JP4009626B2 - Endoscope video signal processor - Google Patents

Endoscope video signal processor Download PDF

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JP4009626B2
JP4009626B2 JP2004250978A JP2004250978A JP4009626B2 JP 4009626 B2 JP4009626 B2 JP 4009626B2 JP 2004250978 A JP2004250978 A JP 2004250978A JP 2004250978 A JP2004250978 A JP 2004250978A JP 4009626 B2 JP4009626 B2 JP 4009626B2
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睦巳 大島
正一 天野
健二 山▲崎▼
和弘 後野
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オリンパス株式会社
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本発明は、内視鏡に設けられた撮像手段に対する信号処理を行う内視鏡用映像信号処理装置に関する。 The present invention relates to an endoscope video signal processing apparatus that performs signal processing on an imaging unit provided in an endoscope.

近年においては、撮像手段を備えた電子内視鏡は、各種の内視鏡検査等において広く採用されるようになった。
電子内視鏡を採用して内視鏡検査を行う場合には、白色光の下で、カラーの光学フィルタを備えた撮像素子を用いて、カラー撮像を行う同時式の内視鏡装置と、モノクロの撮像素子を用いてR,G,Bの面順次の照明光の下でそれぞれ撮像を行うことにより、カラー画像を生成する面順次方式の内視鏡装置があり、信号処理系は両者において異なる。 When performing endoscopic examination using an electronic endoscope, a simultaneous endoscope device that performs color imaging using an image sensor equipped with a color optical filter under white light and a simultaneous endoscope device. There is a surface-sequential endoscope device that generates a color image by performing imaging under R, G, and B surface-sequential illumination light using a monochrome image sensor, and both have signal processing systems. different.
また、例えば特開2002−95635号公報には、狭帯域の照明光を利用して、通常の可視光の場合に得られる光学情報では埋もれてしまい易い粘膜表層付近における深さ方向に対する血管走行の状態等をより識別し易い画像情報として表示することができる内視鏡装置が開示されている。 Further, for example, Japanese Patent Application Laid-Open No. 2002-95635 describes a blood vessel running in the depth direction near the surface layer of the mucous membrane, which is easily buried in the optical information obtained in the case of ordinary visible light by using the illumination light in a narrow band. An endoscope device capable of displaying a state or the like as image information that is easier to identify is disclosed. In recent years, electronic endoscopes equipped with imaging means have been widely adopted in various endoscopic examinations and the like. In recent years, electronic endoscopes equipped with imaging means have been widely adopted in various endoscopic examinations and the like.
When performing an endoscopic examination using an electronic endoscope, a simultaneous endoscope apparatus that performs color imaging using an imaging device including a color optical filter under white light; and 2. Description of the Related Art There is a field sequential endoscope apparatus that generates a color image by performing imaging under R, G, and B surface sequential illumination light using a monochrome image sensor, and the signal processing system is Different. When performing an endoscopic examination using an electronic endoscope, a simultaneous endoscope apparatus that performs color imaging using an imaging device including a color optical filter under white light; and 2. Description of the Related Art There is a field sequential endoscope apparatus that generates a color image by performing imaging under R, G, and B surface sequential illumination light using a monochrome image sensor, and the signal processing system is Different.
Further, for example, in Japanese Patent Application Laid-Open No. 2002-95635, blood vessel traveling in the depth direction in the vicinity of the mucosal surface layer, which is easily buried with optical information obtained in the case of normal visible light, using narrow-band illumination light is disclosed. An endoscope apparatus that can display a state or the like as image information that can be more easily identified is disclosed. Further, for example, in Japanese Patent Application Laid-Open No. 2002-95635, blood vessel traveling in the depth direction in the vicinity of the mucosal surface layer, which is easily buried with optical information obtained in the case of normal visible light, using narrow-band illumination light is disclosed. An optical apparatus that can display a state or the like as image information that can be more easily identified is disclosed.

上記公報の従来例においては、面順次で狭帯域の照明光を用いて狭帯域画像を生成するものであるため、R,G,Bの面順次の照明光の代わりに狭帯域の照明光に変更すれば、信号処理系における大きな変更を必要としないで、比較的簡単に狭帯域の画像を得ることが可能となる。
一方、図10は、従来例の同時式の電子内視鏡用の映像信号処理装置81の構成を示す。
色分離フィルタ82を備えた電荷結合素子(CCDと略記)83により撮像されたカラーの撮像信号は、映像信号処理装置81内のCDS回路84に入力され、CDS処理されてベースバンドの信号成分が抽出される。 The color image pickup signal captured by the charge coupling element (abbreviated as CCD) 83 provided with the color separation filter 82 is input to the CDS circuit 84 in the video signal processing device 81, and is CDS processed to obtain the baseband signal component. Be extracted. In the conventional example of the above publication, a narrow-band image is generated using a narrow-band illumination light in a frame sequence, so that a narrow-band illumination light is used instead of a R-, G-, and B-sequential illumination light. If changed, it is possible to obtain a narrow band image relatively easily without requiring a large change in the signal processing system. In the conventional example of the above publication, a narrow-band image is generated using a narrow-band illumination light in a frame sequence, so that a narrow-band illumination light is used instead of a R-, G-, and B- sequential illumination light. If changed, it is possible to obtain a narrow band image relatively easily without requiring a large change in the signal processing system.
On the other hand, FIG. 10 shows a configuration of a conventional video signal processing device 81 for a simultaneous electronic endoscope. On the other hand, FIG. 10 shows a configuration of a conventional video signal processing device 81 for a simultaneous electronic endoscope.
A color image pickup signal picked up by a charge coupled device (abbreviated as CCD) 83 having a color separation filter 82 is input to a CDS circuit 84 in the video signal processing device 81 and subjected to CDS processing to generate a baseband signal component. Extracted. A color image pickup signal picked up by a charge coupled device (abbreviated as CCD) 83 having a color separation filter 82 is input to a CDS circuit 84 in the video signal processing device 81 and subjected to CDS processing to generate a baseband signal component. Extracted.

このCDS回路84の出力信号は、A/D変換回路85に入力され、アナログ信号からデジタル信号に変換される。このデジタル信号は、Y/C分離回路86に入力され、このY/C分離回路86において、輝度信号Yと線順次の色信号(色差信号)Cとに分離される。
この輝度信号Yは、γ回路87を介してセレクタ88に入力される(この輝度信号をYh)と共に、第1のローパスフィルタ(LPFと略記)89に入力される。 The luminance signal Y is input to the selector 88 via the γ circuit 87 (this luminance signal is Yh) and is input to the first low-pass filter (abbreviated as LPF) 89. このLPF89は、広い帯域に設定されており、このLPF89により設定された帯域の輝度信号Ylが、第1マトリクス回路90に入力される。 The LPF 89 is set in a wide band, and the luminance signal Yl in the band set by the LPF 89 is input to the first matrix circuit 90.
また、色信号Cは、第2のLPF91を介して(線順次)同時化回路92に入力される。 Further, the color signal C is input to the simultaneous circuit 92 (line sequential) via the second LPF 91. この場合、第2のLPF91は、第1のLPF89より低帯域であある。 In this case, the second LPF 91 has a lower band than the first LPF 89.
同時化回路92は、同時化された色差信号Cr(=2R−G),Cb(=2B−G)を生成し、この色差信号Cr,Cbは、第1マトリクス回路90に入力される。 The simultaneous circuit 92 generates simultaneous color difference signals Cr (= 2R-G) and Cb (= 2B-G), and the color difference signals Cr and Cb are input to the first matrix circuit 90. The output signal of the CDS circuit 84 is input to the A / D conversion circuit 85 and converted from an analog signal to a digital signal. This digital signal is input to a Y / C separation circuit 86, where it is separated into a luminance signal Y and a line sequential color signal (color difference signal) C. The output signal of the CDS circuit 84 is input to the A / D conversion circuit 85 and converted from an analog signal to a digital signal. This digital signal is input to a Y / C separation circuit 86, where it is separated into a luminance signal Y and a line sequential color signal (color difference signal) C.
The luminance signal Y is input to the selector 88 via the γ circuit 87 (this luminance signal is Yh) and is input to a first low-pass filter (abbreviated as LPF) 89. The LPF 89 is set in a wide band, and the luminance signal Yl in the band set by the LPF 89 is input to the first matrix circuit 90. The luminance signal Y is input to the selector 88 via the γ circuit 87 (this luminance signal is Yh) and is input to a first low-pass filter (abbreviated as LPF) 89. The LPF 89 is set in a wide band, and the luminance signal Yl in the band set by the LPF 89 is input to the first matrix circuit 90.
The color signal C is input to the synchronization circuit 92 (line-sequentially) via the second LPF 91. In this case, the second LPF 91 has a lower band than the first LPF 89. The color signal C is input to the synchronization circuit 92 (line-sequentially) via the second LPF 91. In this case, the second LPF 91 has a lower band than the first LPF 89.
The synchronization circuit 92 generates synchronized color difference signals Cr (= 2R−G) and Cb (= 2B−G), and the color difference signals Cr and Cb are input to the first matrix circuit 90. The synchronization circuit 92 generates synchronized color difference signals Cr (= 2R−G) and Cb (= 2B−G), and the color difference signals Cr and Cb are input to the first matrix circuit 90.

第1マトリクス回路90は、輝度信号Yl及び色差信号Cr,Cbから3原色信号R1,G1,B1に変換して、γ回路93に出力する。γ回路93によりγ補正された3原色信号R2,G2,B2は、第2マトリクス回路94に入力され、この第2マトリクス回路94により、輝度信号Ynbiと、色差信号R−Y、B−Yに変換される。
この場合、第2マトリクス回路94により、3原色信号R2,G2,B2は、自然な色調となるように、輝度信号Ynbi及び色差信号R−Y、B−Yに変換される。 In this case, the second matrix circuit 94 converts the three primary color signals R2, G2, and B2 into the luminance signal Ynbi and the color difference signals RY and BY so as to have a natural color tone.
第2マトリクス回路94により出力される輝度信号Ynbiは、セレクタ88を経て拡大回路95に入力され、色差信号R−Y、B−Yは拡大回路95に入力される。 The luminance signal Ynbi output by the second matrix circuit 94 is input to the expansion circuit 95 via the selector 88, and the color difference signals RY and BY are input to the expansion circuit 95. セレクタ88は、Y/C分離回路86からγ補正した輝度信号Yhと、第2マトリクス回路94を経て入力される輝度信号Ynbiとを選択して拡大回路95に出力する。 The selector 88 selects the luminance signal Yh γ-corrected from the Y / C separation circuit 86 and the luminance signal Ynbi input via the second matrix circuit 94, and outputs the luminance signal Ynbi to the expansion circuit 95. The first matrix circuit 90 converts the luminance signal Yl and the color difference signals Cr, Cb into the three primary color signals R1, G1, B1, and outputs them to the γ circuit 93. The three primary color signals R2, G2, and B2 that have been γ-corrected by the γ circuit 93 are input to the second matrix circuit 94, and the second matrix circuit 94 converts the luminance signal Ynbi and the color difference signals RY and BY into the second matrix circuit 94. Converted. The first matrix circuit 90 converts the luminance signal Yl and the color difference signals Cr, Cb into the three primary color signals R1, G1, B1, and outputs them to the γ circuit 93. The three primary color signals R2, G2, and B2 that have been γ-corrected by the γ circuit 93 are input to the second matrix circuit 94, and the second matrix circuit 94 converts the luminance signal Ynbi and the color difference signals RY and BY into the second matrix circuit 94. Converted.
In this case, the second matrix circuit 94 converts the three primary color signals R2, G2, and B2 into a luminance signal Ynbi and color difference signals RY and BY so as to have a natural color tone. In this case, the second matrix circuit 94 converts the three primary color signals R2, G2, and B2 into a luminance signal Ynbi and color difference signals RY and BY so as to have a natural color tone.
The luminance signal Ynbi output from the second matrix circuit 94 is input to the expansion circuit 95 via the selector 88, and the color difference signals RY and BY are input to the expansion circuit 95. The selector 88 selects the luminance signal Yh subjected to γ correction from the Y / C separation circuit 86 and the luminance signal Ynbi input through the second matrix circuit 94 and outputs the selected luminance signal Ynbi to the enlargement circuit 95. The luminance signal Ynbi output from the second matrix circuit 94 is input to the expansion circuit 95 via the selector 88, and the color difference signals RY and BY are input to the expansion circuit 95. The selector 88 selects the luminance signal Yh subjected to γ correction from the Y / C separation circuit 86 and the luminance signal Ynbi input through the second matrix circuit 94 and outputs the selected luminance signal Ynbi to the enlargement circuit 95.

この拡大回路95により拡大処理された輝度信号Yh/Ynbiは、強調回路96を経て第3マトリクス回路97に入力され、拡大回路95により拡大処理された色差信号R−Y,B−Yは、強調回路96を通さないで第3マトリクス回路97に入力される。
そして、この第3マトリクス回路97により3原色信号R,G,Bに変換されて図示しないカラーモニタに出力される。
なお、セレクタ88は、通常光による通常光観察の場合には、輝度信号Yh側を選択し、狭帯域光の照明により狭帯域光観察の場合には、第2マトリクス回路94を通した輝度信号、つまりYnbiが選択されるようにしている。
この従来の映像信号処理装置81においては、標準的な映像信号の規格に準拠した信号処理を行うために、輝度信号Yに対しては広帯域による信号処理を実施し、色信号Cに対しては低帯域の信号処理を実施していた。 In this conventional video signal processing device 81, in order to perform signal processing conforming to a standard video signal standard, signal processing with a wide band is performed on the brightness signal Y and the color signal C is subjected to signal processing. Low-band signal processing was being carried out.
特開2002−95635号公報JP-A-2002-95635 The luminance signal Yh / Ynbi enlarged by the enlargement circuit 95 is input to the third matrix circuit 97 via the enhancement circuit 96, and the color difference signals RY and BY enlarged by the enlargement circuit 95 are enhanced. The signal is input to the third matrix circuit 97 without passing through the circuit 96. The luminance signal Yh / Ynbi enlarged by the enlargement circuit 95 is input to the third matrix circuit 97 via the enhancement circuit 96, and the color difference signals RY and BY enlarged by the enlargement circuit 95 are enhanced. The signal is input to the third matrix circuit 97 without passing through the circuit 96.
Then, the third matrix circuit 97 converts the signals to the three primary color signals R, G, B and outputs them to a color monitor (not shown). Then, the third matrix circuit 97 converts the signals to the three primary color signals R, G, B and outputs them to a color monitor (not shown).
Note that the selector 88 selects the luminance signal Yh side in the case of normal light observation with normal light, and the luminance signal that has passed through the second matrix circuit 94 in the case of narrow band light observation with illumination of narrow band light. That is, Ynbi is selected. Note that the selector 88 selects the luminance signal Yh side in the case of normal light observation with normal light, and the luminance signal that has passed through the second matrix circuit 94 in the case of narrow band light observation with illumination of narrow band light. That is, Ynbi is selected.
In this conventional video signal processing device 81, in order to perform signal processing conforming to the standard of a standard video signal, the luminance signal Y is subjected to wideband signal processing, and the color signal C is processed. Low-band signal processing was performed. In this conventional video signal processing device 81, in order to perform signal processing conforming to the standard of a standard video signal, the luminance signal Y is subjected to wideband signal processing, and the color signal C is processed. Low-band signal processing was performed.
JP 2002-95635 A JP 2002-95635 A

図10に示す従来例においては、通常光観察における画質を確保できていたが、狭帯域光観察においては、低帯域な色信号として処理されてしまい解像度が低い画像になる欠点があった。
更に、狭帯域光観察(NBI観察)時は、照明光を狭帯域化するため、観察画像が暗くなってしまうという問題がある。 Further, during narrow band light observation (NBI observation), there is a problem that the observed image becomes dark because the illumination light is narrowed. In the conventional example shown in FIG. 10, the image quality in the normal light observation can be ensured, but in the narrow-band light observation, there is a defect that the image is processed as a low-band color signal and the resolution is low. In the conventional example shown in FIG. 10, the image quality in the normal light observation can be ensured, but in the narrow-band light observation, there is a defect that the image is processed as a low-band color signal and the resolution is low.
Furthermore, during narrow band light observation (NBI observation), there is a problem that the observation image becomes dark because the illumination light is narrowed. Furthermore, during narrow band light observation (NBI observation), there is a problem that the observation image becomes dark because the illumination light is narrowed.

(発明の目的)
本発明は、上述した点に鑑みてなされたもので、通常光観察に対応できると共に、狭帯域光観察時にも画質の良い内視鏡画像が得られる内視鏡用映像信号処理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 points, and provides a video signal processing device for an endoscope that can be used for normal light observation and can obtain an endoscopic image with good image quality even during narrow band light observation. The purpose is. (Object of invention) (Object of invention)
The present invention has been made in view of the above-described points, and provides an endoscope video signal processing apparatus that can cope with normal light observation and obtain an endoscopic image with good image quality even during narrow-band light observation. For the purpose. The present invention has been made in view of the above-described points, and provides an endoscope video signal processing apparatus that can cope with normal light observation and obtain an endoscopic image with good image quality even during narrow-band light observation. For the purpose ..

本発明は、内視鏡に搭載されたカラー撮像を行うための色分離用光学フィルタを設けた撮像手段からの出力信号に対して、色分離手段により輝度信号と色差信号とに分離してカラーの映像信号を生成する信号処理を行う内視鏡用映像信号処理装置において、
可視領域の照明光の場合から狭帯域の照明光の場合の信号処理への切り替えに対応して、前記色分離手段により色分離された信号に対する処理特性を変更する処理特性変更手段と、前記色分離手段より分離された前記色差信号に対する帯域制限を行う帯域制限手段と、を具備し、
前記可視領域の照明光から狭帯域の照明光に切り替えられた場合に、前記処理特性変更手段は、前記帯域制限手段による通過帯域の特性を広帯域に変更することを特徴とする。 When the illumination light in the visible region is switched to the illumination light in a narrow band, the processing characteristic changing means changes the characteristics of the pass band by the band limiting means to a wide band. According to the present invention, an output signal from an imaging unit provided with a color separation optical filter for performing color imaging mounted on an endoscope is separated into a luminance signal and a color difference signal by a color separation unit. In an endoscope video signal processing apparatus that performs signal processing to generate a video signal of According to the present invention, an output signal from an imaging unit provided with a color separation optical filter for performing color imaging mounted on an endoscope is separated into a luminance signal and a color difference signal by a color separation unit. In an endoscope video signal processing apparatus that performs signal processing to generate a video signal of
In response to switching from the case of the illumination light in the visible region to the signal processing in the case of the narrow band illumination light, the processing characteristic changing means for changing the processing characteristics for the color separated signals by the color separating means, the color Band limiting means for performing band limitation on the color difference signal separated by the separating means, and In response to switching from the case of the illumination light in the visible region to the signal processing in the case of the narrow band illumination light, the processing characteristic changing means for changing the processing characteristics for the color separated signals by the color separating means, the color Band limiting means for performing band limitation on the color difference signal separated by the separating means, and
When the illumination light in the visible region is switched to illumination light in a narrow band, the processing characteristic changing unit changes the characteristic of the pass band by the band limiting unit to a wide band. When the illumination light in the visible region is switched to illumination light in a narrow band, the processing characteristic changing unit changes the characteristic of the pass band by the band limiting unit to a wide band.

本発明によれば、可視領域の照明光の場合に対応できると共に、狭帯域の照明光の場合への信号処理の際には、処理特性を変更することにより画質の良い画像が得られる。 According to the present invention, it is possible to deal with the case of illumination light in the visible region, and at the time of signal processing for the case of narrow-band illumination light, an image with good image quality can be obtained by changing the processing characteristics.

以下、図面を参照して本発明の実施例を説明する。 Embodiments of the present invention will be described below with reference to the drawings.

図1ないし図8は本発明の実施例1に係り、図1は本発明の実施例1を備えた内視鏡装置の構成を示し、図2は固体撮像素子に設けられた色分離フィルタのフィルタ配列の構成を示し、図3は狭帯域用フィルタの分光特性例を示し、図4は本実施例の動作説明用のフローチャートを示し、図5は輝度信号と色差信号における信号帯域を示し、図6は図5の特性を考慮して第1変形例において設定される第2マトリクス回路の係数を示し、図7は第2変形例における狭帯域用フィルタの分光特性を示し、図8は図7の場合において設定される第2マトリクス回路の係数を示す。
図1に示すように実施例1を備えた内視鏡装置1は、体腔内等に挿入され、内視鏡検査を行う電子内視鏡(以下、単に内視鏡と略記)2と、この内視鏡2に照明光を供給する光源装置3と、内視鏡2に内蔵された撮像手段を駆動すると共に、撮像手段の出力信号に対する信号処理を行う内視鏡用映像信号処理装置としてのビデオプロセッサ4と、このビデオプロセッサ4から出力される映像信号が入力されることにより、撮像手段により撮像した内視鏡画像を表示するモニタ5とを備えている。 As shown in FIG. 1, the endoscope device 1 provided with the first embodiment includes an electronic endoscope (hereinafter, simply abbreviated as an endoscope) 2 which is inserted into a body cavity or the like and performs endoscopy. As a video signal processing device for an endoscope that drives a light source device 3 that supplies illumination light to the endoscope 2 and an imaging means built in the endoscope 2 and processes signals for the output signal of the imaging means. It includes a video processor 4 and a monitor 5 that displays an endoscopic image captured by an imaging means by inputting a video signal output from the video processor 4. 1 to 8 relate to a first embodiment of the present invention, FIG. 1 shows a configuration of an endoscope apparatus including the first embodiment of the present invention, and FIG. 2 shows a color separation filter provided in a solid-state image sensor. FIG. 3 shows an example of spectral characteristics of the narrowband filter, FIG. 4 shows a flowchart for explaining the operation of the present embodiment, FIG. 5 shows a signal band in the luminance signal and the color difference signal, and FIG. 6 shows the coefficients of the second matrix circuit set in the first modification in consideration of the characteristics of FIG. 5, FIG. 7 shows the spectral characteristics of the narrowband filter in the second modification, and FIG. The coefficient of the 2nd matrix circuit set in the case of 7 is shown. 1 to 8 relate to a first embodiment of the present invention, FIG. 1 shows a configuration of an spectrometer including the first embodiment of the present invention, and FIG. 2 shows a color separation filter provided in a solid-state image sensor. FIG. 3 shows an example of spectral characteristics of the narrowband filter, FIG. 4 shows a flowchart for explaining the operation of the present embodiment, FIG. 5 shows a signal band in the luminance signal and the color difference signal, and FIG. 6 shows the coefficients of the second matrix circuit set in the first modification in consideration of the characteristics of FIG. 5, FIG. 7 shows the spectral characteristics of the narrowband filter in the second modification, and FIG. The coefficient of the 2nd matrix circuit set in the case of 7 is shown.
As shown in FIG. 1, an endoscope apparatus 1 having Example 1 includes an electronic endoscope (hereinafter simply abbreviated as an endoscope) 2 that is inserted into a body cavity or the like and performs endoscopy, As an endoscope video signal processing device that drives a light source device 3 that supplies illumination light to the endoscope 2 and an imaging means built in the endoscope 2 and performs signal processing on an output signal of the imaging means. A video processor 4 and a monitor 5 that displays an endoscopic image captured by the imaging means when a video signal output from the video processor 4 is input are provided. As shown in FIG. 1, an endoscope apparatus 1 having Example 1 includes an electronic endoscope (hereinafter simply abbreviated as an endoscope) 2 that is inserted into a body cavity or the like and performs endoscopy, As an endoscope video signal processing device that drives a light source device 3 that supplies illumination light to the endoscope 2 and an imaging means built in the endoscope 2 and performs signal processing on an output signal of the imaging means. A video processor 4 and a monitor 5 that displays an endoscopic image captured by the imaging means when a video signal output from the video processor 4 is input are provided.

内視鏡2は、細長の挿入部7と、この挿入部7の後端に設けられた操作部8と、この操作部8から延出されたユニバーサルケーブル9とを有し、このユニバーサルケーブル9の端部のライトガイドコネクタ11は、光源装置3に着脱自在に接続され、信号コネクタは、ビデオプロセッサ4に着脱自在に接続される。
上記挿入部7内には、照明光を伝送するライトガイド13が挿通され、このライトガイド13における手元側の端部のライトガイドコネクタ11を光源装置3に接続することにより、光源装置3からの照明光がライトガイド13に供給される。
光源装置3は、通常光観察モード時には、通常照明光としての白色光(可視領域)の照明光を発生して、ライトガイド13に供給し、狭帯域光観察モード時には、狭帯域の照明光を発生して、ライトガイド13に供給する。 In the normal light observation mode, the light source device 3 generates white light (visible region) illumination light as normal illumination light and supplies it to the light guide 13, and in the narrow band light observation mode, emits narrow band illumination light. It is generated and supplied to the light guide 13. The endoscope 2 includes an elongated insertion portion 7, an operation portion 8 provided at the rear end of the insertion portion 7, and a universal cable 9 extending from the operation portion 8. The light guide connector 11 at the end of this is detachably connected to the light source device 3, and the signal connector is detachably connected to the video processor 4. The endoscope 2 includes an elongated insertion portion 7, an operation portion 8 provided at the rear end of the insertion portion 7, and a universal cable 9 extending from the operation portion 8. The light guide connector 11 at the end of this is detachably connected to the light source device 3, and the signal connector is detachably connected to the video processor 4.
A light guide 13 that transmits illumination light is inserted into the insertion portion 7, and the light guide connector 11 at the end on the hand side of the light guide 13 is connected to the light source device 3. Illumination light is supplied to the light guide 13. A light guide 13 that transmits illumination light is inserted into the insertion portion 7, and the light guide connector 11 at the end on the hand side of the light guide 13 is connected to the light source device 3. Illumination light is supplied to the light guide 13.
In the normal light observation mode, the light source device 3 generates white light (visible region) illumination light as normal illumination light and supplies it to the light guide 13, and in the narrow band light observation mode, the narrow band illumination light is supplied. Generated and supplied to the light guide 13. In the normal light observation mode, the light source device 3 generates white light (visible region) illumination light as normal illumination light and supplies it to the light guide 13, and in the narrow band light observation mode, the narrow band illumination light is supplied . Generated and supplied to the light guide 13.

通常光観察モードと狭帯域光観察モードの切替指示は、例えば内視鏡2の操作部8に設けたスコープスイッチ等によるモード切替スイッチ14により行うことができる。なお、モード切替スイッチ14は、内視鏡2に設けたスコープスイッチで構成する他に、フットスイッチにより構成しても良いし、ビデオプロセッサ4のフロントパネルに設けても良いし、図示しないキーボードにより構成する等しても良い。
このモード切替スイッチ14による切替信号は、ビデオプロセッサ4内の制御回路15に入力され、切替信号が入力されると、この制御回路15は、光源装置3のフィルタ挿脱機構16を制御して、通常照明光と、狭帯域照明光とを選択的に切り替える。 The changeover signal by the mode changeover switch 14 is input to the control circuit 15 in the video processor 4, and when the changeover signal is input, the control circuit 15 controls the filter insertion / removal mechanism 16 of the light source device 3. Selectively switches between normal illumination light and narrow band illumination light.
また、後述するように、この制御回路15は、光源装置3からライトガイド13に供給する照明光の切替制御に連動して、ビデオプロセッサ4内の映像信号処理系の特性を切り替える制御も行う。 Further, as will be described later, the control circuit 15 also controls to switch the characteristics of the video signal processing system in the video processor 4 in conjunction with the switching control of the illumination light supplied from the light source device 3 to the light guide 13. そして、モード切替スイッチ14による切替操作により、映像信号処理系の特性を切り替えることにより、通常光観察モードと狭帯域光観察モードとにそれぞれ適した信号処理を行えるようにしている。 Then, by switching the characteristics of the video signal processing system by the switching operation by the mode changeover switch 14, signal processing suitable for the normal light observation mode and the narrow band light observation mode can be performed. The switching instruction between the normal light observation mode and the narrow-band light observation mode can be performed by, for example, the mode change switch 14 such as a scope switch provided in the operation unit 8 of the endoscope 2. In addition to the scope switch provided in the endoscope 2, the mode change switch 14 may be constituted by a foot switch, or may be provided on the front panel of the video processor 4, or by a keyboard (not shown). You may comprise. The switching instruction between the normal light observation mode and the narrow-band light observation mode can be performed by, for example, the mode change switch 14 such as a scope switch provided in the operation unit 8 of the endoscope 2. In addition to the scope switch provided in the endoscope 2, the mode change switch 14 may be composed by a foot switch, or may be provided on the front panel of the video processor 4, or by a keyboard (not shown).
The switching signal by the mode switch 14 is input to the control circuit 15 in the video processor 4. When the switching signal is input, the control circuit 15 controls the filter insertion / removal mechanism 16 of the light source device 3. The normal illumination light and the narrow-band illumination light are selectively switched. The switching signal by the mode switch 14 is input to the control circuit 15 in the video processor 4. When the switching signal is input, the control circuit 15 controls the filter insertion / removal mechanism 16 of the light source device 3. The normal illumination light and the narrow-band illumination light are selectively switched.
As will be described later, the control circuit 15 also performs control for switching the characteristics of the video signal processing system in the video processor 4 in conjunction with switching control of illumination light supplied from the light source device 3 to the light guide 13. Then, by switching the characteristics of the video signal processing system by the switching operation by the mode switch 14, signal processing suitable for the normal light observation mode and the narrowband light observation mode can be performed. As will be described later, the control circuit 15 also performs control for switching the characteristics of the video signal processing system in the video processor 4 in conjunction with switching control of illumination light supplied from the light source device 3 to the light guide 13. Then , by switching the characteristics of the video signal processing system by the switching operation by the mode switch 14, signal processing suitable for the normal light observation mode and the narrowband light observation mode can be performed.

光源装置3は、照明光を発生するランプ20を内蔵し、このランプ20は、可視光領域を含む照明光を発生する。この照明光は、赤外カットフィルタ21により赤外光がカットされて略白色光の波長帯域に近い照明光にされた後、絞り22に入射される。この絞り22は、絞り駆動回路23により、開口量が調整されてその通過光量が制御される。
この絞り22を通過した照明光は、プランジャなどにより構成されるフィルタ挿脱機構16により照明光路中に挿脱される狭帯域用フィルタ24を通して(狭帯域光観察モード時)、或いは狭帯域用フィルタ24を通さないで(通常光観察モード時)、集光レンズ25に入射され、この集光レンズ25により集光されてライトガイド13の手元側の端面、つまり入射端面に入射される。 The illumination light that has passed through the aperture 22 passes through the narrow band filter 24 that is inserted and removed in the illumination optical path by the filter insertion / removal mechanism 16 configured by a plunger or the like (in the narrow band light observation mode), or the narrow band filter. It is incident on the condenser lens 25 without passing through 24 (in the normal light observation mode), is condensed by the condenser lens 25, and is incident on the end face on the hand side of the light guide 13, that is, the incident end face.
図3は、狭帯域用フィルタ24の分光特性の1例を示す。 FIG. 3 shows an example of the spectral characteristics of the narrow band filter 24. この狭帯域用フィルタ24は、3峰性フィルタ特性を示し、例えば、赤、緑、青の各波長域において、それぞれ狭帯域透過フィルタ特性部Ra,Ga,Baを有する。 The narrow band filter 24 exhibits trimodal filter characteristics, and has narrow band transmission filter characteristic units Ra, Ga, and Ba in each of the red, green, and blue wavelength regions, respectively. The light source device 3 incorporates a lamp 20 that generates illumination light, and the lamp 20 generates illumination light including a visible light region. The illumination light is incident on the diaphragm 22 after the infrared light is cut by the infrared cut filter 21 so that the illumination light is close to the wavelength band of substantially white light. The aperture of the diaphragm 22 is adjusted by a diaphragm driving circuit 23 and the amount of light passing therethrough is controlled. The light source device 3 incorporates a lamp 20 that generates illumination light, and the lamp 20 generates illumination light including a visible light region. The illumination light is incident on the diaphragm 22 after the infrared light is cut by the infrared cut filter 21 so that The illumination light is close to the wavelength band of substantially white light. The aperture of the diaphragm 22 is adjusted by a diaphragm driving circuit 23 and the amount of light passing therethrough is controlled.
The illumination light that has passed through the diaphragm 22 passes through the narrow band filter 24 (in the narrow band light observation mode) inserted into and removed from the illumination optical path by the filter insertion / removal mechanism 16 constituted by a plunger or the like, or the narrow band filter. Without passing through 24 (in normal light observation mode), the light is incident on the condensing lens 25, collected by the condensing lens 25, and incident on the end face on the hand side of the light guide 13, that is, the incident end face. The illumination light that has passed through the diaphragm 22 passes through the narrow band filter 24 (in the narrow band light observation mode) inserted into and removed from the illumination optical path by the filter insertion / removal mechanism 16 configured by a plunger or the like , or the narrow band filter. Without passing through 24 (in normal light observation mode), the light is incident on the condensing lens 25, collected by the condensing lens 25, and incident on the end face on the hand side of the light guide 13, that is, the incident end face.
FIG. 3 shows an example of the spectral characteristics of the narrowband filter 24. The narrow band filter 24 exhibits a three-peak filter characteristic, and has, for example, narrow band transmission filter characteristic portions Ra, Ga, and Ba in red, green, and blue wavelength regions, respectively. FIG. 3 shows an example of the spectral characteristics of the narrowband filter 24. The narrow band filter 24 exhibits a three-peak filter characteristic, and has, for example, narrow band transmission filter characteristic portions Ra, Ga, and Ba in red, green, and blue wavelength regions, respectively.

より具体的には、狭帯域透過フィルタ特性部Ra,Ga,Baは、それぞれ中心波長が600nm、540nm、420nmであり、その半値幅が20〜40nmのバンドパス特性を有する。
従って、狭帯域用フィルタ24が照明光路中に配置された場合には、この狭帯域透過フィルタ特性部Ra,Ga,Baを透過した3バンドの狭帯域照明光がライトガイド13に入射される。
これに対して、狭帯域用フィルタ24を照明光路中に配置しない場合には、白色光がライトガイド13に供給されることになる。
ライトガイド13からの照明光は、ライトガイド13によりその先端面に伝送され、挿入部7の先端部26に設けた照明窓に取り付けた照明レンズ27を経て外部に出射され、体腔内の患部等の生体組織の表面を照明する。 The illumination light from the light guide 13 is transmitted to the tip surface of the light guide 13 and is emitted to the outside through an illumination lens 27 attached to an illumination window provided at the tip 26 of the insertion portion 7, and is emitted to the outside, such as an affected portion in a body cavity. Illuminate the surface of living tissue. More specifically, the narrow-band transmission filter characteristic portions Ra, Ga, and Ba have bandpass characteristics having center wavelengths of 600 nm, 540 nm, and 420 nm, respectively, and a half width of 20 to 40 nm. More specifically, the narrow-band transmission filter characteristic portions Ra, Ga, and Ba have bandpass characteristics having center wavelengths of 600 nm, 540 nm, and 420 nm, respectively, and a half width of 20 to 40 nm.
Accordingly, when the narrow band filter 24 is arranged in the illumination optical path, the three bands of narrow band illumination light transmitted through the narrow band transmission filter characteristic portions Ra, Ga, Ba are incident on the light guide 13. Accordingly, when the narrow band filter 24 is arranged in the illumination optical path, the three bands of narrow band illumination light transmitted through the narrow band transmission filter characteristic portions Ra, Ga, Ba are incident on the light guide 13.
On the other hand, when the narrow band filter 24 is not arranged in the illumination optical path, white light is supplied to the light guide 13. On the other hand, when the narrow band filter 24 is not arranged in the illumination optical path, white light is supplied to the light guide 13.
Illumination light from the light guide 13 is transmitted to the distal end surface thereof by the light guide 13, and is emitted to the outside through an illumination lens 27 attached to an illumination window provided at the distal end portion 26 of the insertion portion 7. Illuminate the surface of living tissue. Illumination light from the light guide 13 is transmitted to the distal end surface thereof by the light guide 13, and is emitted to the outside through an illumination lens 27 attached to an illumination window provided at the distal end portion 26 of the insertion portion 7. Illuminate the surface of living tissue.

先端部26には、照明窓に隣接して観察窓が設けてあり、この観察窓には対物レンズ28が取り付けられている。この対物レンズ28は、生体組織からの反射光による光学像を結像する。この対物レンズ28の結像位置には、固体撮像素子として電荷結合素子(CCDと略記)29が配置されており、このCCD29により光電変換される。
このCCD29の撮像面には、光学的に色分離する色分離フィルタ30として例えば図2に示す補色系フィルタが各画素単位で取り付けてある。 On the imaging surface of the CCD 29, for example, a complementary color filter shown in FIG. 2 is attached to each pixel as a color separation filter 30 that optically separates colors.
この補色系フィルタは、各画素の前に、マゼンタ(Mg)、グリーン(G)、シアン(Cy)、イエロ(Ye)の4色のカラーチップが、水平方向には、MgとGとが交互に配置され、縦方向には、Mg、Cy、Mg、YeとG、Ye、G、Cyとの配列順で、それぞれ配置されている。 In this complementary color filter, four color chips of magenta (Mg), green (G), cyan (Cy), and yellow (Ye) are arranged in front of each pixel, and Mg and G alternate in the horizontal direction. In the vertical direction, Mg, Cy, Mg, Ye and G, Ye, G, Cy are arranged in the order of arrangement. The distal end portion 26 is provided with an observation window adjacent to the illumination window, and an objective lens 28 is attached to the observation window. The objective lens 28 forms an optical image by reflected light from the living tissue. A charge coupled device (abbreviated as CCD) 29 is disposed as a solid-state imaging device at the imaging position of the objective lens 28, and photoelectric conversion is performed by the CCD 29. The distal end portion 26 is provided with an observation window adjacent to the illumination window, and an objective lens 28 is attached to the observation window. The objective lens 28 forms an optical image by reflected light from the living tissue. A charge coupled device ( abbreviated as CCD) 29 is disposed as a solid-state imaging device at the imaging position of the objective lens 28, and photoelectric conversion is performed by the CCD 29.
For example, a complementary color filter shown in FIG. 2 is attached to the image pickup surface of the CCD 29 for each pixel as a color separation filter 30 for optically color separation. For example, a complementary color filter shown in FIG. 2 is attached to the image pickup surface of the CCD 29 for each pixel as a color separation filter 30 for similarly color separation.
This complementary color filter has four color chips of magenta (Mg), green (G), cyan (Cy), and yellow (Ye) in front of each pixel, and Mg and G alternate in the horizontal direction. In the vertical direction, Mg, Cy, Mg, Ye and G, Ye, G, Cy are arranged in the order of arrangement. This complementary color filter has four color chips of magenta (Mg), green (G), cyan (Cy), and yellow (Ye) in front of each pixel, and Mg and G alternate in the horizontal direction. In the vertical direction, Mg, Cy, Mg, Ye and G, Ye, G, Cy are arranged in the order of arrangement.

そして、この補色系フィルタを用いたCCD29の場合、縦方向に隣接する2列の画素を加算して順次読み出すが、このとき奇数フィールドと偶数フィールドで画素の列をずらして読み出すようにする。そして、後段側での色分離回路により、公知のように輝度信号と色差信号とが生成されることになる。
上記CCD29は、信号線の一端と接続されており、この信号線の他端が接続された信号コネクタをビデオプロセッサ4に接続することにより、ビデオプロセッサ4内のCCD駆動回路31とCDS回路32とに接続される。 The CCD 29 is connected to one end of a signal line, and by connecting a signal connector to which the other end of the signal line is connected to the video processor 4, the CCD drive circuit 31 and the CDS circuit 32 in the video processor 4 are connected. Connected to.
なお、各内視鏡2は、その内視鏡2に固有の識別情報(ID)を発生するID発生部33を備え、ID発生部33によるIDは、制御回路15に入力され、制御回路15は、IDによりビデオプロセッサ4に接続された内視鏡2の種類やその内視鏡2の内蔵されたCCD29の画素数種類等を識別する。 Each endoscope 2 includes an ID generation unit 33 that generates identification information (ID) unique to the endoscope 2, and the ID generated by the ID generation unit 33 is input to the control circuit 15 to be input to the control circuit 15. Identifyes the type of endoscope 2 connected to the video processor 4 by ID, the number of pixels of the CCD 29 built in the endoscope 2, and the like. In the case of the CCD 29 using this complementary color filter, two adjacent columns of pixels in the vertical direction are added and sequentially read out. At this time, the pixel columns are shifted and read in the odd and even fields. Then, the luminance signal and the color difference signal are generated as is well known by the color separation circuit on the subsequent stage side. In the case of the CCD 29 using this complementary color filter, two adjacent columns of pixels in the vertical direction are added and sequentially read out. At this time, the pixel columns are correlated and read in the odd and even fields. Then, the Bright signal and the color difference signal are generated as is well known by the color separation circuit on the subsequent stage side.
The CCD 29 is connected to one end of a signal line. By connecting a signal connector to which the other end of the signal line is connected to the video processor 4, the CCD driving circuit 31 and the CDS circuit 32 in the video processor 4 are connected. Connected to. The CCD 29 is connected to one end of a signal line. By connecting a signal connector to which the other end of the signal line is connected to the video processor 4, the CCD driving circuit 31 and the CDS circuit 32 in the video processor 4 are connected. Connected to.
Each endoscope 2 includes an ID generation unit 33 that generates identification information (ID) unique to the endoscope 2, and the ID generated by the ID generation unit 33 is input to the control circuit 15, and the control circuit 15 Identifies the type of the endoscope 2 connected to the video processor 4 and the number of pixels of the CCD 29 built in the endoscope 2 by the ID. Each endoscope 2 includes an ID generation unit 33 that generates identification information (ID) unique to the endoscope 2, and the ID generated by the ID generation unit 33 is input to the control circuit 15, and the control circuit 15 Identifies the type of the endoscope 2 connected to the video processor 4 and the number of pixels of the CCD 29 built in the endoscope 2 by the ID.

そして、識別した内視鏡2のCCD29を適切に駆動するように制御回路15は、CCD駆動回路31を制御する。
CCD29は、CCD駆動回路31からのCCD駆動信号の印加により、光電変換された撮像信号は、相関二重サンプリング回路(CDS回路と略記)32に入力される。 In the CCD 29, the photoelectric-converted imaging signal is input to the correlation double sampling circuit (abbreviated as CDS circuit) 32 by applying the CCD drive signal from the CCD drive circuit 31. CDS回路32により、撮像信号から信号成分が抽出されてベースバンドの信号に変換された後、A/D変換回路34に入力され、デジタル信号に変換されると共に、明るさ検波回路35に入力され、明るさ(信号の平均輝度)が検出される。 After the signal component is extracted from the image pickup signal by the CDS circuit 32 and converted into a baseband signal, it is input to the A / D conversion circuit 34, converted into a digital signal, and input to the brightness detection circuit 35. , Brightness (average brightness of the signal) is detected.
明るさ検波回路35により検出された明るさ信号は、調光回路36に入力され、基準の明るさ(調光の目標値)との差分により調光するための調光信号が生成される。 The brightness signal detected by the brightness detection circuit 35 is input to the dimming circuit 36, and a dimming signal for dimming is generated by the difference from the reference brightness (target value of dimming). この調光回路36からの調光信号は、絞り駆動回路23に入力され、基準となる明るさとなるように絞り22の開口量が調整される。 The dimming signal from the dimming circuit 36 ​​is input to the aperture drive circuit 23, and the opening amount of the aperture 22 is adjusted so as to have a reference brightness. Then, the control circuit 15 controls the CCD drive circuit 31 so as to appropriately drive the identified CCD 29 of the endoscope 2. Then, the control circuit 15 controls the CCD drive circuit 31 so as to appropriately drive the identified CCD 29 of the endoscope 2.
The CCD 29 receives the CCD drive signal from the CCD drive circuit 31 and inputs the photoelectrically converted imaging signal to a correlated double sampling circuit (abbreviated as CDS circuit) 32. A signal component is extracted from the imaging signal by the CDS circuit 32 and converted into a baseband signal, which is then input to the A / D conversion circuit 34, converted into a digital signal, and input to the brightness detection circuit 35. , Brightness (average luminance of the signal) is detected. The CCD 29 receives the CCD drive signal from the CCD drive circuit 31 and inputs the photoelectrically converted imaging signal to a correlated double sampling circuit (abbreviated as CDS circuit) 32. A signal component is extracted from the imaging signal by the CDS circuit 32 and converted into a baseband signal, which is then input to the A / D conversion circuit 34, converted into a digital signal, and input to the brightness detection circuit 35., Brightness (average luminance of the signal) is detected.
The brightness signal detected by the brightness detection circuit 35 is input to the dimming circuit 36, and a dimming signal for dimming is generated based on the difference from the reference brightness (target dimming value). The dimming signal from the dimming circuit 36 is input to the aperture driving circuit 23, and the aperture amount of the aperture 22 is adjusted so that the reference brightness is obtained. The brightness signal detected by the brightness detection circuit 35 is input to the dimming circuit 36, and a dimming signal for dimming is generated based on the difference from the reference brightness (target dimming value). The dimming signal from the dimming circuit 36 ​​is input to the aperture driving circuit 23, and the aperture amount of the aperture 22 is adjusted so that the reference brightness is obtained.

A/D変換回路34から出力されるデジタル信号は、Y/C分離回路37に入力され、輝度信号Yと(広義の色信号Cとしての)線順次の色差信号Cr(=2R−G),Cb(=2B−G)が生成される。輝度信号Yは、γ回路38を介してセレクタ39に入力される(この輝度信号をYhと記す)と共に、信号の通過帯域を制限する第1のローパスフィルタ(LPFと略記)41に入力される。
このLPF41は、輝度信号Yに対応して広い通過帯域に設定されており、このLPF41の通過帯域特性により設定された帯域の輝度信号Ylが、第1マトリクス回路42に入力される。
また、色差信号Cr,Cbは、信号の通過帯域を制限する第2のLPF43を介して(線順次)同時化回路44に入力される。 Further, the color difference signals Cr and Cb are input to the simultaneous circuit 44 (line sequential) via the second LPF 43 that limits the pass band of the signal.
この場合、第2のLPF43は、制御回路15により、観察モードに応じてその通過帯域特性が変更される。 In this case, the pass band characteristic of the second LPF 43 is changed by the control circuit 15 according to the observation mode. 具体的には、通常光観察モード時には、第2のLPF43は、第1のLPF 41より低帯域に設定される。 Specifically, in the normal light observation mode, the second LPF 43 is set to a lower band than the first LPF 41 . The digital signal output from the A / D conversion circuit 34 is input to the Y / C separation circuit 37, and the luminance signal Y and the line-sequential color difference signal Cr (= 2R-G) (as the color signal C in a broad sense), Cb (= 2B-G) is generated. The luminance signal Y is input to the selector 39 via the γ circuit 38 (this luminance signal is referred to as Yh), and is also input to a first low-pass filter (abbreviated as LPF) 41 that limits the passband of the signal. . The digital signal output from the A / D conversion circuit 34 is input to the Y / C separation circuit 37, and the luminance signal Y and the line-sequential color difference signal Cr (= 2R-G) (as the color signal C in) a broad sense), Cb (= 2B-G) is generated. The luminance signal Y is input to the selector 39 via the γ circuit 38 (this luminance signal is referred to as Yh), and is also input to a first low- pass filter (abbreviated as LPF) 41 that limits the passband of the signal.
The LPF 41 is set to have a wide pass band corresponding to the luminance signal Y, and the luminance signal Y 1 in the band set by the pass band characteristic of the LPF 41 is input to the first matrix circuit 42. The LPF 41 is set to have a wide pass band corresponding to the luminance signal Y, and the luminance signal Y 1 in the band set by the pass band characteristic of the LPF 41 is input to the first matrix circuit 42.
Further, the color difference signals Cr and Cb are input to the synchronization circuit 44 (line-sequentially) through the second LPF 43 that limits the pass band of the signal. Further, the color difference signals Cr and Cb are input to the synchronization circuit 44 (line-sequentially) through the second LPF 43 that limits the pass band of the signal.
In this case, the passband characteristic of the second LPF 43 is changed by the control circuit 15 according to the observation mode. Specifically, in the normal light observation mode, the second LPF 43 is set to a lower band than the first LPF 41 . In this case, the passband characteristic of the second LPF 43 is changed by the control circuit 15 according to the observation mode. Specifically, in the normal light observation mode, the second LPF 43 is set to a lower band than the first LPF 41 .

一方、狭帯域光観察モード時には、第2のLPF43は、通常光観察モード時における低帯域よりも広い帯域に変更される。例えば第2のLPF43は、第1のLPF41とほぼ同様に広帯域に設定(変更)される。このように第2のLPF43は、観察モードの切替に連動して、色差信号Cr,Cbに対する通過帯域制限する処理特性を変更する処理特性変更手段を形成している。
同時化回路44は、同時化された色差信号Cr,Cbを生成し、この色差信号Cr,Cbは、第1マトリクス回路42に入力される。
第1マトリクス回路42は、輝度信号Y及び色差信号Cr,Cbから3原色信号R,G,Bに変換して、γ回路45に出力する。
また、この第1マトリクス回路42は、制御回路15によって制御され、CCD29の色分離フィルタ30の特性や狭帯域用フィルタ24の特性に応じて(変換特性を決定する)マトリクス係数の値を変更して、混色の無い或いは混色を殆ど解消した3原色信号R1,G1,B1に変換する。 Further, the first matrix circuit 42 is controlled by the control circuit 15 and changes the value of the matrix coefficient (which determines the conversion characteristic) according to the characteristics of the color separation filter 30 of the CCD 29 and the characteristics of the narrow band filter 24. Then, it is converted into three primary color signals R1, G1 and B1 with no color mixing or almost no color mixing. On the other hand, in the narrow band light observation mode, the second LPF 43 is changed to a wider band than the low band in the normal light observation mode. For example, the second LPF 43 is set (changed) in a wide band almost like the first LPF 41. As described above, the second LPF 43 forms processing characteristic changing means for changing the processing characteristic for limiting the pass band for the color difference signals Cr and Cb in conjunction with the switching of the observation mode. On the other hand, in the narrow band light observation mode, the second LPF 43 is changed to a wider band than the low band in the normal light observation mode. For example, the second LPF 43 is set (changed) in a wide band almost like the first LPF 41. As described above, the second LPF 43 forms processing characteristic changing means for changing the processing characteristic for limiting the pass band for the color difference signals Cr and Cb in conjunction with the switching of the observation mode.
The synchronization circuit 44 generates synchronized color difference signals Cr and Cb, and the color difference signals Cr and Cb are input to the first matrix circuit 42. The synchronization circuit 44 generates synchronized color difference signals Cr and Cb, and the color difference signals Cr and Cb are input to the first matrix circuit 42.
The first matrix circuit 42 converts the luminance signal Y and the color difference signals Cr, Cb into the three primary color signals R, G, B, and outputs them to the γ circuit 45. The first matrix circuit 42 converts the luminance signal Y and the color difference signals Cr, Cb into the three primary color signals R, G, B, and outputs them to the γ circuit 45.
The first matrix circuit 42 is controlled by the control circuit 15 to change the matrix coefficient value (determining the conversion characteristics) according to the characteristics of the color separation filter 30 of the CCD 29 and the characteristics of the narrowband filter 24. Thus, the signals are converted into three primary color signals R1, G1, and B1 with no color mixture or almost no color mixture. The first matrix circuit 42 is controlled by the control circuit 15 to change the matrix coefficient value (determining the conversion characteristics) according to the characteristics of the color separation filter 30 of the CCD 29 and the characteristics of the narrowband filter 24. Thus, the signals are converted into three primary color signals R1, G1, and B1 with no color mixture or almost no color mixture.

例えば、ビデオプロセッサ4に実際に接続される内視鏡2により、その内視鏡2に搭載されているCCD29の色分離フィルタ30の特性が異なる場合があり、制御回路15は、IDの情報により実際に使用されているCCD29の色分離フィルタ30の特性に応じて第1マトリクス回路42の係数を変更する。このようにすることにより、実際に使用される撮像手段の種類が異なる場合にも適切に対応でき、偽色の発生を防止したり、混色の無い3原色信号R1,G1,B1に変換することができる。
なお、混色の無い3原色信号R1,G1,B1を生成することにより、特に狭帯域光観察モード時において、特定の色の狭帯域光の下で撮像した色信号が他の色の狭帯域光の下で撮像した色信号のために識別がしにくくなってしまうことを有効に防止できる作用効果を持つ。 By generating the three primary color signals R1, G1 and B1 without color mixing, the color signal imaged under the narrow band light of a specific color is the narrow band light of another color, especially in the narrow band light observation mode. It has the effect of effectively preventing the color signal imaged underneath from becoming difficult to identify. For example, the characteristics of the color separation filter 30 of the CCD 29 mounted on the endoscope 2 may differ depending on the endoscope 2 that is actually connected to the video processor 4. The coefficient of the first matrix circuit 42 is changed according to the characteristics of the color separation filter 30 of the CCD 29 that is actually used. By doing so, it is possible to appropriately cope with different types of imaging means that are actually used, preventing the generation of false colors, or converting the signals to the three primary color signals R1, G1, and B1 having no color mixture. Can do. For example, the characteristics of the color separation filter 30 of the CCD 29 mounted on the endoscope 2 may differ depending on the endoscope 2 that is actually connected to the video processor 4. The coefficient of the first matrix circuit 42 is changed according to the Characteristics of the color separation filter 30 of the CCD 29 that is actually used. By doing so, it is possible to appropriately cope with different types of imaging means that are actually used, preventing the generation of false colors, or converting the signals to the three primary color signals R1, G1, and B1 having no color mixture. Can do.
In addition, by generating the three primary color signals R1, G1, and B1 having no color mixture, particularly in the narrowband light observation mode, the color signal captured under the narrowband light of a specific color is a narrowband light of another color. It is possible to effectively prevent the color signal picked up below from being difficult to identify. In addition, by generating the three primary color signals R1, G1, and B1 having no color mixture, particularly in the narrowband light observation mode, the color signal captured under the narrowband light of a specific color is a narrowband light of another color. is possible to effectively prevent the color signal picked up below from being difficult to identify.

つまり、図10に示す従来例においては、R,G,Bの各波長帯域中にそれぞれ設定された各狭帯域光のもとで撮像された複数の画像成分が混色してしまい、注目する特定の狭帯域光に対応する画像成分の特徴が不明瞭になってしまう欠点があったが、本実施例ではこのように不明瞭にする原因となる混色を防止できる。
また、この混色を防止することにより、その後段側において、注目する特定の狭帯域光に対応する画像成分の比率を大きくして表示したり、注目する特定の狭帯域光に対応する画像成分のみを用いて表示することもできるようになり、注目する特定の狭帯域光に対応する画像成分の特徴を明瞭に反映する画像表示を行うこともできる。 In addition, by preventing this color mixing, the ratio of the image component corresponding to the specific narrow band light of interest is increased and displayed on the subsequent stage side, or only the image component corresponding to the specific narrow band light of interest is displayed. It is also possible to display using the image, and it is also possible to display an image that clearly reflects the characteristics of the image component corresponding to the specific narrow-band light of interest. That is, in the conventional example shown in FIG. 10, a plurality of image components picked up under each narrowband light set in each of the R, G, and B wavelength bands are mixed, and the specific identification of interest However, in this embodiment, it is possible to prevent color mixing that causes such ambiguity. That is, in the conventional example shown in FIG. 10, a plurality of image components picked up under each narrowband light set in each of the R, G, and B wavelength bands are mixed, and the specific identification of interest However, in this embodiment, it is possible to prevent color mixing that causes such ambiguity.
In addition, by preventing this color mixture, on the subsequent stage side, the ratio of the image component corresponding to the specific narrow band light of interest is increased, or only the image component corresponding to the specific narrow band light of interest is displayed. It is also possible to perform display using the image, and it is also possible to perform image display that clearly reflects the characteristics of the image component corresponding to the specific narrow band light of interest. In addition, by preventing this color mixture, on the subsequent stage side, the ratio of the image component corresponding to the specific narrow band light of interest is increased, or only the image component corresponding to the specific narrow band light of interest is displayed. It is also possible to perform display using the image, and it is also possible to perform image display that clearly reflects the characteristics of the image component corresponding to the specific narrow band light of interest.

γ回路45も、制御回路15により制御される。具体的には、狭帯域光観察モード時には、通常光観察モード時よりもγ補正の特性を強調したγ特性に変更される。これにより、低信号レベル側でのコントラストが強調され、より識別し易い表示特性となる。このγ回路45によりγ補正された3原色信号R2,G2,B2は、第2マトリクス回路46に入力され、この第2マトリクス回路46により、輝度信号Yと、色差信号R−Y、B−Yに変換される。
この場合、制御回路15は、通常光観察モード時には、3原色信号R2,G2,B2から輝度信号Yと、色差信号R−Y、B−Yに単に変換するように第2マトリクス回路46のマトリクス係数を設定する。
制御回路15は、狭帯域光観察モード時には、第2マトリクス回路46のマトリクス係数を通常光観察モード時の値から変更して、3原色信号R2,G2,B2から特にB信号に対する比率(重み付け)を大きくした輝度信号Ynbi及び色差信号R−Y、B−Yが生成されるようにする。 In the narrow band light observation mode, the control circuit 15 changes the matrix coefficient of the second matrix circuit 46 from the value in the normal light observation mode, and the ratio (weighting) from the three primary color signals R2, G2, B2 to the B signal in particular. The luminance signal Ynbi and the color difference signals RY and BY are increased so as to be generated. The γ circuit 45 is also controlled by the control circuit 15. Specifically, in the narrow-band light observation mode, the γ characteristic is changed to emphasize the γ correction characteristic than in the normal light observation mode. As a result, the contrast on the low signal level side is enhanced, and the display characteristics are more easily identified. The three primary color signals R2, G2, and B2 that have been γ-corrected by the γ circuit 45 are input to the second matrix circuit 46, and by the second matrix circuit 46, the luminance signal Y and the color difference signals RY and BY are obtained. Is converted to The γ circuit 45 is also controlled by the control circuit 15. Specifically, in the narrow-band light observation mode, the γ characteristic is changed to emphasize the γ correction characteristic than in the normal light observation mode. As a result, the contrast on The low signal level side is enhanced, and the display characteristics are more easily identified. The three primary color signals R2, G2, and B2 that have been γ-corrected by the γ circuit 45 are input to the second matrix circuit 46, and by the second matrix circuit 46, the luminance signal Y and the color difference signals RY and BY are obtained. Is converted to
In this case, in the normal light observation mode, the control circuit 15 matrixes the second matrix circuit 46 so as to simply convert the three primary color signals R2, G2, and B2 into the luminance signal Y and the color difference signals RY and BY. Set the coefficient. In this case, in the normal light observation mode, the control circuit 15 matrixes the second matrix circuit 46 so as to simply convert the three primary color signals R2, G2, and B2 into the luminance signal Y and the color difference signals RY and BY . Set the coefficient.
In the narrow-band light observation mode, the control circuit 15 changes the matrix coefficient of the second matrix circuit 46 from the value in the normal light observation mode, and the ratio (weighting) from the three primary color signals R2, G2, B2 to the B signal in particular. The luminance signal Ynbi and the color difference signals RY and BY are generated. In the narrow-band light observation mode, the control circuit 15 changes the matrix coefficient of the second matrix circuit 46 from the value in the normal light observation mode, and the ratio (weighting) from the three primary color signals R2, G2, B2 to the B signal in particular. The luminance signal Ynbi and the color difference signals RY and BY are generated.

この場合における変換式は、3行3列のマトリクスA、Kを用いると、以下のようになる。
The conversion formula in this case is as follows using the matrix A and K of 3 rows and 3 columns.
この場合における変換式は、3行3列のマトリクスA、Kを用いると、以下のようになる。
The conversion formula in this case is as follows using the matrix A and K of 3 rows and 3 columns.
この場合における変換式は、3行3列のマトリクスA、Kを用いると、以下のようになる。
The conversion formula in this case is as follows using the matrix A and K of 3 rows and 3 columns.
この場合における変換式は、3行3列のマトリクスA、Kを用いると、以下のようになる。
The conversion formula in this case is as follows using the matrix A and K of 3 rows and 3 columns.

ここで、Kは、例えば3個の実数成分k1〜k3(その他の成分は0)からなり、この式(1)ような変換式により、Rの色信号に対して、G,Bの色信号の重み付けが大きく、特にBの色信号の重み付け(比率)が最大となっている。換言すると、長波長となるRの色信号を抑圧し、短波長側のBの色信号を強調している。
又、Aは、RGB信号からY色差信号に変換する為のマトリクス(行列)であり、以下のような公知の演算係数(2)等が用いられる。
Here, K is composed of, for example, three real number components k1 to k3 (the other components are 0), and the G and B color signals with respect to the R color signal by the conversion formula (1). The weighting (ratio) of the B color signal is particularly maximum. In other words, the R color signal having a long wavelength is suppressed, and the B color signal on the short wavelength side is emphasized. Here, K is composed of, for example, three real number components k1 to k3 (the other components are 0), and the G and B color signals with respect to the R color signal by the conversion formula (1). The weighting ( ratio) of the B color signal is particularly maximum. In other words, the R color signal having a long wavelength is suppressed, and the B color signal on the short wavelength side is emphasized.
A is a matrix for converting RGB signals into Y color difference signals, and the following known calculation coefficient (2) and the like are used. A is a matrix for converting RGB signals into Y color difference signals, and the following known calculation coefficient (2) and the like are used.

第2マトリクス回路46により出力される輝度信号Ynbiは、セレクタ39に入力される。このセレクタ39は、制御回路15により切替が制御される。つまり、通常光観察モード時には輝度信号Yhが選択され、狭帯域光観察モード時には、輝度信号Ynbiが選択される。   The luminance signal Ynbi output from the second matrix circuit 46 is input to the selector 39. Switching of the selector 39 is controlled by the control circuit 15. That is, the luminance signal Yh is selected in the normal light observation mode, and the luminance signal Ynbi is selected in the narrow band light observation mode.

第2マトリクス回路46から出力される色差信号R−Y、B−Yは、セレクタ39を通った輝度信号Yh又はYnbi(Yh/Ynbiと表記)と共に、拡大回路47に入力される。
この拡大回路47により拡大処理された輝度信号Yh/Ynbiは、強調回路48により輪郭強調された後、第3マトリクス回路49に入力され、拡大回路47により拡大処理された色差信号R−Y,B−Yは、強調回路48を通さないで第3マトリクス回路49に入力される。
そして、第3マトリクス回路49により3原色信号R,G,Bに変換された後、図示しないD/A変換回路によりアナログの映像信号に変換されて映像信号出力端からモニタ5に出力される。 Then, after being converted into three primary color signals R, G, B by the third matrix circuit 49, it is converted into an analog video signal by a D / A conversion circuit (not shown) and output to the monitor 5 from the video signal output end. The color difference signals RY and BY output from the second matrix circuit 46 are input to the enlargement circuit 47 together with the luminance signal Yh or Ynbi (denoted as Yh / Ynbi) that has passed through the selector 39. The color difference signals RY and BY output from the second matrix circuit 46 are input to the enlargement circuit 47 together with the luminance signal Yh or Ynbi (denoted as Yh / Ynbi) that has passed through the selector 39.
The luminance signal Yh / Ynbi enlarged by the enlargement circuit 47 is subjected to edge enhancement by the enhancement circuit 48, and then input to the third matrix circuit 49, and the color difference signals RY, B that have been enlarged by the enlargement circuit 47. -Y is input to the third matrix circuit 49 without passing through the emphasis circuit 48. The luminance signal Yh / Ynbi enlarged by the enlargement circuit 47 is subjected to edge enhancement by the enhancement circuit 48, and then input to the third matrix circuit 49, and the color difference signals RY, B that have been enlarged by the enlargement circuit 47 . -Y is input to the third matrix circuit 49 without passing through the emphasis circuit 48.
Then, after being converted into the three primary color signals R, G, and B by the third matrix circuit 49, it is converted into an analog video signal by a D / A conversion circuit (not shown) and outputted to the monitor 5 from the video signal output terminal. Then, after being converted into the three primary color signals R, G, and B by the third matrix circuit 49, it is converted into an analog video signal by a D / A conversion circuit (not shown) and conductive to the monitor 5 from the video signal output terminal.

なお、強調回路48により輪郭強調もCCD29及び色分離フィルタ30等の種類に応じてその強調特性(強調帯域が中低帯域にするか中高帯域にするか)等を変更しても良い。 Note that the emphasis circuit 48 may change the emphasis characteristics (whether the emphasis band is a middle or low band or a middle or high band) according to the type of the CCD 29, the color separation filter 30, and the like.

特に狭帯域光観察モード時には、輝度信号Ynbiが強調処理されることになる。この場合、式(1)を採用した場合には、後述するようにB信号による生体表層付近の毛細血管等の構造を強調した処理を行うことになり、注目する画像成分を明瞭に表示できるようになる。
なお、映像信号出力端からモニタ5のR,G,Bの各チャンネルに実際に入力される3原色信号R,G,Bは、狭帯域光観察モード時には、式(1)を採用した場合、G,B,Bの信号(重み付けは係数により異なるが)となり、特にB信号による比率が最も大きくなり、B信号による生体表層付近の毛細血管等の構造に対応した内視鏡画像を識別し易い状態で表示することができるようになる。
つまり、狭帯域光観察モード時におけるモニタ5のRGBチャンネルにそれぞれ入力される信号は、実際にはG,B,B信号(係数の値は別として)となる。 That is, the signals input to the RGB channels of the monitor 5 in the narrow band light observation mode are actually G, B, and B signals (apart from the coefficient values). In particular, in the narrow-band light observation mode, the luminance signal Ynbi is enhanced. In this case, when the formula (1) is adopted, as will be described later, the processing of emphasizing structures such as capillaries near the living body surface layer by the B signal is performed, so that the image component of interest can be clearly displayed. become. In particular, in the narrow-band light observation mode, the luminance signal Ynbi is enhanced. In this case, when the formula (1) is adopted, as will be described later, the processing of emphasizing structures such as capillaries near the living body surface layer by the B signal is performed, so that the image component of interest can be clearly displayed. Become.
Note that the three primary color signals R, G, and B that are actually input from the video signal output terminal to the R, G, and B channels of the monitor 5 are in the narrow-band light observation mode, when the formula (1) is adopted, G, B, and B signals (weighting varies depending on the coefficient), especially the ratio due to the B signal is the largest, and it is easy to identify an endoscopic image corresponding to a structure such as a capillary vessel near the living body surface by the B signal. It can be displayed in the state. Note that the three primary color signals R, G, and B that are actually input from the video signal output terminal to the R, G, and B channels of the monitor 5 are in the narrow-band light observation mode, when the formula ( 1) is adopted, G, B, and B signals (weighting varies depending on the coefficient), especially the ratio due to the B signal is the largest, and it is easy to identify an endoscopic image corresponding to a structure such as a capillary vessel near the living body surface by the B signal. It can be displayed in the state.
That is, the signals input to the RGB channels of the monitor 5 in the narrow-band light observation mode are actually G, B, and B signals (apart from the coefficient values). That is, the signals input to the RGB channels of the monitor 5 in the narrow-band light observation mode are actually G, B, and B signals (apart from the coefficient values).

このように本実施例においては、観察モードの切替に連動して、各観察モードに適した信号処理が行えるようにビデオプロセッサ4の信号処理系(より具体的にはY/C分離回路37以降の信号処理系)における処理特性を変更する処理特性変更手段を形成していることが特徴となっている。
この場合、各観察モードに専用の処理回路を設けるのではなく、殆ど共通の処理回路における処理特性を変更することにより、両観察モードに適した処理を行えるようにして、簡単な構成により、両観察モードに適切に対応できるようにしていることが特徴となっている。 In this case, instead of providing a dedicated processing circuit for each observation mode, by changing the processing characteristics in almost the same processing circuit, processing suitable for both observation modes can be performed, and both can be performed with a simple configuration. The feature is that it can appropriately correspond to the observation mode. As described above, in the present embodiment, the signal processing system of the video processor 4 (more specifically, the Y / C separation circuit 37 and later) so that signal processing suitable for each observation mode can be performed in conjunction with switching of the observation mode. The processing characteristic changing means for changing the processing characteristics in the signal processing system) is formed. As described above, in the present embodiment, the signal processing system of the video processor 4 (more specifically, the Y / C separation circuit 37 and later) so that signal processing suitable for each observation mode can be performed in conjunction with switching of the observation mode. The processing characteristic changing means for changing the processing characteristics in the signal processing system) is formed.
In this case, instead of providing a dedicated processing circuit for each observation mode, it is possible to perform processing suitable for both observation modes by changing the processing characteristics in the almost common processing circuit, so that both processes can be performed with a simple configuration. It is characterized by being able to respond appropriately to the observation mode. In this case, instead of providing a dedicated processing circuit for each observation mode, it is possible to perform processing suitable for both observation modes by changing the processing characteristics in the almost common processing circuit, so that both processes can be performed with a simple configuration . It is characterized by being able to respond appropriately to the observation mode.

本実施例による作用を図4を参照して以下に説明する。
術者は、図1に示すように内視鏡2を光源装置3及びビデオプロセッサ4に接続し、電源を投入することにより、ビデオプロセッサ4の制御回路15は、初期設定の処理を開始し、ステップS1に示すように、光源装置3及びビデオプロセッサ4の動作モードとして、例えば通常光観察モードの設定状態にする。 As shown in FIG. 1, the operator connects the endoscope 2 to the light source device 3 and the video processor 4, and turns on the power, so that the control circuit 15 of the video processor 4 starts the initial setting process. As shown in step S1, the operation mode of the light source device 3 and the video processor 4 is set to, for example, a normal light observation mode. The effect | action by a present Example is demonstrated below with reference to FIG. The effect | action by a present Example is demonstrated below with reference to FIG.
The operator connects the endoscope 2 to the light source device 3 and the video processor 4 as shown in FIG. 1 and turns on the power, whereby the control circuit 15 of the video processor 4 starts the initial setting process. As shown in step S1, as the operation mode of the light source device 3 and the video processor 4, for example, the normal light observation mode is set. The operator connects the endoscope 2 to the light source device 3 and the video processor 4 as shown in FIG. 1 and turns on the power, particularly the control circuit 15 of the video processor 4 starts the initial setting process. As shown in step S1 , as the operation mode of the light source device 3 and the video processor 4, for example, the normal light observation mode is set.

この状態において、光源装置3は、図1の実線で示すように狭帯域用フィルタ24が照明光路から離脱された状態に設定されており、白色照明光のもとで、内視鏡2により撮像を行う状態となる。また、ビデオプロセッサ4側の各部も通常光観察モードの状態で信号処理を行う設定状態になる。
術者は、内視鏡2の挿入部7を患者の体腔内に挿入することにより、内視鏡検査を行うことができる。体腔内における患部等の検査対象組織の表面の血管の走行状態等をより詳しく観察しようと思う場合には、術者は、モード切替スイッチ14を操作する。
ステップS2に示すように制御回路15は、モード切替スイッチ14が操作されたか否かをモニタし、モード切替スイッチ14が操作されていない場合には、その状態を維持し、モード切替スイッチ14が操作された場合には、次のステップS3に進む。 As shown in step S2, the control circuit 15 monitors whether or not the mode changeover switch 14 has been operated, and if the mode changeover switch 14 is not operated, maintains that state and the mode changeover switch 14 operates. If so, the process proceeds to the next step S3. In this state, the light source device 3 is set in a state in which the narrowband filter 24 is detached from the illumination optical path as shown by the solid line in FIG. 1 and is imaged by the endoscope 2 under white illumination light. It will be in the state to perform. In addition, each unit on the video processor 4 side is also set to perform signal processing in the normal light observation mode. In this state, the light source device 3 is set in a state in which the narrowband filter 24 is detached from the illumination optical path as shown by the solid line in FIG. 1 and is imaged by the spectrometer 2 under white illumination light. Will be in the state to perform. In addition, each unit on the video processor 4 side is also set to perform signal processing in the normal light observation mode.
The surgeon can perform an endoscopic examination by inserting the insertion portion 7 of the endoscope 2 into the body cavity of the patient. When the operator wants to observe in more detail the running state of the blood vessels on the surface of the tissue to be examined such as the affected part in the body cavity, the operator operates the mode switch 14. The surgeon can perform an endoscopic examination by inserting the insertion portion 7 of the endoscope 2 into the body cavity of the patient. When the operator wants to observe in more detail the running state of the blood vessels on the surface of the tissue to be examined. such as the affected part in the body cavity, the operator operates the mode switch 14.
As shown in step S2, the control circuit 15 monitors whether or not the mode change switch 14 has been operated. If the mode change switch 14 has not been operated, the control circuit 15 maintains that state, and the mode change switch 14 has been operated. If so, the process proceeds to the next step S3. As shown in step S2, the control circuit 15 monitors whether or not the mode change switch 14 has been operated. If the mode change switch 14 has not been operated, the control circuit 15 maintains that state, and the mode change switch 14 has been operated. If so, the process proceeds to the next step S3.

ステップS3においては、制御回路15は、光源装置3及びビデオプロセッサ4の動作モードを狭帯域光観察モードの設定状態に変更する。
具体的には、制御回路15は、光源装置3に対しては、図1における2点鎖線で示すように狭帯域用フィルタ24を照明光路中に配置するように制御する。 Specifically, the control circuit 15 controls the light source device 3 so that the narrow band filter 24 is arranged in the illumination optical path as shown by the alternate long and short dash line in FIG. 図2にその透過特性を示すように狭帯域用フィルタ24が照明光路中に配置されることにより、狭帯域透過フィルタ特性部Ra,Ga,Baによる狭帯域照明光により、照明が行われる。 By arranging the narrow band filter 24 in the illumination optical path as shown in FIG. 2 as its transmission characteristic, illumination is performed by the narrow band illumination light by the narrow band transmission filter characteristic units Ra, Ga, and Ba.
また、制御回路15は、ビデオプロセッサ4における各部の設定を変更する、具体的には、制御回路15は、LPF43の帯域特性を広帯域化し、第1マトリクス回路42のマトリクス係数を混色が発生しないように変更し、γ回路45のγ特性を変更し、第2マトリクス回路46のマトリクス係数を特に(狭帯域透過フィルタ特性部Baによる)色信号Bによる信号成分の比率が大きくなるように変更し、またセレクタ39を輝度信号Ynbiが選択されるように切り替える等の変更設定を行う。 Further, the control circuit 15 changes the settings of each part in the video processor 4. Specifically, the control circuit 15 widens the band characteristics of the LPF 43 so that the matrix coefficients of the first matrix circuit 42 are not mixed. , The γ characteristic of the γ circuit 45 is changed, and the matrix coefficient of the second matrix circuit 46 is changed so that the ratio of the signal component due to the color signal B (by the narrow band transmission filter characteristic unit Ba) becomes large. Further, change settings such as switching the selector 39 so that the brightness signal Ynbi is selected are performed. In step S3, the control circuit 15 changes the operation mode of the light source device 3 and the video processor 4 to the setting state of the narrowband light observation mode. In step S3, the control circuit 15 changes the operation mode of the light source device 3 and the video processor 4 to the setting state of the narrowband light observation mode.
Specifically, the control circuit 15 controls the light source device 3 so that the narrowband filter 24 is arranged in the illumination optical path as indicated by a two-dot chain line in FIG. As shown in FIG. 2, the narrow band filter 24 is arranged in the illumination optical path so that illumination is performed by the narrow band illumination light by the narrow band transmission filter characteristic portions Ra, Ga, Ba. Specifically, the control circuit 15 controls the light source device 3 so that the narrowband filter 24 is arranged in the illumination optical path as indicated by a two-dot chain line in FIG. As shown in FIG. 2, the narrow band filter 24 is arranged in the illumination optical path so that illumination is performed by the narrow band illumination light by the narrow band transmission filter characteristic portions Ra, Ga, Ba.
Further, the control circuit 15 changes the setting of each unit in the video processor 4. Specifically, the control circuit 15 widens the band characteristic of the LPF 43 so that color mixing does not occur in the matrix coefficient of the first matrix circuit 42. And the γ characteristic of the γ circuit 45 is changed, and the matrix coefficient of the second matrix circuit 46 is changed in particular so that the ratio of the signal component by the color signal B (by the narrowband transmission filter characteristic unit Ba) becomes large, Further, change setting such as switching the selector 39 so that the luminance signal Ynbi is selected is performed. Further, the control circuit 15 changes the setting of each unit in the video processor 4. Specifically, the control circuit 15 widens the band characteristic of the LPF 43 so that color mixing does not occur in the matrix coefficient of the first matrix circuit 42. And the γ characteristic of the γ circuit 45 is changed, and the matrix coefficient of the second matrix circuit 46 is changed in particular so that the ratio of the signal component by the color signal B (by the narrowband transmission filter characteristic unit Ba) becomes large, Further, change setting such as switching the selector 39 so that the luminance signal Ynbi is selected is performed.

このような変更設定を行うことにより、狭帯域光観察モードにおいて、例えば第2マトリクス回路46のマトリクス係数を特にBの色信号による信号成分の比率が大きくなる処理特性に変更されるので、狭帯域透過フィルタ特性部BaによるBの照明光のもとで撮像したBの色信号により得られる生体組織の表層付近における毛細血管の走行状態を識別し易い状態で表示することができる。
また、LPF43の信号通過の帯域特性を広帯域化しているので、毛細血管の走行状態や、狭帯域透過フィルタ特性部Gaによる輝度信号に近いGの照明光のもとで撮像したGの色信号により得られる表層付近に近い血管走行状態などの分解能(解像度)を向上することができ、診断がし易い画質の良い画像が得られる。 Further, since the band characteristic of the signal passage of the LPF43 is widened, the G color signal imaged under the illumination light of G close to the luminance signal by the traveling state of the capillaries and the narrow band transmission filter characteristic unit Ga is used. It is possible to improve the resolution of the obtained blood vessel running state near the surface layer, and it is possible to obtain an image with good image quality that is easy to diagnose.
次のステップS4において、制御回路15は、モード切替スイッチ14が操作されたか否かをモニタし、モード切替スイッチ14が操作されていない場合には、その状態を維持し、モード切替スイッチ14が操作された場合には、次のステップS1に戻ることになる。 In the next step S4, the control circuit 15 monitors whether or not the mode changeover switch 14 is operated, and if the mode changeover switch 14 is not operated, maintains that state and the mode changeover switch 14 operates. If so, the process returns to the next step S1. By performing such a change setting, for example, in the narrowband light observation mode, for example, the matrix coefficient of the second matrix circuit 46 is changed to a processing characteristic that particularly increases the ratio of the signal component by the B color signal. It is possible to display in a state where the running state of capillaries in the vicinity of the surface layer of the biological tissue obtained from the B color signal imaged under the B illumination light by the transmission filter characteristic unit Ba can be easily identified. By performing such a change setting, for example, in the narrowband light observation mode, for example, the matrix coefficient of the second matrix circuit 46 is changed to a processing characteristic that particularly increases the ratio of the signal component by the B color signal. It is possible to display in a state where the running state of capillaries in the vicinity of the surface layer of the biological tissue obtained from the B color signal imaged under the B illumination light by the transmission filter characteristic unit Ba can be easily identified.
In addition, since the band characteristics of the signal passage of the LPF 43 are widened, the traveling state of the capillaries and the G color signal imaged under the G illumination light close to the luminance signal by the narrow band transmission filter characteristic unit Ga. The resolution (resolution) of the blood vessel running state near the surface layer obtained can be improved, and an image with good image quality that is easy to diagnose can be obtained. In addition, since the band characteristics of the signal passage of the LPF 43 are widened, the traveling state of the capillaries and the G color signal imaged under the G illumination light close to the luminance signal by the narrow band transmission filter characteristic unit Ga. The resolution (resolution) of the blood vessel running state near the surface layer obtained can be improved, and an image with good image quality that is easy to diagnose can be obtained.
In the next step S4, the control circuit 15 monitors whether or not the mode change switch 14 has been operated. If the mode change switch 14 has not been operated, the control circuit 15 maintains that state, and the mode change switch 14 has been operated. If so, the process returns to the next step S1. In the next step S4, the control circuit 15 monitors whether or not the mode change switch 14 has been operated. If the mode change switch 14 has not been operated, the control circuit 15 maintains that state, and the mode change switch 14 has been operated. If so, the process returns to the next step S1.

このように動作する本実施例によれば、通常光観察モードにおいて、既存の同時式によるカラー撮像機能を保持し、かつ狭帯域光観察モードにおいてもビデオプロセッサ4内の各部の係数等の設定を変更する等の処理特性を変更することにより、狭帯域光観察モードによる観察機能を十分に確保することができる。
つまり、従来例における解像度の低下を防止して、解像度の良好な内視鏡画像が得られると共に、(従来例では例えばRの狭帯域照明光のもとで撮像した信号のために埋もれ易くなってしまっていた)Bの狭帯域照明光のもとで撮像した毛細血管の走行状態をより明瞭に識別し易い状態で表示することができる。
また、本実施例によれば、信号処理系における一部の処理特性を切り替えることにより、通常光観察モードと狭帯域光観察モードとの両方に簡単に対応できるので、内視鏡検査の際に非常に便利かつ有用な装置となる。 Further, according to this embodiment, by switching a part of the processing characteristics in the signal processing system, both the normal light observation mode and the narrow band light observation mode can be easily supported, so that the endoscopy can be performed. It will be a very convenient and useful device. According to this embodiment that operates in this way, the existing simultaneous color imaging function is maintained in the normal light observation mode, and the coefficient of each part in the video processor 4 is set even in the narrowband light observation mode. By changing the processing characteristics such as changing, it is possible to sufficiently secure the observation function in the narrow-band light observation mode. According to this embodiment that operates in this way, the existing simultaneous color imaging function is maintained in the normal light observation mode, and the coefficient of each part in the video processor 4 is set even in the narrowband light observation mode. By changing the processing characteristics such as changing, it is possible to sufficiently secure the observation function in the narrow-band light observation mode.
In other words, it is possible to prevent a decrease in resolution in the conventional example and obtain an endoscopic image with a good resolution, and (in the conventional example, it is easy to be buried due to a signal imaged under R narrow-band illumination light, for example). It is possible to display the running state of the capillaries imaged under the narrow-band illumination light B) in a state where it is easier to identify clearly. In other words, it is possible to prevent a decrease in resolution in the conventional example and obtain an endoscopic image with a good resolution, and (in the conventional example, it is easy to be buried due to a signal imaged under R narrow-band illumination light, for example). It is possible to display the running state of the capillaries imaged under the narrow-band illumination light B) in a state where it is easier to identify clearly.
In addition, according to the present embodiment, by switching some processing characteristics in the signal processing system, it is possible to easily cope with both the normal light observation mode and the narrow band light observation mode. It becomes a very convenient and useful device. In addition, according to the present embodiment, by switching some processing characteristics in the signal processing system, it is possible to easily cope with both the normal light observation mode and the narrow band light observation mode. It becomes a very convenient and useful device.

また、光源装置3においても、通常光の照明手段の他に、狭帯域用フィルタ24を光路中に挿脱する手段を設けることにより、簡単に狭帯域光の光源装置を形成できる。
次に第1変形例を説明する。実施例1において、第1マトリクス回路42による演算を以下のように行うことにより、乗算処理を低減できるようにしたものである。
上述した第1マトリクス回路42は、入力される輝度信号Y及び色差信号Cr,Cbから3原色信号R1,G1,B1を生成していた。
この場合、第1マトリクス回路42によるマトリクス演算式は、3行3列のマトリクスM(マトリクス係数m11〜m33)を用いて、一般的には以下のようになる。
Also in the light source device 3, a narrow band light source device can be easily formed by providing means for inserting / removing the narrow band filter 24 in / from the optical path in addition to the normal light illumination means. Also in the light source device 3, a narrow band light source device can be easily formed by providing means for inserting / removing the narrow band filter 24 in / from the optical path in addition to the normal light illumination means.
Next, a first modification will be described. In the first embodiment, the multiplication process can be reduced by performing the calculation by the first matrix circuit 42 as follows. Next, a first modification will be described. In the first embodiment, the multiplication process can be reduced by performing the calculation by the first matrix circuit 42 as follows.
The first matrix circuit 42 described above generates the three primary color signals R1, G1, and B1 from the input luminance signal Y and color difference signals Cr and Cb. The first matrix circuit 42 described above generates the three primary color signals R1, G1, and B1 from the input luminance signal Y and color difference signals Cr and Cb.
In this case, the matrix calculation expression by the first matrix circuit 42 is generally as follows using a matrix M (matrix coefficients m11 to m33) of 3 rows and 3 columns. In this case, the matrix calculation expression by the first matrix circuit 42 is generally as follows using a matrix M (matrix coefficients m11 to m33) of 3 rows and 3 columns.

一方、第1マトリクス回路42に入力される輝度信号Y及び色差信号Cr,Cbは、図5にその概略を示すような特性となる。 On the other hand, the luminance signal Y and the color difference signals Cr and Cb input to the first matrix circuit 42 have characteristics as schematically shown in FIG.

上記式(3)の演算を行う場合、図5におけるR,G,Bの各帯域に対する輝度信号Y,色差信号Cr,Cbの寄与の比率(割合)を考慮すると、以下のように近似できる。図5におけるRの帯域における色差信号Cbが寄与する比率は、他のものに比較して十分に小さく0と近似できる。
つまり、上記係数m13を0と近似できる。 That is, the coefficient m13 can be approximated to 0. また、Gの帯域における色差信号Crが寄与する比率は、十分に小さく0と近似できる。 Further, the ratio of the color difference signal Cr contributing in the G band is sufficiently small and can be approximated to 0. つまり、上記係数m22を0と近似できる。 That is, the coefficient m22 can be approximated to 0.
また、Bの帯域における色差信号Crが寄与する比率は、他のものに比較して十分に小さく0と近似できる。 Further, the ratio of the color difference signal Cr contributing in the band B is sufficiently smaller than that of other signals and can be approximated to 0. つまり、上記係数m32を0と近似できる。 That is, the coefficient m32 can be approximated to 0.
従って、上記マトリクスMとして、以下のものを採用することができる。 Therefore, the following can be adopted as the matrix M.
When the calculation of the above equation (3) is performed, considering the ratio (ratio) of the contribution of the luminance signal Y and the color difference signals Cr and Cb to the R, G, and B bands in FIG. The ratio contributed by the color difference signal Cb in the R band in FIG. 5 is sufficiently small compared to the other and can be approximated to zero. When the calculation of the above equation (3) is performed, considering the ratio (ratio) of the contribution of the luminance signal Y and the color difference signals Cr and Cb to the R, G, and B bands in FIG. The ratio contributed by the color difference signal Cb in the R band in FIG. 5 is sufficiently small compared to the other and can be approximated to zero.
That is, the coefficient m13 can be approximated to zero. Further, the ratio contributed by the color difference signal Cr in the G band is sufficiently small and can be approximated to zero. That is, the coefficient m22 can be approximated to zero. That is, the coefficient m13 can be approximated to zero. Further, the ratio contributed by the color difference signal Cr in the G band is sufficiently small and can be approximated to zero. That is, the coefficient m22 can be approximated to zero.
Further, the ratio contributed by the color difference signal Cr in the B band is sufficiently small compared to the other, and can be approximated to zero. That is, the coefficient m32 can be approximated to zero. Further, the ratio contributed by the color difference signal Cr in the B band is sufficiently small compared to the other, and can be approximated to zero. That is, the coefficient m32 can be approximated to zero.
Therefore, the following can be adopted as the matrix M. Therefore, the following can be adopted as the matrix M.

このマトリクスMの係数を、図6(A)に示している。また、図5の特性からこのマトリクスMの係数を、図6(B)、図6(C)、図6(D)のように近似しても良い。このように近似することにより、第1マトリクス回路42による乗算器の構成をより削減或いは単純化でき、高速処理や低コスト化が可能となる。
次に第2変形例を説明する。上述の説明では、狭帯域用フィルタ24は3峰性のフィルタを採用していたが、以下のように2峰性のものを採用しても良い。
第2変形例における狭帯域用フィルタ24Bとして、図7に示すような透過特性のものを採用しても良い。 As the narrow band filter 24B in the second modification, a filter having transmission characteristics as shown in FIG. 7 may be adopted. この狭帯域用フィルタ24Bは、2峰性フィルタであり、GとBの波長域にそれぞれ狭帯域透過フィルタ特性部Ga,Baを有する。 This narrow band filter 24B is a bimodal filter, and has narrow band transmission filter characteristic units Ga and Ba in the wavelength regions of G and B, respectively. つまり、実施例1における3峰性の狭帯域用フィルタ24における狭帯域透過フィルタ特性部Raを設けない特性にしたものである。 That is, the characteristic is such that the narrow band transmission filter characteristic unit Ra is not provided in the trimodal narrow band filter 24 in the first embodiment. The coefficients of this matrix M are shown in FIG. Further, the coefficients of the matrix M may be approximated as shown in FIGS. 6B, 6C, and 6D from the characteristics shown in FIG. By approximating in this way, the configuration of the multiplier by the first matrix circuit 42 can be further reduced or simplified, and high-speed processing and cost reduction are possible. The coefficients of this matrix M are shown in FIG. Further, the coefficients of the matrix M may be approximated as shown in FIGS. 6B, 6C, and 6D from the characteristics shown in FIG. By approximating in this way, the configuration of the multiplier by the first matrix circuit 42 can be further reduced or simplified, and high-speed processing and cost reduction are possible.
Next, a second modification will be described. In the above description, the narrowband filter 24 employs a trimodal filter, but a bimodal filter may be employed as follows. Next, a second modification will be described. In the above description, the narrowband filter 24 employs a trimodal filter, but a bimodal filter may be employed as follows.
As the narrow band filter 24B in the second modification, a filter having transmission characteristics as shown in FIG. 7 may be adopted. This narrow band filter 24B is a bimodal filter, and has narrow band transmission filter characteristic parts Ga and Ba in the G and B wavelength regions, respectively. That is, the narrow band transmission filter characteristic portion Ra in the trimodal narrow band filter 24 in the first embodiment is not provided. As the narrow band filter 24B in the second modification, a filter having transmission characteristics as shown in FIG. 7 may be adopted. This narrow band filter 24B is a bimodal filter, and has narrow band transmission filter characteristic parts Ga and Ba in the G And B wavelength regions, respectively. That is, the narrow band transmission filter characteristic portion Ra in the trimodal narrow band filter 24 in the first embodiment is not provided.

より具体的には、狭帯域透過フィルタ特性部Ga,Baは、それぞれ中心波長が420 nm、540nmであり、その半値幅が20〜40nmのバンドパス特性を有する。
従って、狭帯域用フィルタ24Bが照明光路中に配置された場合には、この狭帯域透過フィルタ特性部Ga,Baを透過した2バンドの狭帯域照明光がライトガイド13に入射される。 Therefore, when the narrow band filter 24B is arranged in the illumination optical path, the two-band narrow band illumination light transmitted through the narrow band transmission filter characteristic portions Ga and Ba is incident on the light guide 13.
この場合における第1マトリクス回路42によるマトリクス演算式は、2行3列のマトリクスMを用いて、一般的には以下のようになる。 In this case, the matrix calculation formula by the first matrix circuit 42 uses the matrix M of 2 rows and 3 columns, and is generally as follows.
More specifically, the narrow-band transmission filter characteristic portions Ga and Ba have bandpass characteristics with center wavelengths of 420 nm and 540 nm, respectively, and a half width of 20 to 40 nm. More specifically, the narrow-band transmission filter characteristic portions Ga and Ba have bandpass characteristics with center wavelengths of 420 nm and 540 nm, respectively, and a half width of 20 to 40 nm.
Accordingly, when the narrow band filter 24B is disposed in the illumination optical path, the two bands of narrow band illumination light that has passed through the narrow band transmission filter characteristic portions Ga and Ba are incident on the light guide 13. Accordingly, when the narrow band filter 24B is disposed in the illumination optical path, the two bands of narrow band illumination light that has passed through the narrow band transmission filter characteristic portions Ga and Ba are incident on the light guide 13.
In this case, the matrix calculation formula by the first matrix circuit 42 is generally as follows using a matrix M of 2 rows and 3 columns. In this case, the matrix calculation formula by the first matrix circuit 42 is generally as follows using a matrix M of 2 rows and 3 columns.

一方、第1マトリクス回路42に入力される輝度信号Y及び色差信号Cr,Cbは、図5に示すような特性を有する。そして、式(4)を導いたのと同様の近似を行うことにより、係数m22とm32を0と近似することができる。
つまり、この場合には、
On the other hand, the luminance signal Y and the color difference signals Cr and Cb input to the first matrix circuit 42 have characteristics as shown in FIG. The coefficients m22 and m32 can be approximated to 0 by performing an approximation similar to that derived from Equation (4).
In this case,
一方、第1マトリクス回路42に入力される輝度信号Y及び色差信号Cr,Cbは、図5に示すような特性を有する。そして、式(4)を導いたのと同様の近似を行うことにより、係数m22とm32を0と近似することができる。
つまり、この場合には、
On the other hand, the luminance signal Y and the color difference signals Cr and Cb input to the first matrix circuit 42 have characteristics as shown in FIG. The coefficients m22 and m32 can be approximated to 0 by performing an approximation similar to that derived from Equation (4).
In this case,
一方、第1マトリクス回路42に入力される輝度信号Y及び色差信号Cr,Cbは、図5に示すような特性を有する。そして、式(4)を導いたのと同様の近似を行うことにより、係数m22とm32を0と近似することができる。
つまり、この場合には、
On the other hand, the luminance signal Y and the color difference signals Cr and Cb input to the first matrix circuit 42 have characteristics as shown in FIG. The coefficients m22 and m32 can be approximated to 0 by performing an approximation similar to that derived from Equation (4).
In this case,
一方、第1マトリクス回路42に入力される輝度信号Y及び色差信号Cr,Cbは、図5に示すような特性を有する。そして、式(4)を導いたのと同様の近似を行うことにより、係数m22とm32を0と近似することができる。
つまり、この場合には、
On the other hand, the luminance signal Y and the color difference signals Cr and Cb input to the first matrix circuit 42 have characteristics as shown in FIG. The coefficients m22 and m32 can be approximated to 0 by performing an approximation similar to that derived from Equation (4).
In this case,

となる。これを図8(A)に示す。また、他の近似の仕方を行うことにより、図8(B),図8(C)のような係数のマトリクスMを採用することもできる。
このようにマトリクスMの係数の一部を0に近似することにより乗算器の数を削減できる。また、より高速にマトリクス演算処理ができるようなる効果がある。さらに2峰性のフィルタとすることにより、高価な狭帯域用フィルタを低コスト化することもできる。
It becomes. This is shown in FIG. Further, by performing other approximation methods, a matrix M of coefficients as shown in FIGS. 8B and 8C can be adopted.
Thus, by approximating some of the coefficients of the matrix M to 0, the number of multipliers can be reduced. Further, there is an effect that matrix calculation processing can be performed at higher speed. Furthermore, by using a bimodal filter, it is possible to reduce the cost of an expensive narrow band filter. Thus, by approximating some of the coefficients of the matrix M to 0, the number of multipliers can be reduced. Further, there is an effect that matrix calculation processing can be performed at higher speed. Further, by using a bimodal filter, it is possible to reduce the cost of an expensive narrow band filter.

次に本発明の第2実施例を図9を参照して説明する。図9は、本発明の第2実施例を備えた内視鏡装置1Bを示す。
この内視鏡装置1Bは、図1のビデオプロセッサ4の一部を変更したビデオプロセッサ4Bを採用した構成である。このビデオプロセッサ4Bは、図1のビデオプロセッサ4において、第1マトリクス回路42、γ回路45,第2マトリクス回路46を1つのマトリクス回路51により構成している。

そして、制御回路15は、実施例1において説明したようにモード切替スイッチ14による切替信号によりγ回路45のγ特性及び第2マトリクス回路46のマトリクス係数の変更を行うのと同様にマトリクス回路51のマトリクス係数の変更等を行う。 Then, as described in the first embodiment, the control circuit 15 of the matrix circuit 51 changes the γ characteristic of the γ circuit 45 and the matrix coefficient of the second matrix circuit 46 by the changeover signal by the mode changeover switch 14. Change the matrix coefficient, etc. Next, a second embodiment of the present invention will be described with reference to FIG. FIG. 9 shows an endoscope apparatus 1B provided with the second embodiment of the present invention. Next, a second embodiment of the present invention will be described with reference to FIG. 9 shows an endoscope apparatus 1B provided with the second embodiment of the present invention.
The endoscope apparatus 1B has a configuration in which a video processor 4B in which a part of the video processor 4 in FIG. 1 is changed is employed. In this video processor 4B, the first matrix circuit 42, the γ circuit 45, and the second matrix circuit 46 in the video processor 4 of FIG. The endoscope apparatus 1B has a configuration in which a video processor 4B in which a part of the video processor 4 in FIG. 1 is changed is employed. In this video processor 4B, the first matrix circuit 42, the γ circuit 45, and the second matrix circuit 46 in the video processor 4 of FIG.
Then, as described in the first embodiment, the control circuit 15 changes the γ characteristic of the γ circuit 45 and the matrix coefficient of the second matrix circuit 46 in accordance with the switching signal from the mode changeover switch 14. Change matrix coefficients. Then, as described in the first embodiment, the control circuit 15 changes the γ characteristic of the γ circuit 45 and the matrix coefficient of the second matrix circuit 46 in accordance with the switching signal from the mode changeover switch 14. Change matrix coefficients.

このマトリクス回路51は、通常光観察モードから狭帯域光観察モードに切り替えられた場合、混色の無い変換、γ特性の変更、及び長波長側の色信号を抑圧し(短波長側の色信号を強調し)た変換を行う処理が、その係数の変更によりまとめて行われる。
また、A/D変換回路34とY/C分離回路37との間に入力信号に対してその信号レベルをオートゲインコントロールするAGC回路52を設けている。

また、明るさ検波回路35にはCDS回路32の出力信号と、マトリクス回路51からの輝度信号Ynbiとが入力されるようにしている。 Further, the output signal of the CDS circuit 32 and the luminance signal Ynbi from the matrix circuit 51 are input to the brightness detection circuit 35. また、制御回路15は、モード切替スイッチ14の切替による観察モードに応じてAGC回路52のAGCゲイン及び追従スピードを変更する。 Further, the control circuit 15 changes the AGC gain and the tracking speed of the AGC circuit 52 according to the observation mode by switching the mode changeover switch 14. When the matrix circuit 51 is switched from the normal light observation mode to the narrow-band light observation mode, the matrix circuit 51 suppresses color-free conversion, changes in γ characteristics, and color signals on the long wavelength side (converts color signals on the short wavelength side). The process of performing the emphasized conversion is collectively performed by changing the coefficient. When the matrix circuit 51 is switched from the normal light observation mode to the narrow-band light observation mode, the matrix circuit 51 suppresses color-free conversion, changes in γ characteristics, and color signals on the long wavelength side (converts color signals on) the short wavelength side). The process of performing the emphasized conversion is collectively performed by changing the coefficient.
In addition, an AGC circuit 52 is provided between the A / D conversion circuit 34 and the Y / C separation circuit 37 for automatically gain-controlling the signal level of the input signal. In addition, an AGC circuit 52 is provided between the A / D conversion circuit 34 and the Y / C separation circuit 37 for automatically gain-controlling the signal level of the input signal.
Further, the brightness detection circuit 35 receives the output signal of the CDS circuit 32 and the luminance signal Ynbi from the matrix circuit 51. Further, the control circuit 15 changes the AGC gain and the follow-up speed of the AGC circuit 52 according to the observation mode by switching the mode switch 14. Further, the brightness detection circuit 35 receives the output signal of the CDS circuit 32 and the luminance signal Ynbi from the matrix circuit 51. Further, the control circuit 15 changes the AGC gain and the follow-up speed of the AGC circuit 52 according to the observation mode by switching the mode switch 14.

具体的には、狭帯域光観察モード時には、制御回路15は、AGC回路51のAGCゲインを通常光観察モード時よりも大きく設定すると共に、例えばAGCゲイン制御の追従スピードを光源装置3の絞り22の絞り制御スピードよりも遅く設定する。このようにして、絞り22による調光動作をAGC回路52による信号のゲイン制御動作よりも優先させるようにしている。
また、調光回路36においては、基準の明るさ(調光の目標値)も、通常光観察モード時と特殊光観察モード時で切り替える。
こうすることにより、光源装置の絞り22による調光動作を優先させて調光を行うようにする。 By doing so, the dimming operation by the aperture 22 of the light source device is prioritized and the dimming is performed. その調光動作により、絞り22による調光が十分に行えない場合には補助的にAGC回路52によるオートゲイン制御動作が行われるようになる。 Due to the dimming operation, when the dimming by the aperture 22 cannot be sufficiently performed, the auto gain control operation by the AGC circuit 52 is assisted. Specifically, in the narrow band light observation mode, the control circuit 15 sets the AGC gain of the AGC circuit 51 to be larger than that in the normal light observation mode, and for example, sets the follow-up speed of AGC gain control to the aperture 22 of the light source device 3. Set slower than the aperture control speed. In this way, the dimming operation by the diaphragm 22 is prioritized over the signal gain control operation by the AGC circuit 52. Specifically, in the narrow band light observation mode, the control circuit 15 sets the AGC gain of the AGC circuit 51 to be larger than that in the normal light observation mode, and for example, sets the follow-up speed of AGC gain control to The aperture 22 of the light source device 3. Set slower than the aperture control speed. In this way, the dimming operation by the diaphragm 22 is prioritized over the signal gain control operation by the AGC circuit 52.
In the light control circuit 36, the reference brightness (target value of light control) is also switched between the normal light observation mode and the special light observation mode. In the light control circuit 36, the reference brightness (target value of light control) is also switched between the normal light observation mode and the special light observation mode.
In this way, the light control is performed by giving priority to the light control operation by the diaphragm 22 of the light source device. When the dimming operation cannot sufficiently perform dimming by the diaphragm 22, an automatic gain control operation by the AGC circuit 52 is supplementarily performed. In this way, the light control is performed by giving priority to the light control operation by the diaphragm 22 of the light source device. When the dimming operation cannot sufficiently perform dimming by the diaphragm 22, an automatic gain control operation by the AGC circuit 52 is supplementarily performed.

具体的には、絞り22が開放となって照明光量が最大となっても明るさが十分でないような場合には、AGC回路52が機能するようになるので、(絞り22が解放になる前に)AGC回路52が動作してしまうことによりS/Nが劣化してしまうことを防止でき、適切な明るさの内視鏡画像が得られるようになる。
本実施例によれば、実施例1の作用効果の他に、特に狭帯域光観察モード時におけるS/Nの劣化を防止して適切な明るさの内視鏡画像が得られるようになる。 According to this embodiment, in addition to the effects of Example 1, deterioration of S / N is prevented especially in the narrow band light observation mode, and an endoscopic image having an appropriate brightness can be obtained.
なお、上述した各実施例等を部分的に組み合わせる等して構成される実施例も本発明に属する。 In addition, an example configured by partially combining the above-mentioned examples and the like also belongs to the present invention. Specifically, if the brightness is not sufficient even when the aperture 22 is opened and the amount of illumination light is maximized, the AGC circuit 52 will function (before the aperture 22 is released). B) S / N can be prevented from deteriorating due to the operation of the AGC circuit 52, and an endoscopic image with appropriate brightness can be obtained. Specifically, if the brightness is not sufficient even when the aperture 22 is opened and the amount of illumination light is maximized, the AGC circuit 52 will function (before the aperture 22 is released). B) S / N can be prevented from deteriorating due to the operation of the AGC circuit 52, and an endoscopic image with appropriate brightness can be obtained.
According to the present embodiment, in addition to the operational effects of the first embodiment, it is possible to obtain an endoscopic image with appropriate brightness by preventing deterioration of S / N particularly in the narrow-band light observation mode. According to the present embodiment, in addition to the operational effects of the first embodiment, it is possible to obtain an endoscopic image with appropriate brightness by preventing deterioration of S / N particularly in the narrow-band light observation mode.
Note that embodiments configured by partially combining the above-described embodiments and the like also belong to the present invention. Note that embodiments configured by partially combining the above-described embodiments and the like also belong to the present invention.

[付記]
1.請求項3において、前記変換手段は、前記輝度信号及び色差信号から混色が殆ど無い3原色信号に変換する。
2.請求項3において、さらに前記3原色信号から輝度信号及び色差信号に変換する第2の変換手段を有し、前記可視領域の照明光から狭帯域の照明光に切り替えられた場合に、前記第2の変換手段は、前記3原色信号における短波長の色信号の重み付けを大きくする変換特性に変更する。

3. 3. 3. 請求項1において、前記色分離手段により分離された前記輝度信号及び色差信号から第2の輝度信号と第2の色差信号に変換する変換手段を有し、前記可視領域の照明光から狭帯域の照明光に切り替えられた場合に、前記変換手段は、短波長の色信号の重み付けを大きくする変換特性に変更する。 The first aspect of the present invention includes a conversion means for converting the luminance signal and the luminance signal separated by the color separating means into a second luminance signal and a second luminance signal, and the illumination light in the visible region has a narrow band. When switched to illumination light, the conversion means changes to a conversion characteristic that increases the weighting of the short-wavelength color signal. [Appendix] [Appendix]
1. 4. The conversion unit according to claim 3, wherein the conversion unit converts the luminance signal and the color difference signal into a three primary color signal having almost no color mixture. 1. 4. The conversion unit according to claim 3, wherein the conversion unit converts the luminance signal and the color difference signal into a three primary color signal having almost no color mixture.
2. 4. The method according to claim 3, further comprising second conversion means for converting the three primary color signals into a luminance signal and a color difference signal, and when the illumination light in the visible region is switched to illumination light in a narrow band. The conversion means changes the conversion characteristic to increase the weighting of the short wavelength color signal in the three primary color signals. 2. 4. The method according to claim 3, further comprising second conversion means for converting the three primary color signals into a luminance signal and a color difference signal, and when the illumination light in the visible region is switched to illumination light in a narrow band. The conversion means changes the conversion characteristic to increase the weighting of the short wavelength color signal in the three primary color signals.
3. 2. The conversion device according to claim 1, further comprising a conversion unit configured to convert the luminance signal and the color difference signal separated by the color separation unit into a second luminance signal and a second color difference signal, and having a narrow band from the illumination light in the visible region. When switched to illumination light, the conversion means changes the conversion characteristic to increase the weighting of the short wavelength color signal. 3. 2. The conversion device according to claim 1, further comprising a conversion unit configured to convert the luminance signal and the color difference signal separated by the color separation unit into a second luminance signal and a second color difference signal, and having a narrow band from the illumination light in the visible region. When switched to illumination light, the conversion means changes the conversion characteristic to increase the weighting of the short wavelength color signal.

4.請求項1において、前記可視領域の照明光から狭帯域の照明光に切り替えられた場合に、γ特性を変更する。
5.請求項1において、前記可視領域の照明光から狭帯域の照明光に切り替えられた場合に、強調手段による強調特性を変更する。
6.内視鏡に搭載されたカラー撮像を行うための色分離用光学フィルタを設けた撮像手段からの出力信号に対して、色分離手段により輝度信号と色差信号とに分離してカラーの映像信号を生成する信号処理を行う信号処理装置と、
可視領域の照明光と狭帯域の照明光とを切り替えて発生する光源装置と、
を備えた内視鏡装置において、
前記可視領域の照明光と狭帯域の照明光との切り替えに連動して、前記色分離手段により色分離された信号に対する処理特性を変更する処理特性変更手段を具備することを特徴とする内視鏡装置。 An endoscope characterized by comprising a processing characteristic changing means for changing the processing characteristic of a signal color-separated by the color separating means in conjunction with switching between the illumination light in the visible region and the illumination light in a narrow band. Mirror device. 4). In claim 1, when the illumination light in the visible region is switched to illumination light in a narrow band, the γ characteristic is changed. 4). In claim 1, when the illumination light in the visible region is switched to illumination light in a narrow band, the γ characteristic is changed.
5). In Claim 1, when the illumination light in the visible region is switched to illumination light in a narrow band, the enhancement characteristic by the enhancement unit is changed. 5). In Claim 1, when the illumination light in the visible region is switched to illumination light in a narrow band, the enhancement characteristic by the enhancement unit is changed.
6). An output signal from an image pickup means provided with a color separation optical filter for color image pickup mounted on an endoscope is separated into a luminance signal and a color difference signal by a color separation means to generate a color video signal. A signal processing device for performing signal processing to be generated; 6). An output signal from an image pickup means provided with a color separation optical filter for color image pickup mounted on an spectrometer is separated into a luminance signal and a color difference signal by a color separation means to generate a color video signal. signal processing device for performing signal processing to be generated;
A light source device that switches between illumination light in a visible region and illumination light in a narrow band; and A light source device that switches between illumination light in a visible region and illumination light in a narrow band; and
In an endoscope apparatus comprising: In an oscillator apparatus comprising:
Intrasight characterized by comprising processing characteristic changing means for changing processing characteristics for signals color-separated by the color separation means in conjunction with switching between illumination light in the visible region and narrow-band illumination light Mirror device. Intrasight characterized by comprising processing characteristic changing means for changing processing characteristics for signals color-separated by the color separation means in conjunction with switching between illumination light in the visible region and narrow-band illumination light Mirror device.

7.付記6において、前記色分離手段より分離された前記色差信号に対する帯域制限を行う帯域制限手段を有し、前記可視領域の照明光から狭帯域の照明光に切り替えられた場合に、前記処理特性変更手段は、前記帯域制限手段による通過帯域の特性を広帯域に変更する。
8. 8. 付記6において、前記色分離手段により分離された前記輝度信号及び色差信号から3原色信号に変換する変換手段手段を有し、前記可視領域の照明光から狭帯域の照明光に切り替えられた場合に、前記処理特性変更手段は、前記変換手段による変換特性を決定する変換係数を変更する。 In Appendix 6, when there is a conversion means means for converting the brightness signal and the color difference signal separated by the color separation means into three primary color signals, and the illumination light in the visible region is switched to the illumination light in a narrow band. , The processing characteristic changing means changes the conversion coefficient which determines the conversion characteristic by the conversion means.
9. 9. 付記6において、さらに照明光の光量を制御する調光信号の生成手段と、前記映像信号のレベルを可変制御するゲイン制御手段とを有し、前記調光信号の生成手段の動作を前記ゲイン制御手段の動作よりも優先させた。 In Appendix 6, a dimming signal generating means for further controlling the amount of illumination light and a gain controlling means for variably controlling the level of the video signal are provided, and the operation of the dimming signal generating means is controlled by the gain. Prioritized over the operation of the means. 7). The supplementary note 6 further comprises a band limiting unit that performs band limitation on the color difference signal separated by the color separation unit, and the processing characteristic change is performed when the illumination light in the visible region is switched to illumination light in a narrow band. The means changes the characteristic of the pass band by the band limiting means to a wide band. 7). The supplementary note 6 further in a band limiting unit that performs band limitation on the color difference signal separated by the color separation unit, and the processing characteristic change is performed when the illumination light in the visible region is switched to illumination light in a narrow band. The means changes the characteristic of the pass band by the band limiting means to a wide band.
8). In Additional Statement 6, when the luminance signal and the color difference signal separated by the color separation means are converted into three primary color signals, when the illumination light in the visible region is switched to the narrow-band illumination light The processing characteristic changing means changes the conversion coefficient for determining the conversion characteristic by the converting means. 8). In Additional Statement 6, when the luminance signal and the color difference signal separated by the color separation means are converted into three primary color signals, when the illumination light in the visible region is switched to the narrow-band illumination light The processing characteristic changing means changes the conversion coefficient for determining the conversion characteristic by the converting means.
9. In Appendix 6, further comprising: a dimming signal generating means for controlling the amount of illumination light; and a gain control means for variably controlling the level of the video signal, wherein the operation of the dimming signal generating means is controlled by the gain control. Prioritized the action of the means. 9. In Appendix 6, further comprising: a dimming signal generating means for controlling the amount of illumination light; and a gain control means for variably controlling the level of the video signal, wherein the operation of the dimming signal generating means is controlled by the gain control. Prioritized the action of the means.

色分離フィルタを備えた内視鏡を用いて白色照明のもとでカラー撮像を行う通常光観察モードで使用できると共に、照明光路中に狭帯域用フィルタを介挿して狭帯域の照明光の場合にはローパスフィルタやマトリクス回路の係数変更による処理特性を変更することで、狭帯域光観察モードにおいても画質の良い画像が得られる。   Can be used in normal light observation mode in which color imaging is performed under white illumination using an endoscope equipped with a color separation filter, and narrowband illumination light is inserted through a narrowband filter in the illumination optical path By changing the processing characteristics by changing the coefficients of the low-pass filter or matrix circuit, an image with good image quality can be obtained even in the narrow-band light observation mode.

本発明の実施例1を備えた内視鏡装置の構成を示すブロック図。 1 is a block diagram showing a configuration of an endoscope apparatus including Example 1 of the present invention. 固体撮像素子に設けられた色分離フィルタのフィルタ配列の構成を示す図。 The figure which shows the structure of the filter arrangement | sequence of the color separation filter provided in the solid-state image sensor. 狭帯域用フィルタの分光特性例を示す特性図。 The characteristic view which shows the example of the spectral characteristic of the filter for narrow bands. 本実施例の動作説明用のフローチャート図。 The flowchart for operation | movement description of a present Example. 輝度信号と色差信号における信号帯域を示す図。 The figure which shows the signal band in a luminance signal and a color difference signal. 図5の特性を考慮して第1変形例において設定される第2マトリクス回路の係数を示す図。 The figure which shows the coefficient of the 2nd matrix circuit set in a 1st modification in consideration of the characteristic of FIG. 第2変形例における狭帯域用フィルタの分光特性を示す特性図。 The characteristic view which shows the spectral characteristics of the filter for narrow bands in the 2nd modification. 図7の場合において設定される第2マトリクス回路の係数を示す図。 The figure which shows the coefficient of the 2nd matrix circuit set in the case of FIG. 本発明の実施例2を備えた内視鏡装置の構成を示すブロック図。 The block diagram which shows the structure of the endoscope apparatus provided with Example 2 of this invention. 従来例の映像信号処理装置の構成を示すブロック図。 The block diagram which shows the structure of the video signal processing apparatus of a prior art example.

符号の説明Explanation of symbols

1…内視鏡装置
2…(電子)内視鏡
3…光源装置
4…ビデオプロセッサ
5…モニタ
7…挿入部
8…操作部
11…ライトガイドコネクタ
13…ライトガイド
14…モード切替スイッチ
15…制御回路
16…フィルタ挿脱機構
20…ランプ
22…絞り
23…絞り駆動回路
24…狭帯域用フィルタ
28…対物レンズ
29…CCD
30…色分離フィルタ 31…CCD駆動回路 32…CDS回路 33…ID発生回路 34…A/D変換回路 35…明るさ検波回路 36…調光回路 37…Y/C分離回路 38,45…γ回路 39…セレクタ 41、43…LPF 30 ... Color separation filter 31 ... CCD drive circuit 32 ... CDS circuit 33 ... ID generation circuit 34 ... A / D conversion circuit 35 ... Brightness detection circuit 36 ​​... Dimming circuit 37 ... Y / C separation circuit 38, 45 ... γ circuit 39 ... Selectors 41, 43 ... LPF
42、46…マトリクス回路 44…同時化回路 47…拡大回路 代理人 弁理士 伊藤 進DESCRIPTION OF SYMBOLS 1 ... Endoscope apparatus 2 ... (Electronic) endoscope 3 ... Light source apparatus 4 ... Video processor 5 ... Monitor 7 ... Insertion part 8 ... Operation part 11 ... Light guide connector 13 ... Light guide 14 ... Mode switch 15 ... Control Circuit 16 ... Filter insertion / removal mechanism 20 ... Lamp 22 ... Aperture 23 ... Aperture drive circuit 24 ... Narrow band filter 28 ... Objective lens 29 ... CCD 42, 46 ... Matrix circuit 44 ... Simultaneous circuit 47 ... Expansion circuit Agent Attorney Susumu Ito DECRIPTION OF SYMBOLS 1 ... Endoscope apparatus 2 ... (Electronic) microscope 3 ... Light source apparatus 4 ... Video processor 5 ... Monitor 7 ... Insertion part 8 ... Operation part 11 ... Light guide connector 13 ... Light guide 14 ... Mode switch 15 ... Control Circuit 16 ... Filter insertion / removal mechanism 20 ... Lamp 22 ... Aperture 23 ... Aperture drive circuit 24 ... Narrow band filter 28 ... Objective lens 29 ... CCD
DESCRIPTION OF SYMBOLS 30 ... Color separation filter 31 ... CCD drive circuit 32 ... CDS circuit 33 ... ID generation circuit 34 ... A / D conversion circuit 35 ... Brightness detection circuit 36 ... Dimming circuit 37 ... Y / C separation circuit 38, 45 ... gamma circuit 39 ... Selector 41, 43 ... LPF DESCRIPTION OF SYMBOLS 30 ... Color separation filter 31 ... CCD drive circuit 32 ... CDS circuit 33 ... ID generation circuit 34 ... A / D conversion circuit 35 ... Brightness detection circuit 36 ​​... Dimming circuit 37 ... Y / C separation circuit 38, 45 ... gamma circuit 39 ... Selector 41, 43 ... LPF
42, 46 ... Matrix circuit 44 ... Synchronization circuit 47 ... Expanded circuit Agent Patent attorney Susumu Ito 42, 46 ... Matrix circuit 44 ... Synchronization circuit 47 ... Expanded circuit Agent Patent attorney Susumu Ito

Claims (3)

  1. 内視鏡に搭載されたカラー撮像を行うための色分離用光学フィルタを設けた撮像手段からの出力信号に対して、色分離手段により輝度信号と色差信号とに分離してカラーの映像信号を生成する信号処理を行う内視鏡用映像信号処理装置において、
    可視領域の照明光の場合から狭帯域の照明光の場合の信号処理への切り替えに対応して、前記色分離手段により色分離された信号に対する処理特性を変更する処理特性変更手段と、
    前記色分離手段より分離された前記色差信号に対する帯域制限を行う帯域制限手段と、
    を具備し、
    前記可視領域の照明光から狭帯域の照明光に切り替えられた場合に、前記処理特性変更手段は、前記帯域制限手段による通過帯域の特性を広帯域に変更することを特徴とする内視鏡用映像信号処理装置。 When the illumination light in the visible region is switched to the illumination light in a narrow band, the processing characteristic changing means changes the characteristic of the passing band by the band limiting means to a wide band. Signal processing device. An output signal from an image pickup means provided with a color separation optical filter for color image pickup mounted on an endoscope is separated into a luminance signal and a color difference signal by a color separation means to generate a color video signal. In an endoscope video signal processing apparatus that performs signal processing to be generated, An output signal from an image pickup means provided with a color separation optical filter for color image pickup mounted on an spectrometer is separated into a luminance signal and a color difference signal by a color separation means to generate a color video signal. signal processing apparatus that performs signal processing to be generated,
    Corresponding to switching from the case of illumination light in the visible region to the signal processing in the case of narrow-band illumination light, processing characteristic changing means for changing processing characteristics for the signals color-separated by the color separation means ; Corresponding to switching from the case of illumination light in the visible region to the signal processing in the case of narrow-band illumination light, processing characteristic changing means for changing processing characteristics for the signals color-separated by the color separation means ;
    Band limiting means for performing band limitation on the color difference signal separated by the color separation means; Band limiting means for performing band limitation on the color difference signal separated by the color separation means;
    Comprising Comprising
    The video for an endoscope , wherein when the illumination light in the visible region is switched to illumination light in a narrow band, the processing characteristic changing unit changes the characteristic of the pass band by the band limiting unit to a wide band Signal processing device. The video for an oscillator, wherein when the illumination light in the visible region is switched to illumination light in a narrow band, the processing characteristic changing unit changes the characteristic of the pass band by the band limiting unit to a wide band Signal processing device.
  2. さらに前記色分離手段により分離された前記輝度信号及び色差信号から3原色信号に変換する変換手段を有し、 Furthermore, it has conversion means for converting the luminance signal and color difference signal separated by the color separation means into three primary color signals,
    前記可視領域の照明光から狭帯域の照明光に切り替えられた場合に、前記処理特性変更手段は、前記変換手段による変換特性を決定する変換係数を変更することを特徴とする請求項1に記載の内視鏡用映像信号処理装置。  The processing characteristic changing unit changes a conversion coefficient for determining a conversion characteristic by the conversion unit when the illumination light in the visible region is switched to illumination light in a narrow band. Endoscope video signal processing device.
  3. さらに照明光の光量を制御する調光信号の生成手段と、前記映像信号のレベルを可変制御するゲイン制御手段とを有し、  Furthermore, it has a dimming signal generating means for controlling the amount of illumination light, and a gain control means for variably controlling the level of the video signal,
    前記調光信号の生成手段の動作を前記ゲイン制御手段の動作よりも優先させたことを特徴とする請求項1に記載の内視鏡用映像信号処理装置。  2. The endoscope video signal processing apparatus according to claim 1, wherein the operation of the dimming signal generation unit is prioritized over the operation of the gain control unit.
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