JP6076847B2 - Laser therapy device - Google Patents
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- JP6076847B2 JP6076847B2 JP2013138010A JP2013138010A JP6076847B2 JP 6076847 B2 JP6076847 B2 JP 6076847B2 JP 2013138010 A JP2013138010 A JP 2013138010A JP 2013138010 A JP2013138010 A JP 2013138010A JP 6076847 B2 JP6076847 B2 JP 6076847B2
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- 238000002647 laser therapy Methods 0.000 title description 2
- 238000013532 laser treatment Methods 0.000 claims description 23
- 239000013307 optical fiber Substances 0.000 claims description 23
- 238000005286 illumination Methods 0.000 claims description 12
- 238000011282 treatment Methods 0.000 claims description 7
- 238000003384 imaging method Methods 0.000 claims description 6
- 230000002093 peripheral effect Effects 0.000 claims description 5
- 230000001225 therapeutic effect Effects 0.000 claims description 4
- 206010028980 Neoplasm Diseases 0.000 description 12
- 206010020843 Hyperthermia Diseases 0.000 description 9
- 239000000835 fiber Substances 0.000 description 9
- 230000036031 hyperthermia Effects 0.000 description 9
- 206010008342 Cervix carcinoma Diseases 0.000 description 7
- 208000006105 Uterine Cervical Neoplasms Diseases 0.000 description 7
- 201000011510 cancer Diseases 0.000 description 7
- 201000010881 cervical cancer Diseases 0.000 description 7
- 230000003287 optical effect Effects 0.000 description 6
- 238000010586 diagram Methods 0.000 description 4
- 230000001678 irradiating effect Effects 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- 230000003247 decreasing effect Effects 0.000 description 2
- 238000002674 endoscopic surgery Methods 0.000 description 2
- 239000011810 insulating material Substances 0.000 description 2
- 239000004973 liquid crystal related substance Substances 0.000 description 2
- 230000005855 radiation Effects 0.000 description 2
- 241000270281 Coluber constrictor Species 0.000 description 1
- 239000000853 adhesive Substances 0.000 description 1
- 230000001070 adhesive effect Effects 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 210000004369 blood Anatomy 0.000 description 1
- 238000002512 chemotherapy Methods 0.000 description 1
- 238000004140 cleaning Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- OQZCSNDVOWYALR-UHFFFAOYSA-N flurochloridone Chemical compound FC(F)(F)C1=CC=CC(N2C(C(Cl)C(CCl)C2)=O)=C1 OQZCSNDVOWYALR-UHFFFAOYSA-N 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 230000036737 immune function Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 239000002504 physiological saline solution Substances 0.000 description 1
- 238000001959 radiotherapy Methods 0.000 description 1
- 238000005507 spraying Methods 0.000 description 1
- 238000005406 washing Methods 0.000 description 1
- 239000002699 waste material Substances 0.000 description 1
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- Laser Surgery Devices (AREA)
- Radiation-Therapy Devices (AREA)
- Surgical Instruments (AREA)
- Endoscopes (AREA)
Description
本発明は内視鏡に組み込み可能なレーザー治療器に係り、特に広範囲を均一照射することで効果的なハイパーサーミアを可能にする矩形断面の光ファイバーを使用したレーザー治療器に関する。 The present invention relates to a laser treatment device that can be incorporated into an endoscope, and more particularly to a laser treatment device using an optical fiber having a rectangular cross section that enables effective hyperthermia by uniformly irradiating a wide area.
内視鏡は主として人体内部の観察を目的とした医療機器である。内視鏡の鏡筒内に光学系を内蔵し、鏡筒の先端を体内に挿入して人体内部の映像をモニタに表示する。近年、この内視鏡にレーザー治療器を組み込んだレーザー内視鏡が、特に新しいがん治療法として注目されている。このレーザー内視鏡は、通常、従来の内視鏡下外科手術でがんを大まかに取り除き、その取り除いた跡にレーザー光を照射して残ったがん細胞を完全に死滅させる使い方をする。 An endoscope is a medical device mainly intended for observation inside the human body. An optical system is built in the barrel of the endoscope, and the distal end of the barrel is inserted into the body to display an image inside the human body on the monitor. In recent years, a laser endoscope in which a laser treatment device is incorporated in this endoscope has attracted attention as a new cancer treatment method. This laser endoscope is usually used in such a manner that cancer is roughly removed by conventional endoscopic surgery, and the remaining cancer cells are completely killed by irradiating the removed marks with laser light.
また、腫瘍が比較的小さく組織内に深く浸潤していない場合は、内視鏡下外科手術を行わず、レーザー内視鏡によるハイパーサーミアでがん細胞を死滅させる試みも行われている。このハイパーサーミア(がん温熱療法)は、腫瘍の局所を42℃以上で30〜60分間加温する治療法である。ハイパーサーミアはがん細胞を死滅させるだけでなく、加温により正常細胞の免疫機能を高めたり、放射線や化学療法の効果を高めたりする効果も期待されている。 In addition, when the tumor is relatively small and does not deeply infiltrate the tissue, an attempt is made to kill cancer cells by hyperthermia using a laser endoscope without performing endoscopic surgery. This hyperthermia (cancer hyperthermia) is a treatment method in which the tumor is heated at 42 ° C. or higher for 30 to 60 minutes. Hyperthermia is expected not only to kill cancer cells but also to increase the immune function of normal cells by heating and to enhance the effects of radiation and chemotherapy.
内視鏡は、手術の方法と目的により、鏡筒が硬い棒状の硬性鏡と、可撓性チューブで出来た軟性鏡を使い分けるようにしている。本発明に係るレーザー治療器は主として硬性鏡に組み込むものであるが、小型化することで軟性鏡に組み込むことも可能である。 The endoscope uses a rod-like rigid mirror with a hard barrel and a flexible mirror made of a flexible tube depending on the method and purpose of the operation. The laser treatment device according to the present invention is mainly incorporated into a rigid endoscope, but can be incorporated into a flexible endoscope by downsizing.
内視鏡は鏡筒内に複数枚のレンズを収納した光学式と、鏡筒先端にCCDイメージセンサによるカメラ部を配設した電子式がある。鏡筒先端には強い光を照射可能な照明部(外部光導入式又はLED発光式)を備えている。また、外科手術用の術具を備えた内視鏡もあり、例えばレーザーメスを備えた子宮鏡として特許文献1(米国特許第4836189号公報)が知られている。 There are two types of endoscopes: an optical type in which a plurality of lenses are housed in a lens barrel, and an electronic type in which a camera unit using a CCD image sensor is provided at the tip of the lens barrel. An illumination part (external light introduction type or LED light emission type) capable of irradiating strong light is provided at the end of the lens barrel. There is also an endoscope including a surgical instrument. For example, Patent Document 1 (US Pat. No. 4,836,189) is known as a hysteroscope including a laser knife.
内視鏡の太さ(直径)はその種類によって大きなものから小さなものまで様々であるが、一般的に患者の負担を軽減するために細径化の方向にある。従来のレーザー内視鏡は、レーザー光を導くためにベアファイバー(裸芯線光ファイバー)を使用したものが一般的である。 The thickness (diameter) of an endoscope varies from a large one to a small one depending on the type, but in general, in order to reduce the burden on the patient, the diameter is decreasing. Conventional laser endoscopes generally use a bare fiber (bare core optical fiber) to guide laser light.
このベアファイバーは円形断面の光ファイバーを使用しており、非接触照射の場合、そのビームプロファイルは断面の中央部分が最も高く周辺部にいくほど低い山形を形成している。このため、レーザー治療に使用可能な領域はビームプロファイルの中央部付近に限られ、ファイバー断面に対する利用可能領域は少ない。従って、一定領域を照射するのに長時間が掛かり、その分だけ患者に負担が掛かったり、十分な治療効果が得られなかったりしていた。 This bare fiber uses an optical fiber having a circular cross section, and in the case of non-contact irradiation, the beam profile forms a mountain shape that is highest at the center of the cross section and lower toward the periphery. For this reason, the area that can be used for laser treatment is limited to the vicinity of the center of the beam profile, and there is little available area for the fiber cross section. Therefore, it took a long time to irradiate a certain area, and the patient was burdened by that much, or a sufficient therapeutic effect could not be obtained.
均一強度のレーザー光を広い範囲で照射するには光ファイバーの直径を大きくする必要がある。しかし、そうするとレーザー内視鏡全体の直径も大きくなり、内視鏡を使用可能な部位が限られたり、患者により大きな負担が掛かったり、或いは操作性が悪くなったりするという課題があった。 In order to irradiate laser light of uniform intensity over a wide range, it is necessary to increase the diameter of the optical fiber. However, if it does so, the diameter of the whole laser endoscope will also become large, the site | part which can use an endoscope has been limited, the big burden was imposed on the patient, or the operativity worsened.
そこで本発明の目的は、均一強度のレーザー光を広範囲に照射可能でありながら、内視鏡の直径を比較的小さくすることができるレーザー内視鏡用のレーザー治療器を提供することにある。 SUMMARY OF THE INVENTION An object of the present invention is to provide a laser treatment device for a laser endoscope that can irradiate a laser beam with uniform intensity over a wide range and can relatively reduce the diameter of the endoscope.
前記課題を解決するため、本発明は、治療用レーザー光を導くための矩形断面の光ファイバーと、当該光ファイバーの先端を接続する内視鏡の鏡筒となる筒部と、当該筒部内に配設され前記光ファイバーの先端から放射されるレーザー光を前記筒部の先端部までガイドするための矩形断面のガイド筒と、当該ガイド筒の辺々と前記筒部の内周面との間に形成された船底形の隙間に配設された撮像手段及び照明手段とを有することを特徴とするレーザー治療器である。 In order to solve the above problems, the present invention provides an optical fiber having a rectangular cross-section for guiding a therapeutic laser beam, a cylindrical part that serves as a lens barrel of an endoscope that connects the distal ends of the optical fiber, and the optical fiber disposed in the cylindrical part. And formed between a guide tube having a rectangular cross section for guiding laser light emitted from the tip of the optical fiber to the tip of the tube, and between the sides of the guide tube and the inner peripheral surface of the tube. A laser treatment device comprising imaging means and illumination means arranged in a gap between the bottoms of the ship.
本発明のレーザー治療器は光ファイバーを矩形断面にしたので、いわゆるトップハット型の均一強度のレーザー光を広範囲に照射可能である。また、レーザー光をガイドする矩形断面のガイド筒の周囲に形成された船底形の隙間を無駄なく利用して撮像手段と照明手段を配設することができる。このため、内視鏡に組み込んだ場合の鏡筒となる筒部の径を低減することが可能であり、これにより患者の負担が少なく操作性が良好であり、広範囲均一照射による効果的なレーザー治療(ハイパーサーミア)が可能になる。 In the laser treatment device of the present invention, since the optical fiber has a rectangular cross section, it is possible to irradiate a so-called top-hat type uniform intensity laser beam over a wide range. In addition, the image pickup means and the illumination means can be arranged without waste using the gap at the bottom of the ship formed around the guide tube having a rectangular section for guiding the laser light. For this reason, it is possible to reduce the diameter of the cylindrical part that becomes a lens barrel when incorporated in an endoscope, thereby reducing the burden on the patient and improving operability, and an effective laser by uniform irradiation over a wide area. Treatment (hyperthermia) becomes possible.
以下、図面を参照して本発明の実施形態に係るレーザー治療器を説明する。図1はレーザー治療器1を使用した子宮頸がん治療用内視鏡レーザーシステムの全体概略図である。当該システムで使用する内視鏡は硬性鏡であり、この硬性鏡は子宮頸がん内視鏡のほか、腹腔鏡、胸腔鏡、膀胱鏡等にも使用可能である。 Hereinafter, a laser treatment device according to an embodiment of the present invention will be described with reference to the drawings. FIG. 1 is an overall schematic view of an endoscopic laser system for treating cervical cancer using a laser treatment device 1. The endoscope used in the system is a rigid endoscope. This rigid endoscope can be used for a laparoscope, a thoracoscope, a cystoscope and the like in addition to a cervical cancer endoscope.
レーザー治療器1は円形断面の筒体2aで構成された鏡筒となる筒部2を有する。当該筒部2の基端部に持ち手3が取り付けられている。持ち手3の基端部に、光ファイバー10と電線(図示せず)を内蔵したケーブル4が接続されている。当該ケーブル4で、レーザー治療器1がレーザー発振器5及びコントローラ6と接続されている。コントローラ6によって液晶モニタ7に映像が出力される。 The laser treatment device 1 has a cylindrical portion 2 that is a lens barrel constituted by a cylindrical body 2a having a circular cross section. A handle 3 is attached to the proximal end portion of the cylindrical portion 2. A cable 4 containing an optical fiber 10 and an electric wire (not shown) is connected to the proximal end of the handle 3. With the cable 4, the laser treatment device 1 is connected to the laser oscillator 5 and the controller 6. An image is output to the liquid crystal monitor 7 by the controller 6.
筒部2の筒体2aは直径が例えば30mm程度の円筒状に形成され、その内部中央位置に図2Aのように光ファイバー10の先端が光学系30に接続されている。この光ファイバー10は矩形(正方形)断面のコア10aと、その外周を覆うクラッド10bを有し、コア10aの端面が光学系30に接続されている。光学系30の右側の放射側は、筒体2a内に同軸的に配設された矩形(正方形)断面のガイド筒2bに接続され、このガイド筒2bが筒体2aの先端部まで延びている。そして筒体2aの先端部が透明なレーザー照射部20とされている。 The cylindrical body 2a of the cylindrical portion 2 is formed in a cylindrical shape having a diameter of, for example, about 30 mm, and the tip of the optical fiber 10 is connected to the optical system 30 at the center position inside as shown in FIG. The optical fiber 10 includes a core 10 a having a rectangular (square) cross section and a clad 10 b covering the outer periphery thereof, and an end surface of the core 10 a is connected to the optical system 30. The right radiation side of the optical system 30 is connected to a guide cylinder 2b having a rectangular (square) cross section disposed coaxially in the cylinder 2a, and the guide cylinder 2b extends to the tip of the cylinder 2a. . And the front-end | tip part of the cylinder 2a is made into the transparent laser irradiation part 20. As shown in FIG.
ガイド筒2bの4つの角部は、図2Bのように円形断面の筒体2aの内周面に接している。従って、ガイド筒2bの直線状の辺々と筒体2aの内周面との間に、船底形の4つの隙間(第1の隙間C1〜第4の隙間C4)が形成されている。 The four corners of the guide tube 2b are in contact with the inner peripheral surface of the cylindrical body 2a having a circular cross section as shown in FIG. 2B. Therefore, four bottom-shaped gaps (first gap C1 to fourth gap C4) are formed between the straight sides of the guide cylinder 2b and the inner peripheral surface of the cylinder 2a.
本発明の実施形態では、この船底形の4つの隙間C1〜C4を撮像手段と照明手段の配設スペースとして有効利用している。すなわち、第1の隙間C1に撮像手段としてのCCDイメージセンサを使用したカメラ部11が配設され、第2の隙間C2に照明手段としての3つの白色LED部12が配設されている。 In the embodiment of the present invention, the four gaps C1 to C4 of the ship bottom shape are effectively used as an arrangement space for the imaging means and the illumination means. That is, a camera unit 11 using a CCD image sensor as an imaging unit is disposed in the first gap C1, and three white LED units 12 as illumination units are disposed in the second gap C2.
また、光ファイバー10を挟んでカメラ部11と対向する第3の隙間C3に、照明手段としての2つの白色LED部12が配設されている。そして、第4の隙間C4に、照明手段としての1つの紫外LED部13が配設されている。この紫外LED部13は、組織に紫外線を照射することで当該組織が発する自家蛍光の強度の差によって正常組織と病変組織を識別するために使用する。なお、LEDの個数は、隙間C2〜C4の大きさとLEDの種類に応じて、白色・紫外とも、適宜増減変更可能であることは勿論である。 In addition, two white LED portions 12 as illumination means are disposed in a third gap C3 facing the camera portion 11 with the optical fiber 10 interposed therebetween. And in the 4th clearance gap C4, one ultraviolet LED part 13 as an illumination means is arrange | positioned. The ultraviolet LED unit 13 is used to distinguish between normal tissue and diseased tissue based on the difference in the intensity of autofluorescence emitted from the tissue by irradiating the tissue with ultraviolet light. Of course, the number of LEDs can be appropriately increased or decreased for both white and ultraviolet in accordance with the size of the gaps C2 to C4 and the type of LED.
なお、従来の内視鏡で知られているように、カメラ部11に隣接して洗浄ノズル部を配設してもよい。当該洗浄ノズル部から生理食塩水をカメラ部11に噴射することで、カメラ部11に付着した血液等を除去することができる。 Note that a cleaning nozzle unit may be disposed adjacent to the camera unit 11 as is known in conventional endoscopes. By spraying physiological saline into the camera unit 11 from the washing nozzle unit, blood or the like attached to the camera unit 11 can be removed.
筒体2aの先端のレーザー照射部20に、図3のように温度センサ部25が配設されている。この温度センサ部25は測温点25aが露出した被覆熱電対で構成されている。同図において25bは熱電対素線、25cは熱電対素線被覆絶縁材、25dは外皮絶縁材である。 A temperature sensor unit 25 is disposed on the laser irradiation unit 20 at the tip of the cylindrical body 2a as shown in FIG. The temperature sensor unit 25 is composed of a coated thermocouple with the temperature measuring point 25a exposed. In the figure, 25b is a thermocouple element, 25c is a thermocouple element covering insulating material, and 25d is a skin insulating material.
温度センサ部25は、レーザー照射部20の中央部から周辺部に向かって形成された半径溝20aに収容されている。温度センサ部25の被覆熱電対は極細のものを使用することができ、複数のメーカーから長径0.5mm以下のものでも容易に入手可能である。被覆熱電対は、レーザー光Lの影響を受けないように全域が金メッキされたものが望ましい。 The temperature sensor unit 25 is accommodated in a radial groove 20 a formed from the central part of the laser irradiation unit 20 toward the peripheral part. The coated thermocouple of the temperature sensor unit 25 can be an extremely thin one, and even those having a major axis of 0.5 mm or less can be easily obtained from a plurality of manufacturers. The coated thermocouple is preferably gold-plated over the entire area so as not to be affected by the laser beam L.
温度センサ部25の先端に測温点25aが設けられ、この測温点25aがレーザー照射部20の中央に位置している。温度センサ部25は、レーザー照射部20に半径溝20aを形成せずに、レーザー照射部20に露出させて接着剤等で貼り付けたり、測温点25aだけをレーザー照射部20に露出させ、残りの部分をレーザー照射部20に埋設したりしてもよい。 A temperature measuring point 25 a is provided at the tip of the temperature sensor unit 25, and the temperature measuring point 25 a is located at the center of the laser irradiation unit 20. The temperature sensor unit 25 does not form the radial groove 20a in the laser irradiation unit 20, but is exposed to the laser irradiation unit 20 and attached with an adhesive or the like, or only the temperature measuring point 25a is exposed to the laser irradiation unit 20, The remaining portion may be embedded in the laser irradiation unit 20.
ハイパーサーミアでは、組織表面から5〜10mm程度の深さを42℃以上に加温する。従って、当該温度が確実に得られるように、温度センサ部25の出力に基づいてレーザー光の波長や強度を調節する。 In hyperthermia, a depth of about 5 to 10 mm from the tissue surface is heated to 42 ° C. or higher. Therefore, the wavelength and intensity of the laser light are adjusted based on the output of the temperature sensor unit 25 so that the temperature can be reliably obtained.
図4は、子宮頸がん治療用内視鏡レーザーシステムのブロック図である。小型カメラ部11、白色LED部12および紫外LED部13がコントローラ6によって制御される。コントローラ6はモニタ制御部6a、調光部6b、制御モジュール6c、電源部6dを有する。温度センサ部25の出力はレーザー発振器5にフィードバックされ、これによりレーザー光の波長や強度が調節される。 FIG. 4 is a block diagram of an endoscopic laser system for treating cervical cancer. The small camera unit 11, the white LED unit 12 and the ultraviolet LED unit 13 are controlled by the controller 6. The controller 6 includes a monitor control unit 6a, a light control unit 6b, a control module 6c, and a power supply unit 6d. The output of the temperature sensor unit 25 is fed back to the laser oscillator 5, thereby adjusting the wavelength and intensity of the laser light.
前述した光ファイバーとガイド筒の断面形状は、必ずしも図5(a)のように正方形である必要はなく、図5(b)のように長方形にしてもよい。この場合、ガイド筒2bの上下に比較的大きな第1の隙間C1と第2の隙間C2が形成されるので、第1の隙間C1に例えばカメラ部11と白色LED部12を配設し、第2の隙間C2に紫外LED部13を配設する。 The cross-sectional shapes of the optical fiber and the guide cylinder described above are not necessarily square as shown in FIG. 5A, and may be rectangular as shown in FIG. In this case, since a relatively large first gap C1 and second gap C2 are formed above and below the guide tube 2b, for example, the camera unit 11 and the white LED unit 12 are disposed in the first gap C1, and the first The ultraviolet LED portion 13 is disposed in the gap C2 between the two.
レーサー治療器1の先端のレーザー照射部20は、図6(a)のように筒部2の先端面と同じ平面に配設してもよいし、図6(b)のように筒部2の先端面からやや突出させて配設してもよい。図6(b)のようにレーザー照射部20を突出させて配設することで、レーザー照射部20を腫瘍に密着させやすくなり、レーザー光の効率的な照射が容易になる。 The laser irradiation unit 20 at the distal end of the racer treatment device 1 may be disposed on the same plane as the distal end surface of the cylindrical portion 2 as shown in FIG. 6 (a), or the cylindrical portion 2 as shown in FIG. 6 (b). You may arrange | position by making it protrude a little from the front end surface. As shown in FIG. 6B, by arranging the laser irradiation unit 20 so as to protrude, the laser irradiation unit 20 can be easily brought into close contact with the tumor, and efficient irradiation of laser light is facilitated.
図7は、本発明の実施形態に係るレーザー治療器1を組み込んだ子宮頸がん内視鏡の使用例である。レーザー照射部20から放射されるレーザー光は矩形状に広範囲に照射され、かつ、後述するようにトップハット型の均一強度のレーザープロファイルを有するので、腫瘍表面を広範囲で均一に加温することができる。従って、例えば子宮頸がん等において、腫瘍全体を照射範囲に収めてがん細胞を一度の照射で残らず死滅させる使用法が可能である。 FIG. 7 is a usage example of a cervical cancer endoscope incorporating the laser treatment device 1 according to the embodiment of the present invention. The laser light emitted from the laser irradiation unit 20 is irradiated in a rectangular shape over a wide area and has a top hat type uniform intensity laser profile as will be described later, so that the tumor surface can be heated uniformly over a wide area. it can. Therefore, for example, in cervical cancer and the like, a method of using the entire tumor within the irradiation range and killing all cancer cells by one irradiation is possible.
光ファイバーないしガイド筒の断面形が正方形でも長方形でも、図8Aに示すようないわゆるトップハット型の均一なビームプロファイルが得られる。レーザー光の出力は、通常のハイパーサーミアの場合は例えば5W程度とすることができるが、治療の内容によっては数百mWの低出力とする場合もある。 Even if the cross-sectional shape of the optical fiber or the guide tube is square or rectangular, a so-called top-hat type uniform beam profile as shown in FIG. 8A can be obtained. In the case of normal hyperthermia, the output of the laser beam can be set to about 5 W, for example. However, depending on the content of treatment, the output may be as low as several hundred mW.
図8Bは、矩形ファイバーとベアファイバー(裸芯線光ファイバー)を比較したイメージ図である。このように、矩形ファイバーはベアファイバーに比べて広範囲に一定強度のレーザー光を照射することができる。従って、ハイパーサーミアの治療効果を向上させることができる。 FIG. 8B is an image diagram comparing a rectangular fiber and a bare fiber (bare core optical fiber). In this way, the rectangular fiber can irradiate laser light having a constant intensity over a wider range than the bare fiber. Therefore, the therapeutic effect of hyperthermia can be improved.
以上、本発明の一実施形態について説明したが、本発明は前記実施形態に限定されることなく種々の変形が可能である。例えば照明部は白色LED部12と紫外LED部13を例示したが、このようなLEDに限らず、他の照明部として例えば照明用外部レーザー光を光ファイバーで導入する外部光導入式としてもよい。 Although one embodiment of the present invention has been described above, the present invention is not limited to the above embodiment, and various modifications can be made. For example, the illuminating unit has exemplified the white LED unit 12 and the ultraviolet LED unit 13, but is not limited to such LEDs, and other illuminating units may be an external light introducing type in which, for example, an external laser beam for illumination is introduced by an optical fiber.
1:レーザー治療器 2:筒部
3:持ち手 4:ケーブル
5:レーザー発振器 6:コントローラ
7:液晶モニタ 10:光ファイバー
11:カメラ部 12:白色LED部
13:紫外LED部 20:レーザー照射部
25:温度センサ部 30:光学系
C1-C4:船底形の隙間
1: Laser therapy device 2: Tube portion 3: Handle 4: Cable 5: Laser oscillator 6: Controller 7: Liquid crystal monitor 10: Optical fiber 11: Camera portion 12: White LED portion 13: Ultraviolet LED portion 20: Laser irradiation portion 25 : Temperature sensor unit 30: Optical system C1-C4: Clearance at the bottom of the ship
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