JPH0472162B2 - - Google Patents
Info
- Publication number
- JPH0472162B2 JPH0472162B2 JP57180818A JP18081882A JPH0472162B2 JP H0472162 B2 JPH0472162 B2 JP H0472162B2 JP 57180818 A JP57180818 A JP 57180818A JP 18081882 A JP18081882 A JP 18081882A JP H0472162 B2 JPH0472162 B2 JP H0472162B2
- Authority
- JP
- Japan
- Prior art keywords
- endoscope
- distance
- light
- output signal
- illumination
- 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.)
- Expired - Lifetime
Links
- 238000005259 measurement Methods 0.000 claims description 7
- 238000005286 illumination Methods 0.000 claims description 6
- 238000003384 imaging method Methods 0.000 claims description 4
- 239000011159 matrix material Substances 0.000 claims description 3
- 230000003287 optical effect Effects 0.000 claims description 3
- 238000010586 diagram Methods 0.000 description 6
- 238000000034 method Methods 0.000 description 4
- 239000003086 colorant Substances 0.000 description 1
- 230000002452 interceptive effect Effects 0.000 description 1
- 230000001678 irradiating effect Effects 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
- G01B11/00—Measuring arrangements characterised by the use of optical techniques
- G01B11/02—Measuring arrangements characterised by the use of optical techniques for measuring length, width or thickness
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/107—Measuring physical dimensions, e.g. size of the entire body or parts thereof
- A61B5/1076—Measuring physical dimensions, e.g. size of the entire body or parts thereof for measuring dimensions inside body cavities, e.g. using catheters
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Physics & Mathematics (AREA)
- Heart & Thoracic Surgery (AREA)
- Molecular Biology (AREA)
- Dentistry (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- General Physics & Mathematics (AREA)
- Medical Informatics (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Endoscopes (AREA)
- Length Measuring Devices By Optical Means (AREA)
- Instruments For Viewing The Inside Of Hollow Bodies (AREA)
Description
【発明の詳細な説明】
この発明は、患部の実際の長さを測ることがで
きる内視鏡自動計測装置に関する。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to an automatic endoscope measuring device that can measure the actual length of an affected area.
一般に、内視鏡を用いて体腔内を観察する場
合、対物端と体腔壁との距離によつて得られる像
の倍率が変わる。そのため、内視鏡像そのものだ
けでは患部の実際の長さの計測は不可能である。
これに対処するために、従来は鉗子を使つて患部
にスケールを置いて長さを測定している。ここ
で、体腔壁は常に動いているので、スケールを置
くことは困難であり、計測に時間がかかるという
欠点がある。また、スケールを置くことにより、
視野が妨げられ、観察に支障をおよぼす虞れがあ
る。 Generally, when observing the inside of a body cavity using an endoscope, the magnification of the image obtained changes depending on the distance between the objective end and the body cavity wall. Therefore, it is impossible to measure the actual length of the affected area using only the endoscopic image itself.
To deal with this, traditionally, forceps are used to place a scale on the affected area to measure the length. Here, since the body cavity wall is constantly moving, it is difficult to place a scale, and there is a drawback that measurement takes time. Also, by placing a scale,
There is a risk that the field of view will be obstructed and observation will be hindered.
この発明の目的は、観察に支障をおよぼすこと
なく簡単に被写体の実際の長さを計測することが
できる内視鏡自動計測装置を提供することであ
る。 An object of the present invention is to provide an endoscope automatic measuring device that can easily measure the actual length of a subject without interfering with observation.
以下、図面を参照してこの発明による内視鏡自
動計測装置の一実施例を説明する。第１図はその
概略的ブロツク図である。ライトガイド１２とイ
メージガイド１０を有する内視鏡１４の接眼部に
テレビジヨンカメラ１６が取付けられる。ライト
ガイド１２の一端は光源ユニツト１８に導びかれ
る。光源ユニツト１８は照明用ランプ２０とレー
ザ発振器２２を有し、両者からの光がハーフミラ
ー２４を介してライトガイド１２の一端に入射さ
れるように構成される。ライトガイド１２の先端
（対物端）からは、照明光が第１図に実線で示す
ように拡散的に放射され、測距用ビーム光として
のレーザ光が第１図に破線で示すように所定角度
で（ここでは、ライトガイド１２に沿つて）放射
される。テレビジヨンカメラ１６の出力信号が計
測部２６および表示部２８に供給される。計測部
２６の出力信号も表示部２８に供給される。 DESCRIPTION OF THE PREFERRED EMBODIMENTS An embodiment of an automatic endoscope measuring device according to the present invention will be described below with reference to the drawings. FIG. 1 is a schematic block diagram thereof. A television camera 16 is attached to an eyepiece of an endoscope 14 having a light guide 12 and an image guide 10. One end of the light guide 12 is guided to a light source unit 18. The light source unit 18 has an illumination lamp 20 and a laser oscillator 22, and is configured so that light from both is incident on one end of the light guide 12 via a half mirror 24. Illumination light is emitted diffusely from the tip (objective end) of the light guide 12 as shown by the solid line in FIG. It is emitted at an angle (here along the light guide 12). An output signal from the television camera 16 is supplied to a measuring section 26 and a display section 28 . The output signal of the measuring section 26 is also supplied to the display section 28 .
第２図は、この実施例の電気的構成を示すブロ
ツク図である。テレビジヨンカメラ１６は撮像素
子としてCCD３２を用いる。CCD３２は２次元
マトリクス状に配列された画素を有し、走査回路
３４により走査され、各画素毎の画素情報を出力
する。CCD３２の出力信号がコンパレータ３６
およびプロセスアンプ３８に供給される。コンパ
レータ３６はCCD３２の出力信号を基準レベル
VRと比較し、その出力はCPU４０に供給され
る。プロセスアンプ３８はCCD３２の出力信号
をテレビジヨン信号のフオーマツトに合つた画像
信号とし、その出力画像信号はビデオコントロー
ラ４２に供給される。ビデオコントローラ４２、
ROM４４、CRTモニタ４８がシステムバス５０
を介してCPU４０に接続される。ライトペン５
２がCPU４０に接続される。 FIG. 2 is a block diagram showing the electrical configuration of this embodiment. The television camera 16 uses a CCD 32 as an image sensor. The CCD 32 has pixels arranged in a two-dimensional matrix, is scanned by a scanning circuit 34, and outputs pixel information for each pixel. The output signal of CCD32 is sent to comparator 36
and is supplied to the process amplifier 38. Comparator 36 sets the output signal of CCD 32 to the reference level.
In comparison with VR, its output is supplied to the CPU 40. A process amplifier 38 converts the output signal of the CCD 32 into an image signal conforming to the format of a television signal, and the output image signal is supplied to a video controller 42. video controller 42,
ROM 44 and CRT monitor 48 are system bus 50
It is connected to the CPU 40 via. light pen 5
2 is connected to the CPU 40.
この実施例の動作を説明する。この発明では、
テレビジヨンカメラ１６の出力信号を表示する画
面上に写る被写体の実際の大きさは被写体までの
距離に応じることが利用される。すなわち、被写
体までの距離がわかつていれば、画面上での長さ
から実際の長さがわかる。そのため、まず、第３
図を参照して、この発明における測距の原理を説
明する。上述したように、ライトガイド１２の先
端からは破線で示すようにライトガイド１２に沿
つてレーザ光が放射されている。一方、イメージ
ガイド１０の先端には、一点鎖線で示すように距
離の増加とともに大きな画像が入射される。その
ため、距離に応じて画像中のレーザ光の照射位置
が異なる。この発明では、画像の直径（通常、イ
メージガイドは円形断面を有するので、画像は円
形である）の一端から測つた照射位置までの間隔
ａ，a′が距離に比例することを利用する。具体的
には、CCD３２のどの画素がレーザ光を受光し
たかによつて距離を測定する。すなわち、CCD
３２は２次元マトリクス状に配列された画素を有
するので、そのうちの一列の画素からの出力期間
中のどのタイミングでレーザ光が検出されるかに
よつて測距する。まず、あらかじめ、距離に対す
る照射位置を光学系の諸条件を考慮して求めて、
これをROM４４に格納しておく。ROM４４は、
画素位置に応じたアドレスにその距離情報を記憶
する。CCD３２の出力信号はプロセスアンプ３
８を介してビデオコントローラ４２に供給され、
CRTモニタ４８で内視鏡像が表示される。一方、
CCD３２の出力信号はコンパレータ３６で基準
レベルVRと比較される。この基準レベルは、レ
ーザ光の照射位置に対応する画素からの信号がコ
ンパレータ３６に供給されたときのみ、コンパレ
ータ３６から信号が出力されるように設定され
る。CPU４０は、CCD３２の走査のためのクロ
ツク信号となる走査回路３４の出力信号から同期
信号を検出して、コンパレータ３６からの信号の
出力タイミングが一列中のどの画素に対応するか
判断する。CPU４０がこの画素位置を検出する
と、ROM４４のこの位置に応じたアドレスから
距離情報が読出される。これにより、対物端と体
腔壁との距離が測定される。 The operation of this embodiment will be explained. In this invention,
It is utilized that the actual size of the object appearing on the screen displaying the output signal of the television camera 16 depends on the distance to the object. In other words, if you know the distance to the subject, you can find the actual length from the length on the screen. Therefore, first, the third
The principle of distance measurement in this invention will be explained with reference to the drawings. As described above, laser light is emitted from the tip of the light guide 12 along the light guide 12 as shown by the broken line. On the other hand, a large image is incident on the tip of the image guide 10 as the distance increases, as shown by the dashed line. Therefore, the irradiation position of the laser beam in the image differs depending on the distance. This invention utilizes the fact that the distances a and a' measured from one end of the diameter of the image (usually the image is circular because the image guide has a circular cross section) to the irradiation position are proportional to the distance. Specifically, the distance is measured depending on which pixel of the CCD 32 receives the laser beam. That is, CCD
Since the reference numeral 32 has pixels arranged in a two-dimensional matrix, the distance is measured depending on the timing during the output period from one row of the pixels when the laser beam is detected. First, determine the irradiation position relative to the distance in advance, taking into account the various conditions of the optical system.
This is stored in the ROM44. ROM44 is
The distance information is stored in an address corresponding to the pixel position. The output signal of CCD32 is the process amplifier 3
8 to the video controller 42;
An endoscopic image is displayed on the CRT monitor 48. on the other hand,
The output signal of the CCD 32 is compared with a reference level VR by a comparator 36. This reference level is set so that a signal is output from the comparator 36 only when a signal from a pixel corresponding to the laser beam irradiation position is supplied to the comparator 36. The CPU 40 detects a synchronizing signal from the output signal of the scanning circuit 34, which serves as a clock signal for scanning the CCD 32, and determines which pixel in the row the output timing of the signal from the comparator 36 corresponds to. When the CPU 40 detects this pixel position, distance information is read from the address corresponding to this position in the ROM 44. Thereby, the distance between the objective end and the body cavity wall is measured.
次に、操作者はCRTモニタ４８上で長さを測
りたい線分の両端をライトペン５２で指示する。
これにより、CPU４０にCRTモニタ４８上での
長さが入力される。CPU４０はこの長さと先に
求めた距離に基づいて、実際の長さを求め、ビデ
オコントローラ４２に供給し、第４図に示すよう
に内視鏡像とともに測長結果を表わす数値が表示
される。図中、点はレーザ光の照射位置を示す。 Next, the operator indicates on the CRT monitor 48 both ends of the line segment whose length is to be measured using the light pen 52.
As a result, the length on the CRT monitor 48 is input to the CPU 40. Based on this length and the previously determined distance, the CPU 40 determines the actual length and supplies it to the video controller 42, and as shown in FIG. 4, a numerical value representing the length measurement result is displayed together with the endoscopic image. In the figure, dots indicate the irradiation position of the laser beam.
このように、この実施例によれば、被写体にビ
ーム光を照射しこの照射位置を検出するだけで被
写体までの距離を求め、この距離と表示画面上の
長さとにより、簡単、かつ、観察に支障をおよぼ
さずに、実際の長さを求めることのできる内視鏡
自動計測装置が提供される。 In this way, according to this embodiment, the distance to the subject is determined simply by irradiating the subject with a beam of light and detecting the irradiation position, and this distance and the length on the display screen make it easy to observe. An automatic endoscope measuring device is provided that can determine the actual length without causing any trouble.
なお、上述の説明では、測距用ビーム光は可視
レーザ光としたが、Nd−YAGレーザ光のような
不可視レーザ光、あるいは、赤外光を用いてもよ
い。赤外光を用いる場合は、イメージガイド１０
とCCD３２の間に入射光を画像用のＲ、Ｇ、Ｂ
成分および赤外成分に分ける４色分解光学系を設
け、CCD３２も４色分設ける。また、テレビジ
ヨンカメラ１６は全て接眼部に設けるのではな
く、CCD等の撮像素子は対物端に設けてもよい。
あるいは、測距用レーザダイオードを内視鏡の先
端に設けてもよい。さらに、測距用には撮像用と
は別のラインセンサを用いてもよい。また、
CRTモニタ４８上での長さの入力は、キーボー
ド等から行なつてもよい。 In the above description, the distance measuring beam light is a visible laser light, but an invisible laser light such as a Nd-YAG laser light or an infrared light may also be used. When using infrared light, image guide 10
and CCD 32 to input the incident light into R, G, B for images.
A four-color separation optical system is provided that separates the infrared component and the infrared component, and the CCD 32 is also provided for four colors. Furthermore, the television camera 16 is not entirely provided at the eyepiece, and an image pickup device such as a CCD may be provided at the objective end.
Alternatively, a distance measuring laser diode may be provided at the tip of the endoscope. Furthermore, a line sensor different from that for imaging may be used for distance measurement. Also,
The length may be entered on the CRT monitor 48 using a keyboard or the like.
以上説明したように、この発明によれば、簡単
な構成で、かつ、観察に支障をおよぼさない内視
鏡自動計測装置が提供される。 As described above, according to the present invention, there is provided an automatic endoscope measurement device that has a simple configuration and does not interfere with observation.
第１図はこの発明による内視鏡自動計測装置の
一実施例のブロツク図、第２図はその電気的構成
を示すブロツク図、第３図はこの発明における測
距の原理を説明するための図、第４図はこの実施
例の表示の一例を示す図である。
１２……ライトガイド、２２……レーザ発振
器、３２……CCD、３６……コンパレータ、３
８……プロセスアンプ、４０……CPU、４２…
…ビデオコントローラ、４４……ROM、４８…
…CRTモニタ、５２……ライトペン。
Fig. 1 is a block diagram of an embodiment of an endoscope automatic measuring device according to the present invention, Fig. 2 is a block diagram showing its electrical configuration, and Fig. 3 is a block diagram for explaining the principle of distance measurement in this invention. FIG. 4 is a diagram showing an example of the display of this embodiment. 12...Light guide, 22...Laser oscillator, 32...CCD, 36...Comparator, 3
8...Process amplifier, 40...CPU, 42...
...Video controller, 44...ROM, 48...
...CRT monitor, 52...Light pen.
Claims (1)
る照明手段によつて得られる照明光で内部を観察
する内視鏡と、 前記内視鏡に接続して照明手段に照明光を供給
する光源装置と、 前記内視鏡により得られた光学像を撮像する２
次元マトリクス状に配列された画素を有する撮像
手段と、 測距用光源より上記照明手段を介して内視鏡の
対物部から出射方向が固定されたビーム光を放射
するビーム光放射手段と、 前記撮像手段の画素の出力信号から撮影画面に
おける前記ビーム光の照射位置を検出し、これに
もとづいて前記内視鏡の対物部と被写体との距離
を求める測距手段と、 前記撮像手段の出力信号を表示するモニタ手段
と、 このモニタ手段の画面上での任意の２点間の距
離を算出する手段からの距離情報と前記測距手段
からの距離情報とから前記２点間の実際の長さを
求める測長手段と、 を具備したことを特徴とする内視鏡自動計測装
置。 ２ 前記測長手段の出力信号が前記モニタ手段で
表示されることを特徴とする特許請求の範囲第１
項記載の内視鏡自動計測装置。[Scope of Claims] 1. An endoscope that is inserted into an object to be observed and observes the interior with illumination light obtained by illumination means consisting of a light guide; and an endoscope that is connected to the endoscope and illuminates the illumination means. a light source device that supplies light; and 2 that captures an optical image obtained by the endoscope.
an imaging means having pixels arranged in a dimensional matrix; a beam light emitting means for emitting a beam of light with a fixed output direction from the objective section of the endoscope from a distance measuring light source via the illumination means; a distance measuring means for detecting the irradiation position of the beam light on the photographing screen from the output signal of the pixel of the imaging means, and determining the distance between the objective section of the endoscope and the subject based on this; and the output signal of the imaging means. a monitor means for displaying the distance between the two arbitrary points on the screen of the monitor means, and an actual length between the two points based on the distance information from the means for calculating the distance between two arbitrary points on the screen of the monitor means and the distance information from the distance measuring means. What is claimed is: 1. An endoscope automatic measuring device comprising: a length measuring means for determining . 2. Claim 1, wherein the output signal of the length measuring means is displayed on the monitor means.
Endoscope automatic measurement device described in Section 1.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57180818A JPS5970903A (en) | 1982-10-15 | 1982-10-15 | Automatic measuring apparatus of endoscope |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57180818A JPS5970903A (en) | 1982-10-15 | 1982-10-15 | Automatic measuring apparatus of endoscope |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5970903A JPS5970903A (en) | 1984-04-21 |
| JPH0472162B2 true JPH0472162B2 (en) | 1992-11-17 |
Family
ID=16089889
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP57180818A Granted JPS5970903A (en) | 1982-10-15 | 1982-10-15 | Automatic measuring apparatus of endoscope |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS5970903A (en) |
Families Citing this family (18)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6468233A (en) * | 1987-09-10 | 1989-03-14 | Fuji Photo Optical Co Ltd | Object dimension measuring apparatus of electronic endoscope |
| JPH0698134B2 (en) * | 1988-03-17 | 1994-12-07 | 和雄 馬場 | Ultrasound endoscopy |
| US4980763A (en) * | 1989-06-12 | 1990-12-25 | Welch Allyn, Inc. | System for measuring objects viewed through a borescope |
| JP3418480B2 (en) * | 1995-04-17 | 2003-06-23 | 医療法人社団ケント会 | Medical support equipment |
| GB9610197D0 (en) * | 1996-05-15 | 1996-07-24 | Keymed Medicals & Ind Equip | Digitally measuring scopes using a high resolution edcoder |
| CN1399528A (en) * | 1999-09-24 | 2003-02-26 | 加拿大国家研究委员会 | Method and apparatus for performing intra-operative angiography |
| US20050182434A1 (en) | 2000-08-11 | 2005-08-18 | National Research Council Of Canada | Method and apparatus for performing intra-operative angiography |
| US20060239921A1 (en) | 2005-04-26 | 2006-10-26 | Novadaq Technologies Inc. | Real time vascular imaging during solid organ transplant |
| US20070122344A1 (en) | 2005-09-02 | 2007-05-31 | University Of Rochester Medical Center Office Of Technology Transfer | Intraoperative determination of nerve location |
| US20080161744A1 (en) | 2006-09-07 | 2008-07-03 | University Of Rochester Medical Center | Pre-And Intra-Operative Localization of Penile Sentinel Nodes |
| US8406860B2 (en) | 2008-01-25 | 2013-03-26 | Novadaq Technologies Inc. | Method for evaluating blush in myocardial tissue |
| US10219742B2 (en) | 2008-04-14 | 2019-03-05 | Novadaq Technologies ULC | Locating and analyzing perforator flaps for plastic and reconstructive surgery |
| WO2009135178A2 (en) | 2008-05-02 | 2009-11-05 | Flower Robert W | Methods for production and use of substance-loaded erythrocytes (s-les) for observation and treatment of microvascular hemodynamics |
| US10492671B2 (en) | 2009-05-08 | 2019-12-03 | Novadaq Technologies ULC | Near infra red fluorescence imaging for visualization of blood vessels during endoscopic harvest |
| EP2863801B8 (en) | 2012-06-21 | 2024-06-12 | Stryker Corporation | Quantification and analysis of angiography and perfusion |
| US9816930B2 (en) | 2014-09-29 | 2017-11-14 | Novadaq Technologies Inc. | Imaging a target fluorophore in a biological material in the presence of autofluorescence |
| WO2016055837A1 (en) | 2014-10-09 | 2016-04-14 | Novadaq Technologies Inc. | Quantification of absolute blood flow in tissue using fluorescence-mediated photoplethysmography |
| US11140305B2 (en) | 2017-02-10 | 2021-10-05 | Stryker European Operations Limited | Open-field handheld fluorescence imaging systems and methods |
-
1982
- 1982-10-15 JP JP57180818A patent/JPS5970903A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5970903A (en) | 1984-04-21 |
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