JPH04135550A - Optical scanner for observing tomographic image - Google Patents
Optical scanner for observing tomographic imageInfo
- Publication number
- JPH04135550A JPH04135550A JP2259914A JP25991490A JPH04135550A JP H04135550 A JPH04135550 A JP H04135550A JP 2259914 A JP2259914 A JP 2259914A JP 25991490 A JP25991490 A JP 25991490A JP H04135550 A JPH04135550 A JP H04135550A
- Authority
- JP
- Japan
- Prior art keywords
- light
- tomographic image
- optical
- insertion section
- observation
- 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.)
- Granted
Links
- 230000003287 optical effect Effects 0.000 title claims abstract description 60
- 238000003780 insertion Methods 0.000 claims description 43
- 230000037431 insertion Effects 0.000 claims description 43
- 238000005286 illumination Methods 0.000 abstract description 9
- 239000013307 optical fiber Substances 0.000 description 36
- 238000012545 processing Methods 0.000 description 17
- 238000010586 diagram Methods 0.000 description 16
- 239000000523 sample Substances 0.000 description 9
- 238000005452 bending Methods 0.000 description 7
- 238000003325 tomography Methods 0.000 description 7
- 238000000034 method Methods 0.000 description 6
- 239000000835 fiber Substances 0.000 description 5
- 238000003384 imaging method Methods 0.000 description 5
- 210000000056 organ Anatomy 0.000 description 5
- 230000000694 effects Effects 0.000 description 3
- 230000006870 function Effects 0.000 description 2
- 101100327165 Arabidopsis thaliana CCD8 gene Proteins 0.000 description 1
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 description 1
- JSQFXMIMWAKJQJ-UHFFFAOYSA-N [9-(2-carboxyphenyl)-6-(ethylamino)xanthen-3-ylidene]-diethylazanium;chloride Chemical compound [Cl-].C=12C=CC(=[N+](CC)CC)C=C2OC2=CC(NCC)=CC=C2C=1C1=CC=CC=C1C(O)=O JSQFXMIMWAKJQJ-UHFFFAOYSA-N 0.000 description 1
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 description 1
- 229910052782 aluminium Inorganic materials 0.000 description 1
- 230000008827 biological function Effects 0.000 description 1
- 239000003795 chemical substances by application Substances 0.000 description 1
- 238000012937 correction Methods 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 238000002594 fluoroscopy Methods 0.000 description 1
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 description 1
- 229910052737 gold Inorganic materials 0.000 description 1
- 239000010931 gold Substances 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 229910052709 silver Inorganic materials 0.000 description 1
- 239000004332 silver Substances 0.000 description 1
- 230000001360 synchronised effect Effects 0.000 description 1
- 238000002604 ultrasonography Methods 0.000 description 1
- 238000012800 visualization Methods 0.000 description 1
- 230000002747 voluntary effect Effects 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
Landscapes
- Investigating Materials By The Use Of Optical Means Adapted For Particular Applications (AREA)
- Investigating Or Analysing Materials By Optical Means (AREA)
- Endoscopes (AREA)
- Length Measuring Devices By Optical Means (AREA)
Abstract
Description
【発明の詳細な説明】
［産業上の利用分野］
本発明は断層像観察のための光を走査し、被検体の内部
情報の可視化を容易とする断層像観察用光走査装置に関
する。DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to an optical scanning device for tomographic image observation that scans light for tomographic image observation and facilitates visualization of internal information of a subject.
［従来技術］
近年、診療における画像利用が普及し、被検体の内部情
報を無侵襲的、非接触的に計測する技術の重要性がまず
ます高まっている。[Prior Art] In recent years, the use of images in medical treatment has become widespread, and the importance of technology for measuring internal information of a subject in a non-invasive and non-contact manner is increasing.
従来、生体などの被検体内部の情報の無侵襲的、非接触
的な計測は、主としてＸ線によって行われていたが、こ
のＸ線の使用は、放射線被爆の問題や生体機能の画像化
が困難という問題があり、超音波内視鏡による体腔内組
織の透視が行われるようになった。Conventionally, non-invasive, non-contact measurement of information inside a subject such as a living body has been mainly performed using X-rays, but the use of X-rays poses problems such as radiation exposure and the imaging of biological functions. Due to this problem, fluoroscopy of the internal tissues of body cavities using an ultrasound endoscope has been performed.
しかしながら、前記超音波内視鏡は、空間分解能があま
り高くなく、形態以外の生理的組成などの情報を知るこ
とはできない、さらに前記超音波内視鏡の使用に際して
は、水などの媒体が必要であるため、被検体の観察に際
しての処置が繁雑であるという問題がある。However, the ultrasonic endoscope does not have very high spatial resolution and cannot obtain information such as physiological composition other than morphology, and furthermore, when using the ultrasonic endoscope, a medium such as water is required. Therefore, there is a problem that the procedure for observing the subject is complicated.
このため、最近では、光を用いて被検体内部の情報を可
視化する光ＣＴに係わる技術が種々提案されており、例
えば、特開平１−２０９３４２号公報に、その先行技術
が開示されている。For this reason, recently, various techniques related to optical CT that visualize information inside a subject using light have been proposed, and for example, the prior art is disclosed in Japanese Patent Application Laid-open No. 1-209342.
［発明が解決しようとする課題］
前記光ＣＴなどによる断層像観察においては、断層像観
察のための光を導く挿入部を被検体内部へ挿入し、この
挿入部を湾曲動作させるなどして、適切に光走査が行わ
れるようにする必要がある。[Problems to be Solved by the Invention] In tomographic image observation using optical CT or the like, an insertion section that guides light for tomographic image observation is inserted into the subject, and this insertion section is moved in a curved manner, etc. It is necessary to ensure that optical scanning is performed appropriately.
しかしながら、従来、前記挿入部外周に位置する観察部
位の断層像を得ようとする場合などには、前記挿入部の
複雑な湾曲操作などが必要となり、光走査が不適切とな
るおそれがある。However, conventionally, when attempting to obtain a tomographic image of an observation site located on the outer periphery of the insertion section, a complicated bending operation of the insertion section is required, which may make optical scanning inappropriate.
さらに、前記挿入部の挿入が可能な被検体内部の空間が
極めて狭い場合などには、前記挿入部の動きが制限され
て適切な光走査が行なえず、希望する断層像が得られな
い可能性がある。Furthermore, if the space inside the subject into which the insertion section can be inserted is extremely narrow, the movement of the insertion section will be restricted, making it impossible to perform appropriate optical scanning, and there is a possibility that the desired tomographic image will not be obtained. There is.
本発明は上記事情に鑑みてなされたものであり、断層像
観察に必要な光の走査を、簡単な操作で、しかも、確実
に行なうことのできる断層像観察用光走査装置を提供す
ることを目的とする。The present invention has been made in view of the above circumstances, and it is an object of the present invention to provide an optical scanning device for tomographic image observation that can perform the scanning of light necessary for tomographic image observation with simple operation and moreover. purpose.
［課題を解決するための手段及び作用］本発明の断層像
観察用光走査装置は、被検体内部に挿入する挿入部に、
断層像観察のための光を前記挿入部から放射状に走査す
る手段を備えており、この手段により光走査が容易に行
なえる。[Means and effects for solving the problems] The optical scanning device for tomographic image observation of the present invention includes an insertion section inserted into the inside of a subject,
A means is provided for scanning light for tomographic image observation radially from the insertion section, and optical scanning can be easily performed by this means.
［実施例コ 以下、図面を参照して本発明を具体的に説明する。[Example code] Hereinafter, the present invention will be specifically described with reference to the drawings.
第１図〜第３図は本発明の第１実施例を示し、第１図は
断層像観察用光走査装置の概略構成図、第２図は光ファ
イバの配置を示す説明図、第３図は光ファイバの先端形
状を示す説明図である。1 to 3 show a first embodiment of the present invention, FIG. 1 is a schematic configuration diagram of an optical scanning device for tomographic image observation, FIG. 2 is an explanatory diagram showing the arrangement of optical fibers, and FIG. FIG. 2 is an explanatory diagram showing the shape of the tip of an optical fiber.
第１図に示すように、断層像観察用光走査装置は、被検
体内部に挿入される細長で可視性を有する挿入部１と、
断層像観察のための光を出射するとともに、被検体内部
からの反射光を受光する送受光装置３と、ガルバノメー
タ４と、このガルバノメータ４を制御する制御回路５と
を備えている。As shown in FIG. 1, the optical scanning device for tomographic image observation includes an elongated and visible insertion section 1 inserted into a subject;
It includes a light transmitting/receiving device 3 that emits light for tomographic image observation and receives reflected light from inside the subject, a galvanometer 4, and a control circuit 5 that controls the galvanometer 4.
前記挿入部１は、例えば内視鏡の挿入部として構成され
、先端部６０チャンネル部６ａに、照明窓７、観察窓８
、及び、吸引チャンネル９などが形成されている。The insertion section 1 is configured as an insertion section of an endoscope, for example, and has an illumination window 7 and an observation window 8 in a distal end section 60 and a channel section 6a.
, a suction channel 9, etc. are formed.
前記照明窓７の内側には図示しない配光レンズが装着さ
れ、この配光レンズの後端にライトガイド１０が連設さ
れている。このライトガイド１０は、前記挿入部１内を
挿通されて図示しない光源装置に接続され、この光源装
置からの照明光を伝送して前記照明窓７から被検体の観
察部位に照射するようになっている。A light distribution lens (not shown) is mounted inside the illumination window 7, and a light guide 10 is connected to the rear end of the light distribution lens. The light guide 10 is inserted through the insertion section 1 and connected to a light source device (not shown), and transmits illumination light from the light source device to illuminate the observation region of the subject through the illumination window 7. ing.
また、前記観察窓８の内側には図示しない対物レンズが
設けられ、この対物レンズの結像位置に、イメージガイ
ド１１の先端面が配置されている。Further, an objective lens (not shown) is provided inside the observation window 8, and the front end surface of the image guide 11 is disposed at the imaging position of this objective lens.
このイメージガイド１１は、前記挿入部１内を挿通され
、後端面が図示しない接眼部内の接眼レンズに対向して
いる。そして、前記対物レンズによって結像された観察
部位の光学像が前記イメージガイド１１によって導かれ
、前記接眼部から肉眼観察が可能なようになっている。The image guide 11 is inserted through the insertion section 1, and its rear end face faces an eyepiece lens (not shown) in an eyepiece section. The optical image of the observation site formed by the objective lens is guided by the image guide 11, and observation with the naked eye is possible from the eyepiece.
また、前記挿入部１には、断層像観察のための光を放射
状に走査する手段としての光ファイバ束２が設けられ、
この光ファイバ束２は、前記挿入部１外周側に複数の光
ファイバ１２が環状に配設されて構成されている。Further, the insertion section 1 is provided with an optical fiber bundle 2 as a means for radially scanning light for tomographic image observation,
This optical fiber bundle 2 is configured by a plurality of optical fibers 12 arranged in a ring shape on the outer circumferential side of the insertion section 1.
第２図に示すように、前記光ファイバ１２の先端は、前
記先端部６の外周側に前記チャンネル部６ａを囲繞する
よう配設されており、第３図に示すように、先端がファ
イバ軸に対して、例えば４５°にカットされてテーパ面
１２ａが形成されている。As shown in FIG. 2, the tip of the optical fiber 12 is disposed on the outer peripheral side of the tip portion 6 so as to surround the channel portion 6a, and as shown in FIG. The tapered surface 12a is formed by cutting, for example, at an angle of 45 degrees.
そして、このテーバ面１．２ ａに、アルミニウム、銀
、金などが蒸着されてミラー面が形成されるとともに、
このミラー面が前記挿入部１先端で内側になるよう配列
され、前記送受光装置３からの光をファイバ軸側方に放
射し、また、被検体内部から反射された反射光をファイ
バ軸方向に入射するようになっている。Then, aluminum, silver, gold, etc. are deposited on this Taber surface 1.2a to form a mirror surface, and
This mirror surface is arranged inward at the tip of the insertion section 1, and emits the light from the light transmitting/receiving device 3 to the side of the fiber axis, and also directs the reflected light from inside the subject in the direction of the fiber axis. It is designed to be incident.
また、前記送受光装置３の内部には、例えばピコ秒単位
の光パルスを出射するパルスレーザ、このパルスレーザ
から出射される光パルスの光路を形成するためのレンズ
及びミラー群、及び、撮像手段などを備えている。Further, inside the light transmitting/receiving device 3, a pulse laser that emits a light pulse of picosecond units, a lens and mirror group for forming an optical path of the light pulse emitted from this pulse laser, and an imaging means are included. It is equipped with such things as
前記送受光装置３のパルスレーザ−から光パルスが出射
されると、この光パルスの出射に連動して前記制御回路
５により前記ガルバノメータ４のミラー４ａの振り角が
制御され、前記光ファイバ束２の各光ファイバ１２へ入
射されるようになっている。When a light pulse is emitted from the pulse laser of the light transmitting/receiving device 3, the swing angle of the mirror 4a of the galvanometer 4 is controlled by the control circuit 5 in conjunction with the emission of this light pulse. The light beam is inputted into each optical fiber 12 of .
尚、前記光ファイバ１２は、端部にテーパ面１２ａを形
成せずにプリズムを配置しても良く、また、前記光ファ
イバ１２に代え、第４図に示すように、先端部１３ａを
前記挿入部ｌから外側方向に曲げた光ファイバ１３を使
用して前記光ファイバ束２を構成しても良い。Note that the optical fiber 12 may have a prism disposed at its end without forming the tapered surface 12a, and instead of the optical fiber 12, as shown in FIG. The optical fiber bundle 2 may be constructed using the optical fibers 13 bent outward from the portion 1.
次に、前記断層像観察用光走査装置を用いた光断層像観
察について説明する。Next, optical tomographic image observation using the optical scanning device for tomographic image observation will be explained.
例えば、人体臓器の患部の光断層像を観察する場合、ま
ず、挿入部１を体腔内部に挿入する。次いで、先端部６
外周側が患部位置に達したら、送受光装置３内のパルス
レーザ−より、半値幅が数ピコ秒の極めて時間幅の短い
光パルスを発生させ、この光パルスをガルバノメータ４
のミラー４ａで反射させて光ファイバ束２を構成する各
光ファイバ１２に入射させる。For example, when observing an optical tomographic image of a diseased part of a human organ, first, the insertion section 1 is inserted into a body cavity. Next, the tip 6
When the outer circumferential side reaches the affected area position, a pulse laser in the light transmitting/receiving device 3 generates an extremely short optical pulse with a half-width of several picoseconds, and this optical pulse is transmitted to the galvanometer 4.
The light is reflected by the mirror 4a and is incident on each optical fiber 12 constituting the optical fiber bundle 2.
前記各光ファイバ１２に入射された光パルスは、先端の
テーバ面１２ａで反射されてファイバ軸側方へ放射され
、前記光ファイバ束２から外側に向かって放射状に光走
査が行われる。そして、患部に照射された光が組織表面
及び内部で反射されると、この反射光が、前記光ファイ
バ束２から前記ガルバノメータ４のミラー４ａを経て訪
記送受光装置３内に導光され、内部のレンズ及びミラー
群を経て、例えばストリークカメラなどの撮像手段に入
射される。The light pulses incident on each of the optical fibers 12 are reflected by the Taper surface 12a at the tip and radiated to the side of the fiber axis, and light is scanned radially outward from the optical fiber bundle 2. When the light irradiated to the affected area is reflected on the surface and inside of the tissue, this reflected light is guided from the optical fiber bundle 2 through the mirror 4a of the galvanometer 4 into the visiting light transmitting/receiving device 3, The light passes through an internal lens and mirror group and enters an imaging means such as a streak camera.
前記ストリークカメラでは、前記反射光の時間分解波形
を検出し、この時間分解波形を図示しない処理装置で処
理することにより観察部位の断層像が得られ、図示しな
い表示装置に表示される。The streak camera detects a time-resolved waveform of the reflected light and processes this time-resolved waveform with a processing device (not shown) to obtain a tomographic image of the observed region, which is displayed on a display device (not shown).
すなわち、前記挿入部１を被検体内部に挿入して断層像
を観察する場合、前記挿入部１の複雑な湾曲操作を要す
ることなく、前記挿入部１の先端部６外周側を観察部位
まで挿入するのみで、前記挿入部１から放射状に光走査
が行われるため、希望する観察部位の断層像が容易に得
られるのである。That is, when inserting the insertion section 1 into a subject to observe a tomographic image, the outer circumferential side of the distal end 6 of the insertion section 1 can be inserted to the observation site without requiring a complicated bending operation of the insertion section 1. By simply doing this, optical scanning is performed radially from the insertion section 1, making it easy to obtain a tomographic image of the desired observation site.
尚、前記ガルバノメータ４に代え、第５図に示すように
、前記光ファイバ束２と前記送受光装置３との間に、Ａ
ＯＭ （音響光学素子）１４を配置し、このＡ ＯＭ
１．４を制御回路１５で制御することにより、前記送受
光装置３からの光を走査制御するようにしても良い。Incidentally, instead of the galvanometer 4, as shown in FIG.
OM (acousto-optic element) 14 is arranged, and this A OM
1.4 may be controlled by the control circuit 15 to perform scanning control of the light from the light transmitting/receiving device 3.
第６図及び第７図は本発明の第２実施例を示し、第６図
は光断層像観察のためのシステム構成図、第７図はプロ
ーブ保持バルーンを示す説明図である。6 and 7 show a second embodiment of the present invention, FIG. 6 is a system configuration diagram for optical tomographic image observation, and FIG. 7 is an explanatory diagram showing a probe holding balloon.
この第２実施例は、前述の第１実施例に対してシングル
ファイバを用い、このシングルファイバ先端に配置した
ミラーを回転させて機械的に光走査を行なうものである
。This second embodiment differs from the first embodiment in that it uses a single fiber and mechanically performs optical scanning by rotating a mirror placed at the tip of the single fiber.
第６図に示すように、光断層像観察のためのシステムは
、７０−ブ２１と、光断層処理制御部２２と、画像処理
装置２３と、前記プローブ２１の光走査駆動を制御する
制御回路２４とを備えている。As shown in FIG. 6, the system for optical tomographic image observation includes a 70-bu 21, an optical tomographic processing control section 22, an image processing device 23, and a control circuit that controls the optical scanning drive of the probe 21. It is equipped with 24.
前記プローブ２１は、被検体内部に挿入される細長で可
視性を有する挿入部２５と、この挿入部２５の基部側に
設けられた大幅の操作部２６とを有し、前記挿入部２５
先端側には、先端がｒＲ塞された円筒状の透光性カバー
２７が装着されている。The probe 21 includes an elongated and visible insertion section 25 that is inserted into the subject, and a large operation section 26 provided on the base side of the insertion section 25.
A cylindrical translucent cover 27 whose tip is R-closed is attached to the tip side.
また、前記挿入部２５のほぼ軸心上に、前記光断層処理
制御部２２に接続される光ファイバ２８を内蔵したフレ
キシブルシャフト２９が挿通され、このフレキシブルシ
ャフト２９の先端側が軸受３０により回転自在に支持さ
れている。さらに、前記透光性カバー２７内に露呈する
前記フレキシブルシャフト２９先端に、前記フレキシブ
ルシャフト２９の軸心に対して例えば４５°の傾斜角を
有するミラー３１と、このミラー３１からの反射光を配
光するためのレンズ３２とが設置されている。Further, a flexible shaft 29 having a built-in optical fiber 28 connected to the optical tomography processing control section 22 is inserted approximately on the axis of the insertion section 25, and the distal end side of the flexible shaft 29 is rotatably supported by a bearing 30. Supported. Furthermore, a mirror 31 having an inclination angle of, for example, 45° with respect to the axis of the flexible shaft 29 is disposed at the tip of the flexible shaft 29 exposed in the transparent cover 27, and reflected light from this mirror 31 is arranged. A lens 32 for emitting light is installed.
また、前記フレキシブルシャフト２９の前記操作部２６
側には、ギア３３が外嵌固定され、このギア３３にギア
３４が噛合している。このギア３４はモータ３５の出力
軸に固定され、このモータ３５にはエンコーダ３６が連
設されている。前記モータ３５には前記制御回路２４が
接続され、この制御部１２４に前記エンコーダ３６がら
の信号が入力されて前記モータ３５の回転が制御される
ようになっている。Further, the operating portion 26 of the flexible shaft 29
A gear 33 is externally fitted and fixed on the side, and a gear 34 meshes with this gear 33. This gear 34 is fixed to the output shaft of a motor 35, and an encoder 36 is connected to this motor 35. The control circuit 24 is connected to the motor 35, and a signal from the encoder 36 is input to the control section 124 to control the rotation of the motor 35.
前記光断層処理制御部２２は、例えば色素レーザーとＮ
ｄ：ＹＡＧレーザーとを組合わせたパルスレーザ−３７
を備え、前記Ｎｄ：ＹＡＧレーザ−の出射光が色素レー
ザー内の色素（例えばＲｈｏｄａｍｉｎｅ Ｇ）に照
射され、この色素レーザーの出射光がレンズ３８により
収束されてビームスプリッタ３９によって２つに分離さ
れるようになっている。The optical tomography processing control unit 22 uses, for example, a dye laser and an N
d: Pulse laser combined with YAG laser-37
The light emitted from the Nd:YAG laser is irradiated onto a dye (for example, Rhodamine G) in the dye laser, and the light emitted from the dye laser is converged by a lens 38 and separated into two by a beam splitter 39. It looks like this.
前記ビームスアリツタ３９を透過した光は、さらにビー
ムスプリッタ４０を透過してレンズ４］にて集光され、
前記プローブ２１の光ファイバ２８に入射された後、こ
の光ファイバ２８を経て観察部位に照射される。また、
観察部位からの反射光は、前記レンズ４１を通り、前記
ビームスプリッタ４０で反射されてビームスプリッタ４
２を透過し、ＫＤＰ４３などの非線形光学素子に入射さ
れる。The light that has passed through the beam splitter 39 further passes through a beam splitter 40 and is condensed by a lens 4.
After entering the optical fiber 28 of the probe 21, the light is irradiated onto the observation site via the optical fiber 28. Also,
The reflected light from the observation site passes through the lens 41 and is reflected by the beam splitter 40.
2 and enters a nonlinear optical element such as KDP43.
一方、前記パルスレーザ−３７から出射され、ビームス
プリッタ３９で反射された光は、遅延ミラー装置４４の
ミラー４４ａ、４４ｂで反射され、ミラー４５を経て前
記ビームスズリツタ４２で反射され、参照光として前記
ＫＤＰ４３に入射されるようになっている。On the other hand, the light emitted from the pulse laser 37 and reflected by the beam splitter 39 is reflected by the mirrors 44a and 44b of the delay mirror device 44, passes through the mirror 45, and is reflected by the beam tinter 42, and is used as reference light. The light is input to the KDP 43.
前記ＫＤＰ４３は、観察部位からの反射光と前記参照光
とを入力することにより、第２高調波を発生する。この
第２高調波はフィルタ４６を通過して光電子増倍管４７
により検出されるようになっており、前記フィルタ４６
は、前記パルスレーザ−３７の出射光の波長をλとしな
とき、第２高調波である波長λ／２を含む狭い帯域を通
過させる特性となっている。The KDP 43 generates a second harmonic by inputting the reflected light from the observation site and the reference light. This second harmonic passes through a filter 46 and passes through a photomultiplier tube 47.
The filter 46
When the wavelength of the light emitted from the pulsed laser 37 is λ, it has a characteristic of passing a narrow band including the second harmonic wavelength λ/2.
また、前記遅延ミラー装置４４は、互いに対向するミラ
ー４４ａ、４４ｂが可動ステージ４４ｃに固定され、こ
の可動ステージ４４ｃを移動させる移動装置４４ｄがモ
ータ４４ｅによって駆動されて前記参照先の光路長を変
化させるようになっている。Further, in the delay mirror device 44, mirrors 44a and 44b facing each other are fixed to a movable stage 44c, and a moving device 44d for moving the movable stage 44c is driven by a motor 44e to change the optical path length of the reference destination. It looks like this.
前記ＫＤＰ４３が発生する第２高調波の強度は、前記反
射光と参照光をそれぞれ時間の関数とした場合の反射光
と参照光の積の積分値に比例するため、前記ミラー４４
ａ、４４ｂを移動させて参照光の光路長を変化させるこ
とにより、観察部位内部からの反射光の任意の時間成分
の強度を、前記光電子増倍管４７で検出することができ
る。The intensity of the second harmonic generated by the KDP 43 is proportional to the integral value of the product of the reflected light and the reference light when each of the reflected light and the reference light is a function of time.
By moving a and 44b to change the optical path length of the reference light, the intensity of any time component of the reflected light from inside the observation site can be detected by the photomultiplier tube 47.
前記光電子増倍管４７の出力は、画像処理装置２３に入
力され、この画像処理装置２３内には、同期検波増幅器
と直流電流計とを組合わせて前記光電子増倍管４７の出
力を高感度に検出するロックインアンプ４８、このロッ
クインアンプ４８からのアナログ信号をデジタル信号に
変換するＡ／Ｄコンバータ４９、及び、このＡ／Ｄコン
バータ４９からのデジタル信号を処理し、観察部位の光
断層像を画像処理するコンピュータ５０を備えている。The output of the photomultiplier tube 47 is input to an image processing device 23, and the image processing device 23 includes a combination of a synchronous detection amplifier and a DC ammeter to convert the output of the photomultiplier tube 47 into a high-sensitivity device. an A/D converter 49 that converts the analog signal from the lock-in amplifier 48 into a digital signal, and an A/D converter 49 that processes the digital signal from the A/D converter 49 to detect the optical tomography of the observation site. It is equipped with a computer 50 that processes the image.
次に、本実施例の作用について説明する。Next, the operation of this embodiment will be explained.
プローブ２１の挿入部２５を生体などの被検体内部に挿
入し、この挿入部２５の先端側を観察部位に位置させ、
次いで、光断層処理制御部２２内のパルスレーザ３７よ
り数ピコ秒の光パルスを出射させる。この光パルスは、
ビームスプリッタ３９．４０を透過し、レンズ４１を介
して光ファイバ２８に入射され、この光フアイバ２８内
を導かれて先端面から出射される。Insert the insertion part 25 of the probe 21 into a subject such as a living body, position the distal end of the insertion part 25 at the observation site,
Next, a pulse laser 37 in the optical tomography processing control unit 22 emits a light pulse of several picoseconds. This light pulse is
The light passes through the beam splitters 39 and 40, enters the optical fiber 28 via the lens 41, is guided through the optical fiber 28, and is emitted from the tip end.
前記光ファイバ２８から出射された光パルスは、透光性
カバー２７内に露呈するフレキシブルシャフト２９先端
のミラー３１で反射され、レンズ３２を介して前記挿入
部２５側方に出射されて観察部位に照射される。The light pulse emitted from the optical fiber 28 is reflected by a mirror 31 at the tip of the flexible shaft 29 exposed in the transparent cover 27, and is emitted to the side of the insertion section 25 via a lens 32 to reach the observation site. irradiated.
そして、照射された光パルスが、生体組織表面及び内部
の屈折率の異なる境界面で反射されると、反射光パルス
が前記光ファイバ２８により前記光断層処理制御部２２
に導かれ、前記レンズ４１ににより良光されて前記ビー
ムスプリッタ４つで反射され、ビームスプリッタ４２を
透過してＫＤＰ４３に入射される。When the irradiated light pulse is reflected at the interface between the surface and inside of the biological tissue having different refractive indexes, the reflected light pulse is transmitted to the optical tomography processing control unit 22 by the optical fiber 28.
The light is guided by the lens 41, reflected by the four beam splitters, transmitted through the beam splitter 42, and incident on the KDP 43.
このとき、前記パルスレーザ−３７より出射されビーム
スプリッタ３９にて分離された光パルスは、ミラー４４
ａ、４４ｂ→ビームスプリツタ４５→ビームスプリツタ
４２へと導かれ、このビームスプリッタ４２で反射され
て前記ＫＤＰ４Ｂに参照光として入射される。At this time, the optical pulses emitted from the pulse laser 37 and separated by the beam splitter 39 are sent to the mirror 44.
a, 44b→beam splitter 45→beam splitter 42, is reflected by this beam splitter 42, and enters the KDP 4B as a reference light.
このＫＤＰ４３で発生した第２高調波は、フィルタ４６
を介して光電子増倍管４７により検出され、さらに、ロ
ックインアンプ４８を経てＡ／Ｄコンバータ４９により
デジタル信号に変換されてコンピュータ５０に入力され
る。The second harmonic generated by this KDP43 is transmitted to the filter 46
The signal is detected by a photomultiplier tube 47 via a lock-in amplifier 48, converted into a digital signal by an A/D converter 49, and input to a computer 50.
同時に、前記プローブ２１の操作部２６に内蔵されたモ
ータ３５が、エンコーダ３６の出力に基づいて制御回路
２４によりフィードバック制御され、一定の回転数で回
転させられる。前記モータ３５の回転は、ギア３３．３
４を介して前記フレキシブルシャフト２９に伝達され、
このフレキシブルシャフト２９先端の前記ミラー３１が
回転さぜられる。At the same time, the motor 35 built in the operating section 26 of the probe 21 is feedback-controlled by the control circuit 24 based on the output of the encoder 36, and is rotated at a constant rotation speed. The rotation of the motor 35 is controlled by the gear 33.3.
4 to the flexible shaft 29,
The mirror 31 at the tip of the flexible shaft 29 is rotated.
そして、前記挿入部２５から放射状に光走査が行われて
上記動作が繰返されると、観察部位の各位置での反射光
の時間成分の強度が検出され、前記制御回路２４からの
走査位置情報とともに前記コンピュータ５０にて処理さ
れる。その結果、観察部位の光断層像が構築され、図示
しない表示器に表示される。Then, when light scanning is performed radially from the insertion section 25 and the above operation is repeated, the intensity of the time component of the reflected light at each position of the observation site is detected, and together with the scanning position information from the control circuit 24, Processed by the computer 50. As a result, an optical tomographic image of the observed region is constructed and displayed on a display (not shown).
この第２実施例においても、前述した第１実施例同様、
光断層像の観察に際して、前記挿入部２５の複雑な湾曲
操作を要することなく、希望する観察部位の光断層像を
容易に得ることができる。In this second embodiment as well, like the first embodiment described above,
When observing an optical tomographic image, it is possible to easily obtain an optical tomographic image of a desired observation site without requiring a complicated bending operation of the insertion section 25.
ところで、前記プローブ２１を用いて光断層像観察を行
なう際には、第７図に示すように、前記挿入部２５に装
着したプローブ保持用バルーン５１を使用することが望
ましい。Incidentally, when observing an optical tomographic image using the probe 21, it is desirable to use a probe holding balloon 51 attached to the insertion section 25, as shown in FIG.
この場合、前記挿入部２５を被検体内部に挿入し、先端
部が観察部位に達したとき、送吸気用チャンネル５２か
ら前記バルーン５１に送気することにより、前記挿入部
２５の位置がずれないよう保持することができ、被検体
内部からの反射光強度が小さい場合などの積分値に対し
、ノイズを低減してＳ／Ｎ比を向上させることができる
という利点を有する。In this case, when the insertion section 25 is inserted into the subject and the tip reaches the observation site, air is supplied from the air supply/intake channel 52 to the balloon 51 so that the insertion section 25 is not displaced. This has the advantage that noise can be reduced and the S/N ratio can be improved with respect to an integral value when the intensity of reflected light from inside the subject is small.
第８図以下は本発明の第３実施例を示し、第８図は光断
層像観察のための内視鏡装置の構成図、第９図はシステ
ム構成図、第１０図は光フアイバ用外装チューブの構成
を示す断面図である。Figure 8 and subsequent figures show a third embodiment of the present invention, in which Figure 8 is a configuration diagram of an endoscope device for observing optical tomographic images, Figure 9 is a system configuration diagram, and Figure 10 is an exterior for optical fibers. FIG. 3 is a cross-sectional view showing the configuration of a tube.
第８図に示すように、内視鏡装置は、内視鏡６０と、こ
の内視鏡６０が接続される光源装置６１゜ビデオプロセ
ッサ６２及び光断層処理装置６３と、前記ビデオプロセ
ッサ６２に接続されるモニタ６４とを備えている。As shown in FIG. 8, the endoscope apparatus includes an endoscope 60, a light source device 61 to which the endoscope 60 is connected, a video processor 62, an optical tomographic processing device 63, and a video processor 62 connected to the video processor 62. A monitor 64 is provided.
前記内視鏡６０は、細長で可撓性を有する挿入部６５と
、この挿入部６５の後端に連設された操作部６６と、こ
の操作部６６の側部から延出されたユニバーサルコード
６７とを備えている。The endoscope 60 includes an elongated and flexible insertion section 65, an operation section 66 connected to the rear end of the insertion section 65, and a universal cord extending from the side of the operation section 66. 67.
前記ユニバーサルコード６７内には、前記光源装置６１
からの照明光を伝送する図示しないライトガイドが挿通
されており、また、前記ユニバーサルコード６７の端部
には、前記光源装置６１に着脱自在に接続される光源コ
ネクタ６８が設けられている。この光源コネクタ６８か
らは、信号ケーブル６９が延出され、この信号ケーブル
６９の端部に、前記ビデオプロセッサ６２に着脱自在に
接続される信号コネクタ７０が設けられている。The light source device 61 is included in the universal cord 67.
A light guide (not shown) that transmits illumination light from the universal cord 67 is inserted through the universal cord 67, and a light source connector 68 that is detachably connected to the light source device 61 is provided at the end of the universal cord 67. A signal cable 69 extends from the light source connector 68, and a signal connector 70 that is detachably connected to the video processor 62 is provided at the end of the signal cable 69.
また、前記操作部６６には、前記挿入部６５に設けられ
た湾曲部を湾曲操作するための湾曲操作ノブ７１と、ラ
イトガイド駆動部７２とが設けられ、このライトガイド
駆動部７２と前記光断層処理装置６３とが、ライドガイ
ド７３を介して接続されている。Further, the operation section 66 is provided with a bending operation knob 71 for bending the bending section provided in the insertion section 65 and a light guide drive section 72. A fault processing device 63 is connected via a ride guide 73.
また、前記挿入部６５の先端部７４の側部には、観察窓
７５と２つの照明窓７６が設けられ、前記先端部７４の
最前端部には、先端が閉塞された円筒状の透光性カバー
７７が装着されている。Further, an observation window 75 and two illumination windows 76 are provided on the sides of the distal end 74 of the insertion section 65, and a cylindrical light-transmitting window with a closed end is provided at the front end of the distal end 74. A sex cover 77 is attached.
さらに、前記挿入部６５及び操作部６６内には、先端側
が前記透光性カバー７７内に連通し、後端側が前記ライ
トガイド駆動部７２に接続されたチャンネル７８が設け
られている。Furthermore, a channel 78 is provided in the insertion section 65 and the operation section 66, the distal end side of which communicates with the translucent cover 77, and the rear end side connected to the light guide drive section 72.
第９図に示すように、前記観察窓７５の内側には、対物
レンズ７９が設けられるとともに、この対物レンズ７９
の結像位置にＣＣＤ８０が設けられ、このＣＣＤ８０に
駆動回路８１が接続されている。この駆動部＃Ｉ８１に
接続された信号線８２は、挿入部６５．操作部６６、ユ
ニバーサルコード６７、光源コネクタ６８及び信号ケー
ブル６９内を挿通されて信号コネクタ７０に接続され、
この信号コネクタ７０を介してビデオプロセッサ６２に
接続されるようになっている。As shown in FIG. 9, an objective lens 79 is provided inside the observation window 75.
A CCD 80 is provided at the imaging position, and a drive circuit 81 is connected to this CCD 80. The signal line 82 connected to this drive section #I81 is connected to the insertion section 65. It is inserted through the operation unit 66, the universal cord 67, the light source connector 68, and the signal cable 69 and connected to the signal connector 70,
It is connected to the video processor 62 via this signal connector 70.
また、前記チャンネル７８内には、光断層像観察のため
のライトガイド８３が挿通されている。Further, a light guide 83 for observing an optical tomographic image is inserted into the channel 78.
このライトガイド８３の先端面には、前記透光性カバー
７７内に配設され、光軸を先端部７４の側方に向けるプ
リズム８４が固着されている。A prism 84 is fixed to the distal end surface of the light guide 83, which is disposed within the translucent cover 77 and whose optical axis is directed to the side of the distal end portion 74.
一方、前記ライトガイド８３の後端部は、前記ライトガ
イド駆動部７２内に導入されており、前記ライトガイド
駆動部７２内において、前記ライトガイド８３の後端部
に円筒状の口金８５が固定されている。また、前記ライ
トガイド駆動部７２内には、前記口金８５を回転自在に
支持する軸受８６が設けられ、前記口金８５にギア８７
が外嵌固定されて、このギア８７にギア８８が噛合して
いる。On the other hand, the rear end of the light guide 83 is introduced into the light guide drive section 72, and a cylindrical base 85 is fixed to the rear end of the light guide 83 within the light guide drive section 72. has been done. Further, a bearing 86 that rotatably supports the base 85 is provided in the light guide drive unit 72, and a gear 87 is provided on the base 85.
is externally fitted and fixed, and a gear 88 meshes with this gear 87.
前記ギア８８は、第１のパルスモータ８９の出力軸に固
定され、この第１のパルスモータ８９及び前記軸受８６
は、ラック９０に固定されている。The gear 88 is fixed to the output shaft of a first pulse motor 89, and the first pulse motor 89 and the bearing 86
is fixed to the rack 90.
さらに、このラック９０には、第２のパルスモータ９］
の出力軸に固定されたビニオン９２が噛合している。Furthermore, this rack 90 includes a second pulse motor 9]
A pinion 92 fixed to the output shaft is engaged with the output shaft.
従って、前記第１のパルスモータ８９を回転させること
により前記ライトガイド８３が回転し、前記第２のパル
スモータ９１を回転させることにより、前記ラック９０
を介して前記ライトガイド８３が進退するようになって
いる。Therefore, by rotating the first pulse motor 89, the light guide 83 is rotated, and by rotating the second pulse motor 91, the rack 90 is rotated.
The light guide 83 moves forward and backward through the.
また、前記光断層処理装置６３内には、前述の第２実施
例と同様のパルスレーザ−３７，ＫＤＰ４３、フィルタ
４６．光電子増倍管４７９画像処理装置２３などが備え
られ、前記パルスレーザ−３７からの出射光が、前記ラ
イトガイド７３内の光ファイバ束７３ａを介して前記ラ
イトガイド駆動部７２内のレーザーミラー群に入射され
る。Further, inside the optical tomography processing apparatus 63, a pulse laser 37, a KDP 43, a filter 46. A photomultiplier tube 479, an image processing device 23, etc. are provided, and the emitted light from the pulse laser 37 is transmitted to a group of laser mirrors in the light guide drive unit 72 via an optical fiber bundle 73a in the light guide 73. It is incident.
このレーザーミラー群においては、前述の第２実施例同
様、ビームスプリッタ３９によって前記パルスレーザ−
３７からの出射光が２つに分離され、前記ビームスプリ
ッタ３９を透過した光は、さらにビームスプリッタ４０
を透過して前記ライトガイド８３に入射され、被検体内
部の観察部位に照射されるようになっている。In this laser mirror group, as in the second embodiment described above, the beam splitter 39
The light emitted from the beam splitter 37 is separated into two, and the light transmitted through the beam splitter 39 is further transmitted to the beam splitter 40.
The light passes through and enters the light guide 83, and is irradiated onto the observation site inside the subject.
また、この観察部位からの反射光は、前記ライトガイド
８３から前記ビームスプリッタ４０に導かれ、このビー
ムスプリッタ４０で反射されてビームスプリッタ４２を
透過し、前記ライドガイド７３内の光ファイバ束７３ｂ
を経てＫＤＰ４３に入射されるようになっている。Further, the reflected light from this observation site is guided from the light guide 83 to the beam splitter 40, reflected by the beam splitter 40, and transmitted through the beam splitter 42, and is then connected to the optical fiber bundle 73b in the ride guide 73.
The light is then input to the KDP43.
一方、前記パルスレーザ−３７から出射され、ビームス
プリッタ３９で反射された光は、遅延ミラー装置４３の
ミラー４４ａ、４４ｂで反射され、さらに、ミラー４５
を経て前記ビームスプリッタ４２で反射され、前記光フ
ァイバ束７３ｂを経て参照光として前記ＫＤＰ４３に入
射されるようになっている。On the other hand, the light emitted from the pulse laser 37 and reflected by the beam splitter 39 is reflected by the mirrors 44a and 44b of the delay mirror device 43, and further reflected by the mirror 45.
The light is reflected by the beam splitter 42, passes through the optical fiber bundle 73b, and enters the KDP 43 as a reference light.
そして、前述の第２実施例と同様、前記ＫＤＰ４３から
の第２高調波がフィルタ４６を通過して光電子増倍管４
７により検出され、ロックインアンプ４８．Ａ／Ｄコン
バータ４９を経てコンピュータ５０により画像処理され
る。As in the second embodiment, the second harmonic from the KDP 43 passes through the filter 46 and passes through the photomultiplier tube 4.
7 and lock-in amplifier 48. The image is processed by the computer 50 via the A/D converter 49.
前記コンピュータ５０で処理された画像信号は、例えば
、前記ビデオプロセッサ６２内のスーパーインボーズ回
路に入力され、このスーパーインボーズ回路では、内視
鏡画像の信号と光断層画像の信号とを合成し、モニタ６
４に表示するようになっている。The image signal processed by the computer 50 is input, for example, to a superimpose circuit in the video processor 62, and this superimpose circuit combines the endoscopic image signal and the optical tomographic image signal. , monitor 6
4 is displayed.
尚、前記ライトガイド８３は、第１０図に示すように、
前記口金８５に装着される第１の外装チューブ９３内に
、前記ライトガイド８３の光ファイバ束９４を被覆する
第２の外装チコーブ９５が設けられた構造となっており
、前記第２の外装チューブ９５の外径Ｄ２と、前記第１
の外装チューブ９３の内径Ｄ１との間のクリアランスが
、前記第２の外装チューブ９５の肉厚ｔとほぼ同程度に
設定されている。これにより、湾曲時の軸方向の動きが
確保され、前記光ファイバ束９４の耐久性が向上して折
損などを防止することができる。Incidentally, the light guide 83, as shown in FIG.
The structure is such that a second armored tube 95 that covers the optical fiber bundle 94 of the light guide 83 is provided inside the first armored tube 93 attached to the base 85, and the second armored tube 95 covers the optical fiber bundle 94 of the light guide 83. 95 and the first
The clearance between the inner diameter D1 of the exterior tube 93 and the second exterior tube 93 is set to be approximately the same as the wall thickness t of the second exterior tube 95. This ensures axial movement during bending, improves the durability of the optical fiber bundle 94, and prevents breakage.
次に、本実施例の作用について説明する。Next, the operation of this embodiment will be explained.
光源装置６１からの照明光は、ユニバーサルコード６７
内の図示しないライトガイドから照明窓７６を経て、被
検体、例えば臓器９６に照射される。この臓器９６の光
学像は、ＣＣＤ８０によって撮像される。このＣＣＤ８
０の出力信号は、ビチオプロセッサ６２内の映像信号処
理回路によって処理され、この映像信号処理回路からの
映像信号がスーパーインボーズ回路を経てモニタ６４に
入力され、このモニタ６４に内視鏡画像が表示される。The illumination light from the light source device 61 is transmitted through the universal code 67.
The light is irradiated from a light guide (not shown) inside the body through the illumination window 76 to the subject, for example, an organ 96. An optical image of this organ 96 is captured by the CCD 80. This CCD8
The output signal of 0 is processed by the video signal processing circuit in the video processor 62, and the video signal from this video signal processing circuit is input to the monitor 64 via the superimpose circuit, and the endoscope image is displayed on the monitor 64. is displayed.
一方、前記臓器９６の生体組織９７の光断層像観察する
場合には、まず、光断層処理装置６３内のパルスレーザ
−３７より数ピコ秒の光パルスを発生させる。この光パ
ルスは、ビームスプリッタ３９．４０を透過してライト
ガイド８３に入射され、このライトガイド８３からプリ
ズム８４を経て、臓器９６の生体組織９７に照射される
。On the other hand, when observing an optical tomographic image of the biological tissue 97 of the organ 96, first, a pulse laser 37 in the optical tomography processing device 63 generates a light pulse of several picoseconds. This light pulse passes through the beam splitter 39 , 40 and enters the light guide 83 , and from this light guide 83 passes through the prism 84 and is irradiated onto the biological tissue 97 of the organ 96 .
すると、照射された光パルスに対し、生体組織９７内の
屈折率の異なる境界面で反射された反射光パルスが、前
記ライトガイド８３を介して前述した第２実施例と同様
の光路を経て導光され、ＫＤＰ４３に参照光とともに入
射される。Then, with respect to the irradiated light pulse, the reflected light pulse reflected at the boundary surface with a different refractive index in the living tissue 97 is guided through the light guide 83 through the same optical path as in the second embodiment described above. The light is emitted and enters the KDP 43 together with the reference light.
このＫＤＰ４Ｂからの第２高調波は光電子増倍管４７で
検出され、ライトガイド駆動部７２にて前記ライトガイ
ド８３を進退１回転させて観測位置を走査しながら上記
動作を繰り返すことにより、生体組織９７の光断層像を
構成するのに必要なデータが取得される。The second harmonic from the KDP4B is detected by the photomultiplier tube 47, and the light guide drive unit 72 moves the light guide 83 forward and backward once, scanning the observation position and repeating the above operation, thereby detecting the biological tissue. Data necessary to construct 97 optical tomographic images is acquired.
そして、このデータを光断層像観察Ｗ６３で処理するこ
とにより光断層画像を構築し、ビデオプロセッサ６２内
のスーパーインポーズ回路により内視鏡画像と光断層画
像とを合成してモニタ６４に表示させる。Then, an optical tomographic image is constructed by processing this data in the optical tomographic image observation W63, and the endoscopic image and the optical tomographic image are combined by the superimpose circuit in the video processor 62 and displayed on the monitor 64. .
このように本実施例によれば、通常の内視鏡画像の観察
とともに、生体組［９７の光断層画像の観察が可能とな
る。その他の作用、効果は前述した各実施例と同様であ
る。As described above, according to this embodiment, it is possible to observe an optical tomographic image of a living body [97] in addition to observing a normal endoscopic image. Other functions and effects are the same as those of the embodiments described above.
［発明の効果］
以上述べたように本発明によれば、被検体内部に挿入す
る挿入部に、断層像観察のための光を前記挿入部から放
射状に走査する手段を備えたため、光走査が容易に行な
え、確実に断層像を得ることができるという効果がある
。[Effects of the Invention] As described above, according to the present invention, the insertion section inserted into the subject is provided with a means for scanning light for tomographic image observation radially from the insertion section, so that optical scanning is possible. This method has the advantage of being easy to perform and ensuring that tomographic images can be obtained.
第１図〜第３図は本発明の第１実施例を示し、第１図は
断層像観察用光走査装置の構成図、第２図は光ファイバ
の配置を示す説明図、第３図は光ファイバの先端形状を
示す説明図、第４図及び第５図は変形例を示し、第４図
は光ファイバの先端形状を示す説明図、第５図は断層像
観察用光走査装置の構成図、第６図及び第７図は本発明
の第２実施例を示し、第６図は光断層像観察のためのシ
ステム構成図、第７図はプローブ保持バルーンを示す説
明図、第８図以下は本発明の第３実施例を示し、第８図
は光断層像観察のための内視鏡装置の構成図、第９図は
システム構成図、第１０図は光フアイバ用外装チューブ
の構成を示す断面図である。
１・・・挿入部
２・・・光ファイバ束
３・・・送受光装置
４・・・ガルバノメータ
５・・・制御回路
第１図
第５図
３、補正をする者
事件との関係
住所
名 称
４、代理人
住所
氏 名
５、補正命令の０１寸
６、補正の対象
［七１■Ｅ書（自発）
平成２年１１月２６日1 to 3 show a first embodiment of the present invention, FIG. 1 is a configuration diagram of an optical scanning device for tomographic image observation, FIG. 2 is an explanatory diagram showing the arrangement of optical fibers, and FIG. 3 is an explanatory diagram showing the arrangement of optical fibers. An explanatory diagram showing the tip shape of an optical fiber, FIGS. 4 and 5 show modified examples, FIG. 4 is an explanatory diagram showing the tip shape of the optical fiber, and FIG. 5 is a configuration of an optical scanning device for tomographic image observation. 6 and 7 show a second embodiment of the present invention, FIG. 6 is a system configuration diagram for optical tomographic image observation, FIG. 7 is an explanatory diagram showing a probe holding balloon, and FIG. 8 The following shows a third embodiment of the present invention, FIG. 8 is a configuration diagram of an endoscope device for observing optical tomographic images, FIG. 9 is a system configuration diagram, and FIG. 10 is a configuration of an exterior tube for optical fiber. FIG. 1... Insertion section 2... Optical fiber bundle 3... Light transmitting/receiving device 4... Galvanometer 5... Control circuit Figure 1 Figure 5 Figure 3 Person making the correction Address and name related to the case 4. Address of agent Name 5. Amendment order 01 sun 6. Subject of amendment [71 ■ Letter E (voluntary) November 26, 1990
Claims (1)
を前記挿入部から放射状に走査する手段を備えたことを
特徴とする断層像観察用光走査装置。1. An optical scanning device for tomographic image observation, characterized in that an insertion section inserted into a subject is provided with means for scanning light for tomographic image observation radially from the insertion section.
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP02259914A JP3104984B2 (en) | 1990-09-27 | 1990-09-27 | Optical scanning device for tomographic image observation |
| US07/700,225 US5305759A (en) | 1990-09-26 | 1991-05-14 | Examined body interior information observing apparatus by using photo-pulses controlling gains for depths |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP02259914A JP3104984B2 (en) | 1990-09-27 | 1990-09-27 | Optical scanning device for tomographic image observation |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH04135550A true JPH04135550A (en) | 1992-05-11 |
| JP3104984B2 JP3104984B2 (en) | 2000-10-30 |
Family
ID=17340685
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP02259914A Expired - Fee Related JP3104984B2 (en) | 1990-09-26 | 1990-09-27 | Optical scanning device for tomographic image observation |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP3104984B2 (en) |
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