passages and probes, ~urther, a controller for the passages and the probes are necessary in these apparatus.
2 5~ l'herefore, an increase in cost is produced.
It is there~ore a main object of the pre~ent invention to provicle inexpensive laser light irradiation apparatus by which laser light can be irradiated against living tissues uniformly.
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Disclosure__of_ the Invention In order to solve the above mentioned problems, laser light irradiation apparatus of the present invention comprises a laser light penetrating member and at least one laser light transmitting S member through which laser light goes so as to be fed into the penetrating member. Then, the laser light penetrating member contains laser light scattering particles and is fabricated from a laser light penetrating synthetic material.
In order to heat the tissues efficiently, a lead wire for detecting a temperature shou1d be brought into contact with the treated tissues for temperature control.
Then, for heating the tissues, in laser light irradiation apparatus comprising the laser light penetrating member and at least one laser light transmitting member through which the laser light goes so as to be fed into ~he penetrating member, the 1aser light penetrating member contains laser light scattering particles and is fabricated from a laser lîght penetrating synthetic material, further the lead wire for detecting the temperature is preferably provided. This lead wire is inserted through the penetrating member so as to be projected from the external surface of the fore - -end portion of the penetrating member and whose inserting part is buried in the synthetic materia1 of the penetrating member.
Now, comparing the prior art, the advantages of the present invention will be described.
Almost all of contact probes, which had been invented by the inventor, are fabricated from a ceramic material such as sapphire .. .. .
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and the like. In this case, for the ef~lcient laser light irradiation, there were only following methods; the surface of the probe was roughened or a laser light scattering surface 1ayer was provided on the surface of the probe.
S Since the probe fabricated from the ceramic material is excellent in heat resistance, the probe can be used effectively when the heat resistance is required. However, when the tis~ues are just heated in a thermal therapy and the like as described above, high power level of the laser light is not required. That is to say, the I O probe can be worked sufflciently with low power level of the laser light.
As the result of researches by the inventor, a synthetic material is found to be used for the probe as the penetrating member in the present invention. Then, by fabricating the synthetic material containing laser light scattering particles to be a predetermined shape, the laser light fed into the probe is scattered with the scattering particles in the probe. Therefore, the laser light is emitted in various directions from the surface of the probe. This --produces a large area of laser light irradiation. Further, since the 2 0 probe is fabricated from the synthetic material, the probe has also an advantage that it can be formed to be many types of suitable shapes according to the usage of the probe.
The lead wire for detecting the temperature in the tissues is necessary for controlling the temperature for a suitable medical 2 5 treatment. Therefore, the probe can be formed from the synthetic material so that the lead wire for detecting the temperature such as the lead wire having a thermocouple at its fore end can be inserted throu~h the probe. In this case, the tenlperature is required to be - . . , i ~, . . .
- .
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detected at a position, which exists inside of the tissues and which is adjacent to the fore end of the probe being brought into contact with the surface of the tissues. Then, according to the present invention, detecting the temperature can be carried out precisely due to the suitable location of the lead wire. However, in the prior art, the temperature at the above mentioned position can not be detected by following reasons;
~n the prior art, it has been known that the lead wire is provided separately with a probe or a balloon. Therefore, the thermocouple attached to the fore end of the lead wire is set to be inserted into the tissues at the side part of the probe. That is to say, the thermocouple can not be set the above mentioned position in the tissues due to the unsuitable location of the lead wire.
Accordingly, it is impossible to detect the temperature at the above mentioned precise position. A1ternatively, it has been known that the lead wire is passed around and attached from the side surface to the tip end of the probe and the fore end of the lead wire is attached to the tip end of the probe. By this method, the temperature at a point on the surface of the tissues adjacent to the fore end of the contacted probe can be detected. However, the detected temperature is that of the surface of the tissues or is not that of the inside of the tissues. As a result, by the conventional methods, it is impossible to detect the temperature at the precise position.
2 S However, in the present invention, since the penetrating member or the probe is fabricated from the synthetic material, the probe can be formed so that the lead wire can be inserted through and buried in the synthetic material of the probe. The lead wire : :
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7 2 ~i ~ 7 .9 2 has the thermocouple at its fore end. Further, since the fore end of the lead wire is projected from the external surface of the fore end portion of the probe, when the probe is brought into contact with the tissues, the fore end of the lead wire can be inserted into the S tissues together with the fore end of the probe. Accordingly, by apparatus of the present invention, the temperature at the precise position, which is adjacent to the fore end of the contacted probe and which exists inside of the tissues, can be detected. That is to say, the probe is excel1ent in temperature control for heating the I 0 tissues.
Brief Descript;on of the Dra~win~s ;
Fig. 1 is a longitudinal sectional view of an important part of laser light irradiation apparatus in a f1rst embodiment related to the present invention; Fig. 2 is a side view taken on line II-Il of Fig.
15 l; Fig. 3 is a perspective i11ustration showing an embodiment of local thermal therapy for cancer tissues with laser light irradiation apparatus of the first embodiment and the temperature distribution diagram with this apparatus; Fig. 4 is a longitudinal sectional view of an important part of 1aser 1ight irradiation apparatus in a second 20 embodiment; Fig. S is a side view of apparatus of Fig. 4 from the left side; Fig. 6 is a longitudinal sectional view of 1aser light irradiation apparatus in a third embodiment; Pig. 7 is a longitudinal sectiona1 view of an important part of 1aser 1ight irradiation apparatus in a fourth embodiment; Fig. 8 is a longitudinal sectional view of an 2 5 important part of 1aser light irradiation apparatus in a fifth embodiment; Fig. 9 is a longitudinal sectional view showing an .. ~
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embodiment of forming fl guide in the tissues prior to inserting of laser ligh2 irradiation apparatus of Fig. 8.
The Best Mode to Carrv Out the Invention Now, the present invention is described more particularly with 5 several kinds of embodiments.
Fig. I shows a first embodiment. An optical fiber 1, which serves as a laser light transmitting member, is surrounded by a sheath tube 2, which is fabricated from the resin of tetrafluor-ethylene and the like. The fore end portion of the optical fiber I is 10 inserted through a nipple 3, which is fabricated from a synthetic material such as polyethylene and the 1ike. A lead wire 4 for detecting a temperature has a thermocouple 4a at its fore end.
Then, this lead wire 4 is provided along the optical fiber 1 and is also inserted through the nipple 3.
A flexible protective tube S, which is fabricated from the resin of tetrafluorethylene and the like, is connected to the back end of the nipple 3. The back end of the optical fiber 1 is optically connected to a laser light generator (not shown). The lead wire 4 for detecting tbe temperature is connected to a temperature 20 measuring unit (not shown). Then, according to the result of detecting the temperature, the power level of the laser light, which is fed into the optical fiber 1 from the laser light generator, should be contro11ed. This control is calTied out by, for example, adjusting a timer switch, which is provided between the laser light generator 25 and the back end of the optical fiber 1.
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_ 9 _ On the other hand, the fore end portion of the nipple 3 is -connected to a holder 6 by means of a screw. The holder 6 at itS
fore end portion, holds a probe 7 as a laser light penetrating member.
S The holder 6 comprises a body 6A, which is tapered toward its back end, and a sleeve-like connector 6B, which has a hollow shape and which is projected from the body 6A. The screw of the nipple 3 is adapted to mate with a connecting screw hole 6C of the holder 6 for connection. The optical fiber 1 and the lead wire 4 for detecting ~, -the temperature are inserted through the body 6A. The probe 7 composes a substantial cylindrical part with a fore end circumference being rounded off and another cylindrical part at the back side of the substantial cylindrical part llaving a smaller radius by the thickness of the sleeve-like connector 6B. The smaller cylindrical part of the probe 7 is fitted in the sleeve-like connector 6B, further might be fixed integra11y thereto by using an adhesive between the mating surfaces; a circumferential bottom face of the larger cylindrical part of the probe 7 and the top circumferential face of the sleeve-like connector 6B for high strength in ffxing.
A laser light reflective layer 8 is formed on the mating surfaces -of the probe 7 and the holder 6, in this embodiment, the circu1ar front face of the body 6A and the internal side face of the sleeve-like connector 6B. Although the reflective layer 8 is preferably gold plated to give high heat resistance, it might be aluminum plated and the like in view of the material of the layer. For forming the layer, vapor-deposit as well as plating can be used.
Further, the fore end porlion of the optical fiber 1 is inserted to ~be buried in the synthetic material of the probe 7 and the fore end ,.- -. ~. ~ . ..... . .......... ~ . . . - . , ..
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of the core of the optical fiber I is contacted with the synthetic material of the probe 7 directly without any gap. The fore end portion of the lead wire 4 for detecting the temperature is inserted through the probe 7 so as to be projected from the external surface S of the fore end portion of the probe 7 and has a sharpened tip end for inserting into the tissues easi1y.
The probe of the present invention contains laser light scattering particles and is fabricated from the 1aser light penetrating synthetic material. The material is synthetic resin such 10 as silicone resin, acrylic resin (more preferàbly, methyl metha-acrylate resin), carbonate resin, polyamide resin, polyethylene resin, urethane resin, polyester resin and the like, more preferably, thermoplastic synthetic resin. For the scattering particles, the material, which has a larger refi~active index for the laser light than 15 that of the above mentioned synthetic material of the probe, is used, for example, a natura1 or artificial material such as diamond, sapphire, quartz material, single crystal zirconium oxide, laser light penetrating synthetic resin having heat resistance (it is needless to say that it is different from the above mentioned synthetic resin 20 material of the probe), laser 1ight reflective metal (such as gold, aluminum and the like)9 and these particles on whose surface the above mentioned laser light reflective metal is coated to be a compound material.
On the other hand, if desir~d, when the probe contains laser 2 5 light absorbing particles such as carbon9 graphite, iron oxide, manganese dioxide and the like together with the laser light scattering particles, the laser light is impinged on the absorbing , . . ~ - . . ~ ............... . . .
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particles to generate heat energy while the laser light is scattered in the probe to be emitted from the probe.
The probe 7 of the present invention is made by moulding to be a desired shape from the synthetic material, which is in a molten S state and into which the scattering particles are dispersed. ln the present invention, the fore end portion of the optical fiber 1 is buried in ~he synthetic materia1 of the probe 7 as shown in Fig. 1 and the middle part of the lead wire 4 for detecting the temperature is buried in the synthetic material of the probe 7 so as 10 to be fixed integrally to the probe 7. Accordingly, for fabricating this apparatus, for example, the ho1der 6 is made easily by moulding ~rom one mould to which the material is poured, while the optical fiber 1 and the lead wire 4 are projected from the body 6A of the holder 6. -Laser light irradiation apparatus of this type is used, for example, in a following manner. This apparatus is connected to an endoscope and inserted to a treated target area in a human body.
At the same time, the laser light is generated from the laser light generator. Then, the laser light from the laser light generator is fed 20 into the back end of the optical ~Iber 1 and is transmitted therein to be emitted from the fore end of the optical fiber l. Continuously, the emitted laser light is fed into the probe 7 directly and is penetrated therein to be emitted from its external surface, while the laser light is refracted on the scattering particles many times in 25 the probe 7. Therefore, as shown in Fig. 1, the laser light, after the many refraction, is emitted from the external surface of the probe 7 uniformly against the tissues. In this case, as shown in Fig. l, the - laser light reaching at the internal sur~ace of the holder 6 is ' :' , '' ' ' , ' ' . ' ............... 1, ' , ~ ' ~ ~ , . .-: - : . .
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reflected on the reflection 1ayer 8. Therefore, the metal holder 6 is prevented from being heated and from being damaged, further, the reflected laser light is brought to go forward.
Fig. 3 shows an embodiment where cancer tissues M are 5 treated by a local thermal therapy with the probe 7 of the first embodiment. In this therapy, the external surface of the fore end of the probe 7 is brought into contact with the cancer tissues M.
Then, the fore end portion of the lead wire 4 for detecting the temperature is projected from the external surface of the fore end 10 portion of the probe 7 and is inserted into the tissues M. The temperature of the tissues M is detected with the thermocouple 4a for controlling the power level of the laser light fed into the optical fiber 1. In other words, the power level of the laser light emitted -from the external surface of the probe 7 is controlled as described 15 before. Then, the cancer tissues M are destroyed by keeping its temperature at about 42-44C.
On the other hand, the 1aser light is irradiated against also the lead wire 4 for detecting the temperature in the probe 7.
Therefore, in order to prevent the lead wire 4 from being to be 20 heated and from being to be damaged, the wire 4 is preferably coated with a laser light reflecting layer such as a gold plated layer and a titanium coating layer.
Figs. 4 and 5 show the second embodiment. The side face of a ~ -probe 10 is tapered toward the back end of the probe 10 to be a -2 S ~ substant~ally truncated cone sh~e. Plural number of optical fibers I are provided in the probe 107 while the fore ends of the optical fibers I are buried in the synthetic material of the probe 10. In this embodiment, three optica1 fibers 1 are provided SQ that the --~ : , ., 2. ~ ~ 7 ~
fibers 1 are deflected toward the circumference of the fore end portion of the probe 10 to be apart each other from the back end of the probe 10 and, in a side view, the three fore ends of the fibers I
are disposed circumferentially with the same angular space of 120, 5 as shown in Fig. 5. A holder 11 held by a medical operator directly has a fore end part, which is tapered towards the back end of the probe 10 so that the probe 10 can be fitted in the fore end part of the holder 11. A laser light reflecting layer 12 such as a gold plate 1ayer is provided on the inner side surface of the tapered fore end 10 part of the ho1der 11. A lead wire 13 is provided for detecting a temperature. Laser light irradiation apparatus of this second embodiment is mainly suitable for the laser light irradiation against the skin layer of a human body.
In the present invention, since the probe is fabricated from the 15 synthetic resin material, comparing with a ceramic material, it is much easier to mould the material to be a desired shape.
Therefore, as shown in the third embodiment of Fig. 6, the material can be moulded to be a probe lOA having an elaborated shape suitable for, for example, a treatment for uterin cancers formed 20 adjacent to the cervical os of an uterin U.
In Fig 6 showing the third embodiment and Fig. 7 showing the fourth embodiment, each 1ead wire 4 for detecting the temperature is not ~rojected from the external surface~ of the fore end portion of the probe lOA or a probe 7. That is to say, each fore end portion of 25 each 1ead wire remains to be buried in the synthetic material of the probe lOA or the probe 7. In this case, if the relation of the temperature in the treated tissues and the temperature in the probe IOA or the probe 7 is known, the temperature of the tissues . . ~ . , . , .. .. . , :
. . . . .. .
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,~ , - 1 4 - ~ ~ ~ 7 can be controlled by detecting the temperature in the probe I OA or in the probe 7, although the degree of accuracy in this control is more or less lowered.
Fig. 8 shows the fifth embodiment. In this embodiment, 5 apparatus is used effectively in a treatment not for the surface of tissues but for inside of the tissues.
At the fore end portion of an optical fiber 20, a clad 20B is removed so that a core 20A is exposed. The tip end of the core 20A
is tapered. A laser light scattering layer is formed on almost all of 10 the external surface of the core 20A. In this figure, this laser light scattering 1ayer is directed by marking dots. For forming this scattering layer, ~Irst, ceramic powders such as silicon dioxide and the like are sprayed and heated to a temperature which is slightly lower than its melting point. Therefore, the original sprayed 15 powders do not become to be homogeneous due to incomplète heating. Then, these incompletely heated ceramic powders are cooled. Accordingly, the laser light scattering layer can be formed - on me core 20A, where the powders pa~tly melt and partly remain.
Due to this scattering 1ayer, when the laser light is emitted from the 20 external surface of the core 20A, the laser light impinges on eacl resulting ceramic powder with refraction to be scattered.
On the other hand, a probe 21 is provided so as to surround the core 20A covered with this scattering layer. The probe 21 is ~abricated from a synthetic material containing scattering particles 2 5 in the same manner as the first embodiment.
The external surface of a lead wire 22 for detecting a temperature is gold p1ated. Then, the fore end of the lead wire 22 fixed to the optical fiber 20 locates adjacent to the back end of the - . . . ,............... . . :
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probe 21. The lead wire 22 together with the optical fiber 20 is surrounded by a flexible sheath 23, which is fabricated from synthetic resin such as polyethylene~ urethane and the like, silicone rubber and so on By moulding, the sheath 23 is ~Ixed integrally to the lead wire 22, the optica1 fiber 20 and the probe 21.
In case of applying this apparatus of the ~1fth embodiment, as shown in Fig. 9, first, a so-called puncture needle 31 together with a guide tube 30 is inserted into the tissues M such as liver tissues.
Next, only the puncture needle 31 is removed. Then, instead of the needle 31, the fore end portion of this laser light irradiation apparatus is inserted into the tissues M so as to go through the guide tube 30. Continuously, the laser light is fed into the optica1 fiber 20 to be emitted from the core 20A provided at the fore end portion of the optica1 fiber 20. Then, the laser light is scattered in the scattering layer covering the core 20A. Then, the scattered and emitted laser light is fed into t~se probe 21 and goes through it, while the laser light is scattered many times with the scattering particles in the probe 21. At 1ast~ the laser light is emitted from the external surface of the probe 21 uniformly. This apparatus is applied for a local thermal therapy for cancer tissues in a liver, encephalic malignant tumors and cancer tissues in a breast.
The scattering particles contained in the scattering layer are in princip1e the same as the above mentioned scattering particles in the probe. However, the particles, which can not make a film when 2 5 they melt, are not suitable, thus, ceramic partic1es are generally used for tbe scattering particles.
Further, if desired, a surface layer might be formed on each surface of the above mentioned several kinds of probes or the .
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above mentioned scattering surface layer covered on the core 20A
to give a high scattering effect. This surface layer contains the light scattering particles, which have the larger refractive index than that of the material of the probe or the above mentioned synthetic S material, such as sapphire, silicon dioxide, aluminum oxide and the like, the laser light absorbing particles, which can be included in the probe as described before, such as carbon and the like and a binder, which sticks the particles to each surface and forms a ~llm on the surface as dçscribed hereinafter.
The laser light is scattered with the laser light scattering particles, further, when the laser light impinges on the laser light absorbing particles, the greater part of the energy of the laser light is converted to heat energy.
Therefore, as the vaporization of the tissues is accelerated, the 15 tissues can be incised with a low energy of the laser light penetrated into the probe. Accordingly, when the tissues are incised, the probe can be moved rapidly. Further, since the required energy of the laser light penetrating into the probe is low, ., .
the medical operation can be carried in short time with a cheap and 2 0 small scaled laser light generator.
On the other hand, referring to the surface layer, if a dispersion containing the laser light absorbing particles and the light scattering particles is coated on the surface of the probe, after a vaporization of a dispersion medium, the contact of the probe having the sur~ace 25 layer with the tissues or other substances causes a damage to the surface layer, because the both kinds of particles are attached to the surface of the probe only by physical adsorptive power.
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Therefore, by the binder which sticks the laser light absorbing particles and the light scattering particles to the surface of the probe, an adhesion of the surface layer to the probe is enhanced. In this case, the binder is preferably made of light penetrating S particles such as synthetic particles or ceramic particles such as quartz particles and the like. For forming the film, when the .-synthetic particles are used as the material of the binder, the particles should be melted, or when the ceramic particles having a higher melting point than that of the probe are used, the surface of .-~'.
the probe should be me1ted. ~-.
Further, by forming a rough surface on the surface of the probe or by forming the above mentioned surface layer on the rough :
surface, the laser light can be irradiated more effectively, because, - ' . ;' the laser light is scattered on the rough surface when the iaser light : l S is~ emitted. If desired, the rough surface is formed on the core 20A, ~ ' ' . further the above mentioned scattering layer might be formed on .' the rough surface.
Although, in each embodiment described before, the fore end of the :optical fiber is buried :in the synthetic mlaterial of the probe, 20~ t he~ fore end of the~optical fiber ~might be 10c~ted so as to be apart from the back end of ~the probe. However, an exception is the émbodiment~of Fig. ~8, becauso the scattering layer in this '' '-embodi~:ment~is~formed on:~the'surface: of the core and the probe is ? ~ ~ ~`set;~to`~:bé~ rovidod so:as to surround the core. Then, în case of 2~5~ providing 'a~ :gap~ betwoen the~ fore end of the optical fiber and the ba~c~k~é~n~d~of tho~probe~:of~tho~:present invention other than the probe in~ ~the~'.ènibodiment of ~ Fig.~ ~8, impuritios ~such ~as~ dusts and the like . ' ';'are:'pmd~uced:in the~gap,:~further, the:impurities are attached to the - 18 - 2~ 2i~
surfaces of the back end of the probe and the ~re end of the optical ~Iber or fibers. Accordingly, since the laser light is impinged on the impurities, the surfaces of the back end of the probe are heated.
That is to say, the power level of the laser light fed into the probe is 5 lowered. Therefore, the fore end of the optical fiber is preferably buried in the synthetic material of the probe.
Industrial Utilization .. . , ._ ~ . . ............................ ...
As a result, by above mentioned laser light irradiation apparatus of the present invention, the penetrating member can be 10 fabricated to be a desired shape easily, decrease in cost for fabricating apparatus is attained and the lead wire for detecting the temperature can be placed so as to be suitable for each medical treatment, further, the laser light can be irradiated against the living tissues uniformly.
Claims (10)
1. Laser light irradiation apparatus comprising a penetrating member and at least one transmitting member through which laser light goes so as to be fed into said penetrating member, said apparatus being characterized by;
said penetrating member which contains laser light scattering particles and which is fabricated from a laser light penetrating synthetic material.
said penetrating member which contains laser light scattering particles and which is fabricated from a laser light penetrating synthetic material.
2. Laser light irradiation apparatus according to claim 1, wherein said laser light transmitting member is an optical fiber and the fore end portion of a core of said optical fiber is buried in said synthetic material of said penetrating member.
3. Laser light irradiation apparatus according to claim 2, wherein a laser light scattering layer is formed on the surface of the buried part of said core.
4. Laser light irradiation apparatus according to claim 3, wherein said laser light scattering layer is fabricated from heat resistant ceramic particles partly melting and partly remaining to be in a particle-state.
5. Laser light irradiation apparatus according to claim 1, wherein said penetrating member is supported to be surrounded by a holder on its inner surface and a laser light reflecting layer covers at least a part of said inner surface.
6. Laser light irradiation apparatus according to claim 5, wherein said reflecting layer is a gold plated layer.
7. Laser right irradiation apparatus comprising a penetrating member, at least one transmitting member through which laser light goes so as to be fed into said penetrating member and a lead wire for detecting a temperature, said apparatus being characterized by;
said penetrating member which contains laser light scattering particles and which is fabricated from a laser light penetrating synthetic material; and said lead wire which is inserted through said penetrating member so as to be projected from the external surface of the fore end portion of said penetrating member and inserting part of which is buried in said synthetic material of said penetrating member.
said penetrating member which contains laser light scattering particles and which is fabricated from a laser light penetrating synthetic material; and said lead wire which is inserted through said penetrating member so as to be projected from the external surface of the fore end portion of said penetrating member and inserting part of which is buried in said synthetic material of said penetrating member.
8. Laser right irradiation apparatus according to claim 7, wherein at least said inserting part and the projecting part of said lead wire are coated by a laser light reflecting material.
9. Laser right irradiation apparatus according to claim 1 or 7, wherein a surface layer is formed on the surface of said laser light penetrating member and said surface layer contains laser light absorbing particles, light scattering particles having a larger refractive index than that of said penetrating member and a laser light penetrating material as a binder.
10. Laser right irradiation apparatus according to any claim of claims 1, 7 and 9, wherein a rough surface is formed on the surface of said laser light penetrating member.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1217869A JP2882814B2 (en) | 1989-08-24 | 1989-08-24 | Laser irradiation equipment |
| JP1-217869 | 1989-08-24 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2037924A1 true CA2037924A1 (en) | 1991-02-25 |
Family
ID=16711045
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002037924A Abandoned CA2037924A1 (en) | 1989-08-24 | 1990-08-23 | Laser light irradiation apparatus |
Country Status (10)
| Country | Link |
|---|---|
| US (1) | US5209748A (en) |
| EP (1) | EP0439629B1 (en) |
| JP (1) | JP2882814B2 (en) |
| CN (1) | CN1049612A (en) |
| AT (1) | ATE145564T1 (en) |
| AU (1) | AU6184890A (en) |
| CA (1) | CA2037924A1 (en) |
| DE (1) | DE69029257T2 (en) |
| WO (1) | WO1991002561A1 (en) |
| ZA (1) | ZA906664B (en) |
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-
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-
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- 1990-08-22 ZA ZA906664A patent/ZA906664B/en unknown
- 1990-08-23 DE DE69029257T patent/DE69029257T2/en not_active Expired - Fee Related
- 1990-08-23 AT AT90912470T patent/ATE145564T1/en not_active IP Right Cessation
- 1990-08-23 AU AU61848/90A patent/AU6184890A/en not_active Abandoned
- 1990-08-23 EP EP90912470A patent/EP0439629B1/en not_active Expired - Lifetime
- 1990-08-23 CA CA002037924A patent/CA2037924A1/en not_active Abandoned
- 1990-08-23 WO PCT/JP1990/001079 patent/WO1991002561A1/en active IP Right Grant
- 1990-08-24 CN CN90107189A patent/CN1049612A/en active Pending
-
1992
- 1992-06-16 US US07/899,043 patent/US5209748A/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| EP0439629A4 (en) | 1992-05-06 |
| WO1991002561A1 (en) | 1991-03-07 |
| DE69029257D1 (en) | 1997-01-09 |
| US5209748A (en) | 1993-05-11 |
| JP2882814B2 (en) | 1999-04-12 |
| CN1049612A (en) | 1991-03-06 |
| ZA906664B (en) | 1991-06-26 |
| JPH0380845A (en) | 1991-04-05 |
| AU6184890A (en) | 1991-04-03 |
| DE69029257T2 (en) | 1997-07-03 |
| EP0439629B1 (en) | 1996-11-27 |
| EP0439629A1 (en) | 1991-08-07 |
| ATE145564T1 (en) | 1996-12-15 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FZDE | Discontinued |