JP4554944B2 - Endoscope device - Google Patents

Endoscope device Download PDF

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JP4554944B2
JP4554944B2 JP2004007475A JP2004007475A JP4554944B2 JP 4554944 B2 JP4554944 B2 JP 4554944B2 JP 2004007475 A JP2004007475 A JP 2004007475A JP 2004007475 A JP2004007475 A JP 2004007475A JP 4554944 B2 JP4554944 B2 JP 4554944B2
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浩平 池谷
三文 福山
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Hoya Corp
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本発明は、内視鏡装置に関し、特に、波長帯域幅の異なる２つの光源を用いた内視鏡装置に関する。   The present invention relates to an endoscope apparatus, and more particularly, to an endoscope apparatus using two light sources having different wavelength bandwidths.

体腔内の観察や検査を行う内視鏡装置において、波長の短い光は生体組織表面から浅い領域にまで到達して反射し、波長の長い光は生体組織表面から深い領域にまで到達して反射する特性を使って、波長の異なる光を観察面に照射することのできる光源装置が提案されている。   In an endoscopic device that observes and examines the body cavity, light with a short wavelength reaches the shallow area from the surface of the living tissue and reflects, and light with a long wavelength reaches the deep area from the surface of the living tissue and reflects. There has been proposed a light source device that can irradiate an observation surface with light having different wavelengths by using such characteristics.

特許文献１は、キセノンランプなどの放電ランプによる白色光を、フィルタを使って波長の異なるＲ、Ｇ、Ｂの三色に分けて照射させ、フィルタの透過度合いを調整することによって生体組織表面から所望する深度の情報を得る装置を開示する。
特開２００２−９５６３５号公報 In Patent Document 1, white light from a discharge lamp such as a xenon lamp is irradiated with three colors of R, G, and B having different wavelengths using a filter, and the degree of transmission of the filter is adjusted to adjust the degree of transmission of the filter. An apparatus for obtaining information on a desired depth is disclosed.
JP 2002-95635 A

しかし、この装置において光源となるキセノンランプなどの放電ランプによる白色光は、波長帯域が広く一定の波長分布の広がりを有している。そのため、フィルタを用いたとしても波長帯域を狭めることは困難で、所望の深度以外の領域の画像情報も得られてしまい鮮明な画像を得るまでに至らなかった。   However, white light emitted from a discharge lamp such as a xenon lamp that is a light source in this apparatus has a wide wavelength band and a constant wavelength distribution. Therefore, even if a filter is used, it is difficult to narrow the wavelength band, and image information in a region other than the desired depth is obtained, so that a clear image cannot be obtained.

図１に、一般的なＣＣＤにおけるフィルタの分光特性と、後述する青色レーザー光の波長帯域をグラフで示す。４００〜７００ｎｍ程度の幅広い波長帯域を有する白色光では、フィルタによってＢを中心とした分光、Ｇを中心とした分光、Ｒを中心とした分光を行うことは可能であるが、フィルタによる分光では、一定の幅以下に波長帯域を抑えることは困難であることが分かる。   FIG. 1 is a graph showing the spectral characteristics of a filter in a general CCD and the wavelength band of blue laser light described later. With white light having a wide wavelength band of about 400 to 700 nm, it is possible to perform spectrum centered on B, spectrum centered on G, and spectrum centered on R with a filter. It can be seen that it is difficult to suppress the wavelength band below a certain width.

また、白色光は、幅広い波長帯域を有するが比較的波長の長い５００ｎｍ以上の波長帯域の成分が多く、比較的波長の短い５００ｎｍ以下の波長帯域の成分が少ない。そのため通常観察画像を得ることには問題が生じないが、生体組織表面から浅い領域の画像を鮮明に得るために、フィルタによって波長の短い光だけを分光して照射すると照明光量不足が生じていた。   Further, white light has a wide wavelength band, but has many components in a wavelength band of 500 nm or more with a relatively long wavelength, and few components in a wavelength band of 500 nm or less with a relatively short wavelength. Therefore, there is no problem in obtaining a normal observation image. However, in order to obtain a clear image of a shallow region from the surface of a living tissue, if the light is split and irradiated only with light having a short wavelength, the amount of illumination light is insufficient. .

したがって本発明の目的は、通常観察画像に加えて生体組織表面から浅い領域における鮮明な画像を取得する装置を提供することである。   Accordingly, an object of the present invention is to provide an apparatus for acquiring a clear image in a shallow region from the surface of a living tissue in addition to a normal observation image.

本発明に係る内視鏡装置は、波長帯域の広い光を照射する第１光源部と、波長が短く且つ波長帯域が狭い光を照射する第２光源部と、第１、第２光源部を切り替えて観察面に照射する光源切り替え部と、第１、第２光源部の各光の照射時に撮像により得られた第１、第２画像信号のうち先に照射して得られた画像信号を一時記録する第１画像メモリ部と、第１、第２画像信号を合成する映像信号合成部とを備える内視鏡装置。これにより、白色光照射により得られる生体組織表面から深い領域の画像に加えて、励起光照射により得られる生体組織表面から浅い領域の画像を合成して、観察面の鮮明な画像を取得することが可能になる。   An endoscope apparatus according to the present invention includes a first light source unit that emits light having a wide wavelength band, a second light source unit that emits light having a short wavelength and a narrow wavelength band, and first and second light source units. A light source switching unit that switches and irradiates the observation surface, and an image signal obtained by first irradiating the first and second image signals obtained by imaging at the time of irradiation of each light of the first and second light source units. An endoscope apparatus comprising: a first image memory unit that temporarily records; and a video signal synthesis unit that synthesizes first and second image signals. In this way, in addition to the image of the deep region from the surface of the biological tissue obtained by irradiation with white light, the image of the shallow region from the surface of the biological tissue obtained by irradiation with excitation light is synthesized to obtain a clear image of the observation surface Is possible.

好ましくは、第１、第２画像信号のうち後に照射して得られた画像信号を一時記録する第２画像メモリ部をさらに備える。   Preferably, the image processing apparatus further includes a second image memory unit that temporarily records an image signal obtained by subsequent irradiation of the first and second image signals.

また、好ましくは、第１光源部は、放電ランプによる白色光源を有する。   Preferably, the first light source unit includes a white light source using a discharge lamp.

また、好ましくは、第２光源部は、レーザーによる青色光源を有する。これにより、特定の波長で狭い波長領域を有する光を励起光として照射することが可能となる。   Preferably, the second light source unit has a blue light source using a laser. This makes it possible to irradiate light having a narrow wavelength region at a specific wavelength as excitation light.

また、好ましくは、第２光源部が発する光の波長帯域は、４００ｎｍから４２０ｎｍである。   Preferably, the wavelength band of light emitted from the second light source unit is 400 nm to 420 nm.

また、好ましくは、第２画像信号は、第２光源部の照射時に得られた画像信号のうち高周波成分だけを取り出して得られる。これにより、励起光照射により得られた画像のうち輪郭部分を強調させた第２画像信号を第１画像信号と合成させることができ、生体組織表面から浅い領域の画像をより鮮明に得ることが可能になる。   Preferably, the second image signal is obtained by extracting only a high-frequency component from the image signal obtained when the second light source unit is irradiated. As a result, the second image signal in which the contour portion of the image obtained by the excitation light irradiation is emphasized can be combined with the first image signal, and a shallow region image can be obtained more clearly from the surface of the living tissue. It becomes possible.

さらに好ましくは、第２画像信号を構成する画素信号のそれぞれは、第２光源部の照射時に撮像により得られた画像信号を構成する画素信号のそれぞれにおいて隣接画素との輝度情報の差分値である。これにより、励起光照射により得られた画像の輪郭部分の情報を簡易に得ることが可能になる。   More preferably, each of the pixel signals constituting the second image signal is a difference value of luminance information with the adjacent pixel in each of the pixel signals constituting the image signal obtained by imaging at the time of irradiation of the second light source unit. . Thereby, it becomes possible to easily obtain information on the contour portion of the image obtained by the excitation light irradiation.

以上のように本発明によれば、通常観察画像に加えて生体組織表面から浅い領域における鮮明な画像を取得する装置を提供することができる。   As described above, according to the present invention, it is possible to provide an apparatus that acquires a clear image in a shallow region from the surface of a living tissue in addition to a normal observation image.

以下、本発明の実施形態について、図２〜７を参照して説明する。図２は、内視鏡装置の構成図を示す。本実施形態に係る内視鏡装置は、電子スコープ１０と、カラープロセッサ（電子内視鏡用プロセッサ）２０と、カラーモニタ４０とを備える。電子スコープ１０は、カラープロセッサ２０の制御により、被写体を撮像する。撮像により得られた画像信号はカラープロセッサ２０によってカラーモニタ４０で出力（画面表示）が可能な映像信号に変換される。変換された映像信号はアナログ信号でカラーモニタ４０に伝達される。伝達された映像信号は、カラーモニタ４０によって出力される。使用者は、カラーモニタ４０による出力結果により、電子スコープで撮像された被写体映像を観察することができる。   Hereinafter, embodiments of the present invention will be described with reference to FIGS. FIG. 2 shows a configuration diagram of the endoscope apparatus. The endoscope apparatus according to the present embodiment includes an electronic scope 10, a color processor (electronic endoscope processor) 20, and a color monitor 40. The electronic scope 10 images the subject under the control of the color processor 20. The image signal obtained by imaging is converted by the color processor 20 into a video signal that can be output (screen display) on the color monitor 40. The converted video signal is transmitted to the color monitor 40 as an analog signal. The transmitted video signal is output by the color monitor 40. The user can observe the subject image captured by the electronic scope based on the output result from the color monitor 40.

電子スコープ１０は、撮像部１１と、照明部１２とを有し、照明部１２が被写体に適度な光量を与えながら撮像部１１が被写体を撮像する。   The electronic scope 10 includes an imaging unit 11 and an illumination unit 12, and the imaging unit 11 captures an image of the subject while the illumination unit 12 gives an appropriate amount of light to the subject.

撮像部１１は、対物レンズ１１ａ、ＣＣＤなどの撮像素子１１ｂとを有する。撮像素子１１ｂの駆動は、後述する制御回路２４が出力するクロックパルスに従って行われる。被写体の撮像によって撮像素子１１ｂに蓄積された電荷は、画像信号としてＲとＧとＢに色分離されて、映像信号処理部２１に転送される。   The imaging unit 11 includes an objective lens 11a and an imaging element 11b such as a CCD. The image sensor 11b is driven in accordance with a clock pulse output from a control circuit 24 described later. The charges accumulated in the image sensor 11b by imaging the subject are color-separated into R, G, and B as image signals and transferred to the video signal processing unit 21.

照明部１２は、白色光を発し、光誘導部材１２ｂ、配光レンズ１２ａを介して生体組織に照射する第１光源部２６からの光、及び励起光を発し、光誘導部材１２ｂ、配光レンズ１２ａを介して、生体組織に照射する第２光源部２７からの光を照射面に供給する。電子スコープ１０と、カラープロセッサ２０は、コネクタ部（不図示）で電気的、光学的に接続される。   The illuminating unit 12 emits white light, emits light from the first light source unit 26 that irradiates the living tissue via the light guiding member 12b and the light distribution lens 12a, and excitation light, and the light guiding member 12b and light distribution lens. The light from the 2nd light source part 27 which irradiates a biological tissue is supplied to an irradiation surface via 12a. The electronic scope 10 and the color processor 20 are electrically and optically connected by a connector portion (not shown).

カラープロセッサ２０は、映像信号処理部２１、制御回路２４、第１、第２光源部２６、２７、及び光源切り替え部３０を有しており、電子スコープ１０で撮像し電荷転送された画像信号を、カラーモニタ４０で出力できる映像信号に変換する。   The color processor 20 includes a video signal processing unit 21, a control circuit 24, first and second light source units 26 and 27, and a light source switching unit 30. The color processor 20 captures an image signal captured by the electronic scope 10 and subjected to charge transfer. Then, it is converted into a video signal that can be output by the color monitor 40.

映像信号処理部２１は、電子スコープ１０から送られてきた画像信号を前段映像信号処理回路２１ａでＡ／Ｄ変換、ガンマ補正、輪郭強調、及び増幅し、メモリ切り替え部２１ｂを介して、第１、第２画像メモリ部２１ｃ、２１ｄに順次一時記録する。メモリ切り替え部２１ｂは、後述する光源切り替え部３０で第１、第２光源部２６、２７のいずれかに切り替えられた光源に対応して画像信号を一時記録させるメモリを切り替える。第１画像メモリ部２１ｃは、第１光源部２６から供給された白色光照射による第１画像信号を一時記録する。第２画像メモリ部２１ｄは、第２光源部２７から供給された励起光照射による第２画像信号を一時記録する。第２画像信号は、第２光源部２７から供給された励起光による画像信号のうち高周波成分だけを取り出した画像信号である。高周波成分の取り出しについては後述する。第１、第２画像メモリ部２１ｃ、２１ｄに一時記録された第１、第２画像信号は、後段映像信号処理回路２１ｅに転送される。後段映像信号処理回路２１ｅは、転送された第１、第２画像信号を合成した後、Ｖｉｄｅｏコンポジット信号、Ｙ／Ｃ分離信号などの映像信号に変換し、Ｄ／Ａ変換部２１ｆでアナログ信号に変換された後、カラーモニタ４０に出力する。   The video signal processing unit 21 performs A / D conversion, gamma correction, contour enhancement, and amplification on the image signal sent from the electronic scope 10 by the preceding video signal processing circuit 21a, and the first signal is sent via the memory switching unit 21b. The second image memory units 21c and 21d are temporarily recorded sequentially. The memory switching unit 21b switches the memory for temporarily recording the image signal corresponding to the light source switched to one of the first and second light source units 26 and 27 by the light source switching unit 30 described later. The first image memory unit 21 c temporarily records the first image signal by the white light irradiation supplied from the first light source unit 26. The second image memory unit 21d temporarily records the second image signal by the excitation light irradiation supplied from the second light source unit 27. The second image signal is an image signal obtained by extracting only a high frequency component from the image signal based on the excitation light supplied from the second light source unit 27. The extraction of the high frequency component will be described later. The first and second image signals temporarily recorded in the first and second image memory units 21c and 21d are transferred to the subsequent video signal processing circuit 21e. The post-stage video signal processing circuit 21e synthesizes the transferred first and second image signals, converts them to video signals such as a video composite signal and a Y / C separation signal, and converts them into analog signals by the D / A converter 21f. After the conversion, the data is output to the color monitor 40.

制御回路２４は、図示しないＣＰＵとＲＡＭとを有し、内視鏡装置各部の制御や信号の一時記録を行う。   The control circuit 24 includes a CPU and a RAM (not shown), and controls each part of the endoscope apparatus and temporarily records signals.

第１光源部２６は、白色光を発するキセノンランプなど印加された高電圧パルスによって放電を開始し白色光を発光する放電ランプによる白色光源を有する。第２光源部２７は、励起光を含む青色レーザー光を発するレーザーダイオード（ＬＤ）などの励起光を発するレーザーによる青色光源を有する。発光された白色光、励起光は、光源切り替え部３０、光ファイバなどの光誘導部材１２ｂ、配光部１２ａを介して被写体である生体組織（観察面）に照射される。白色光、励起光のいずれを照射させるかは、使用者が選択する。   The first light source unit 26 has a white light source such as a xenon lamp that emits white light and a discharge lamp that starts discharge by emitting high voltage pulses and emits white light. The second light source unit 27 includes a blue light source using a laser that emits excitation light, such as a laser diode (LD) that emits blue laser light including excitation light. The emitted white light and excitation light are irradiated to the living tissue (observation surface) that is the subject through the light source switching unit 30, the light guiding member 12b such as an optical fiber, and the light distribution unit 12a. The user selects whether to irradiate white light or excitation light.

放電ランプによる白色光は、短い波長から長い波長まで波長帯域の広い広帯域光である。レーザーによる青色レーザー光の励起光は、短い波長（４００ｎｍ〜４２０ｎｍ）で波長帯域の狭い狭帯域光である（図１参照）。   White light from a discharge lamp is broadband light having a wide wavelength band from a short wavelength to a long wavelength. The excitation light of the blue laser light by the laser is narrow-band light with a short wavelength (400 nm to 420 nm) and a narrow wavelength band (see FIG. 1).

光源切り替え部３０は、第１、第２シャッタ３０ａ、３０ｂと、ハーフミラー３０ｃと、励起光反射ミラー３０ｄとを有する。第１、第２シャッタ３０ａ、３０ｂは、開閉により白色光や励起光を透過又は遮断させる。使用者によって、白色光を観察面に照射させる選択がされた場合には、第１シャッタ３０ａはオープン状態にして第１光源部２６からの白色光を透過させ、第２シャッタ３０ｂはクローズ状態にして第２光源部２７からの励起光を遮断する。透過された白色光はハーフミラー３０ｃを透過して光誘導部材１２ｂ、配光部１２ａを介して観察面に照射される。使用者によって、励起光を観察面に照射させる選択がされた場合には、第１シャッタ３０ａはクローズ状態にして第１光源部２６からの白色光を遮断し、第２シャッタ３０ｂはオープン状態にして第２光源部２７からの励起光を透過させる。透過された励起光は、励起光反射ミラー３０ｄ、ハーフミラー３０ｃを反射し、光誘導部材１２ｂ、配光部１２ａを介して観察面に照射される。第１、第２シャッタ３０ａ、３０ｂの開閉制御は、使用者の選択に対応する信号を受けた制御回路２４が行う。   The light source switching unit 30 includes first and second shutters 30a and 30b, a half mirror 30c, and an excitation light reflecting mirror 30d. The first and second shutters 30a and 30b transmit or block white light and excitation light by opening and closing. When the user selects to irradiate the observation surface with white light, the first shutter 30a is opened to transmit white light from the first light source unit 26, and the second shutter 30b is closed. Then, the excitation light from the second light source unit 27 is blocked. The transmitted white light passes through the half mirror 30c and is irradiated onto the observation surface through the light guiding member 12b and the light distribution unit 12a. When the user selects to irradiate the observation surface with excitation light, the first shutter 30a is closed to block white light from the first light source unit 26, and the second shutter 30b is opened. Then, the excitation light from the second light source unit 27 is transmitted. The transmitted excitation light is reflected by the excitation light reflecting mirror 30d and the half mirror 30c, and is irradiated onto the observation surface via the light guiding member 12b and the light distribution unit 12a. Control of the opening and closing of the first and second shutters 30a and 30b is performed by the control circuit 24 that receives a signal corresponding to the user's selection.

カラーモニタ４０は、映像信号を取り込んで表示することが可能な市販のカラーモニタであり、電子スコープ１０で撮像され、カラープロセッサ２０で変換された映像信号を、出力（画面表示）する。   The color monitor 40 is a commercially available color monitor that can capture and display a video signal, and outputs (screen display) the video signal that is captured by the electronic scope 10 and converted by the color processor 20.

配光レンズ１２ａを介して白色光が生体組織に照射されると、生体組織で反射されたあるいは散乱した広帯域光が対物レンズ１１ａで集光され撮像素子１１ｂで受光される。配光レンズ１２ａを介して励起光が生体組織に照射されると、生体組織で反射されたあるいは散乱した狭帯域光と、励起された生体組織が発する自家蛍光の双方が対物レンズ１１ａに集光され撮像素子１１ｃで受光される。但し自家蛍光については微弱な光なので撮像結果には大きく影響しない。   When white light is irradiated onto the living tissue via the light distribution lens 12a, the broadband light reflected or scattered by the living tissue is collected by the objective lens 11a and received by the imaging device 11b. When the living tissue is irradiated with the excitation light through the light distribution lens 12a, both the narrow-band light reflected or scattered by the living tissue and the autofluorescence emitted from the excited living tissue are condensed on the objective lens 11a. The image sensor 11c receives the light. However, since autofluorescence is weak light, it does not greatly affect the imaging result.

生体組織に対する光の深さ方向の到達度合いは、その波長に依存する。すなわち短い波長の光は生体組織表面から浅い領域にまでしか光は到達せず、長い波長の光は生体組織表面から深い領域にまで光が到達する（図３参照）。   The degree of light reaching the living tissue in the depth direction depends on the wavelength. That is, light having a short wavelength reaches only a shallow region from the surface of the living tissue, and light having a long wavelength reaches the deep region from the surface of the living tissue (see FIG. 3).

波長帯域が広い放電ランプによる白色光は、生体組織表面から深い領域にまで光が到達し、到達した深さの範囲から反射、散乱した広帯域光によって生体組織表面から深い領域にある太い血管などを映し出すことが可能になる。そのため、生体組織の観察面の全体像を把握し易い。但し、白色光は比較的短い波長成分が多くは含まれないので、生体組織表面から浅い領域にある毛細血管などを映し出すことはできない。図４に、広帯域光による観察画像例を示す。   White light from a discharge lamp with a wide wavelength band reaches the deep region from the surface of the living tissue, and reflects from the reach depth range. It becomes possible to project. Therefore, it is easy to grasp the entire image of the observation surface of the living tissue. However, since white light does not include many relatively short wavelength components, it is not possible to project capillaries or the like in a shallow region from the surface of the living tissue. FIG. 4 shows an example of an observation image using broadband light.

波長が短く波長帯域が狭いレーザーによる青色レーザー光の励起光は、生体組織表面付近までしか光が到達せず、到達した深さの範囲から反射、散乱した狭帯域光によって粘膜表面の毛細血管などの微細構造を映し出すことが可能になる。そのため、生体組織表面から進行が始まる癌などを発見するのに役立つ。但し、生体組織表面から深い領域にある毛細血管よりも太い血管などを映し出すことはできない。図５に、図４と同じ被写体の観察面を撮像した狭帯域光による観察画像例を示す。   The blue laser beam excitation light from a laser with a short wavelength and narrow wavelength band reaches only near the surface of the living tissue, and capillary blood vessels on the mucous membrane surface due to the narrowband light reflected and scattered from the reach depth range. It is possible to project the fine structure of. Therefore, it is useful for finding cancers that begin to progress from the surface of living tissue. However, blood vessels that are thicker than capillaries in a deep region from the surface of the living tissue cannot be projected. FIG. 5 shows an example of an observation image using narrowband light obtained by imaging the same observation surface of the subject as in FIG.

従って、白色光の広帯域光による観察画像に、狭帯域光による観察画像を合成することで、被写体の観察面に関する鮮明な画像を得ることが可能になる。図６は、図４の広帯域光による観察画像に、図５の狭帯域光による観察画像を合成した画像例である。   Therefore, it is possible to obtain a clear image relating to the observation surface of the subject by combining the observation image based on the narrowband light with the observation image based on the broadband light of white light. FIG. 6 is an image example in which the observation image with narrowband light in FIG. 5 is combined with the observation image with broadband light in FIG. 4.

広帯域光による観察画像と狭帯域光による観察画像の合成については、第１画像信号と第２画像信号をそれぞれ第１、第２画像メモリ部２１ｃ、２１ｄに一時記録しこれらを合成することによって得られる。第２画像信号は、狭帯域光による観察画像そのままでもよいが、第２画像信号のうち毛細血管など画像を構成する輪郭線に関する情報だけを取り出して合成を行った方がより鮮明な画像を得ることが出来る。   The composition of the observation image using the broadband light and the observation image using the narrow-band light is obtained by temporarily recording the first image signal and the second image signal in the first and second image memory units 21c and 21d, respectively, and combining them. It is done. The second image signal may be an observation image as it is with narrow-band light, but a clearer image can be obtained by extracting only the information related to the contour lines constituting the image such as capillaries from the second image signal. I can do it.

毛細血管などの輪郭線に関する情報の取り出しは、狭帯域光による観察画像のうち高周波（高空間周波数）成分だけを取り出すことによって行う。具体的には、前段映像信号処理回路２１ａにおける輪郭強調処理で画像信号を構成する画素信号のそれぞれにおいて隣接画素との輝度情報の差分値、すなわちそれぞれの画素の輝度値と隣接画素の輝度の平均値との差分値を求める。各画素信号がこの差分値で構成される画像信号を第２画像信号として第２画像メモリ部２１ｄに一時記録し第１画像信号と合成する。   Extraction of information related to contour lines such as capillaries is performed by extracting only a high-frequency (high spatial frequency) component from an observation image using narrowband light. Specifically, in each of the pixel signals constituting the image signal by the edge enhancement processing in the preceding stage video signal processing circuit 21a, the difference value of the luminance information with the adjacent pixel, that is, the average of the luminance value of each pixel and the luminance of the adjacent pixel The difference value from the value is obtained. An image signal in which each pixel signal is composed of the difference value is temporarily recorded in the second image memory unit 21d as a second image signal and synthesized with the first image signal.

これらの手順を図７のフローチャートで説明する。ステップＳ１１で内視鏡操作が開始されると、ステップＳ１２で第１シャッタ３０ａがオープン状態にされる。このとき第２シャッタ３０ｂはクローズ状態である。ステップＳ１３で第１光源部２６から白色光を観察面に向かって照射する。ステップＳ１４で、照射された白色光の反射による広帯域光を撮像し、第１画像信号を通常観察画像として第１メモリ２１ｃに一時記録する。ステップＳ１５で、第１シャッタ３０ａをクローズ状態にし、ステップＳ１６で、第２シャッタ３０ｂをオープン状態にする。ステップＳ１７で、第２光源部２７から青色レーザー光の励起光を観察面に向かって照射する。ステップＳ１８で、照射された励起光の反射による狭帯域光を撮像し、狭帯域光画像として第２メモリ２１ｄに一時記録する。このとき狭帯域光画像として一時記録するのは、輪郭線に関する情報を強調した第２画像信号である。ステップＳ１９で、第２シャッタ３０ｂをクローズ状態にする。ステップＳ２０で、第１、第２画像メモリ２１ｃ、２１ｄに一時記録された第１画像信号及び第２画像信号を合成する。ステップＳ２１で、合成した画像信号を映像信号に変換してカラーモニタ４０に表示する。ステップＳ２２で、観察を継続するか否かすなわち映像信号処理を継続させるか否かを判断する。観察を継続する場合は、ステップＳ１２に戻って次のフレームの撮像手順に入る。観察を継続せず終了する場合は、ステップＳ２３で終了する。   These procedures will be described with reference to the flowchart of FIG. When the endoscope operation is started in step S11, the first shutter 30a is opened in step S12. At this time, the second shutter 30b is in a closed state. In step S13, white light is emitted from the first light source unit 26 toward the observation surface. In step S14, broadband light resulting from reflection of the irradiated white light is imaged, and the first image signal is temporarily recorded in the first memory 21c as a normal observation image. In step S15, the first shutter 30a is closed, and in step S16, the second shutter 30b is opened. In step S17, excitation light of blue laser light is emitted from the second light source unit 27 toward the observation surface. In step S18, the narrowband light resulting from the reflection of the irradiated excitation light is imaged and temporarily recorded in the second memory 21d as a narrowband light image. At this time, what is temporarily recorded as a narrow-band optical image is the second image signal in which information about the contour line is emphasized. In step S19, the second shutter 30b is closed. In step S20, the first image signal and the second image signal temporarily recorded in the first and second image memories 21c and 21d are synthesized. In step S21, the combined image signal is converted into a video signal and displayed on the color monitor 40. In step S22, it is determined whether or not to continue observation, that is, whether or not to continue video signal processing. When continuing observation, it returns to step S12 and starts the imaging procedure of the next frame. When ending without continuing observation, the process ends in step S23.

なお、生体組織に照射させる光の光源を白色光と励起光のいずれかに切り替える光源切り替え部３０は、第１、第２シャッタ３０ａ、３０ｂを用いるものとして説明したが、これは放電ランプのようにオンオフ信号により瞬時に点灯消灯が行えないものの場合に有効である。白色光の光源をＬＥＤなど瞬時の点灯消灯が行えるものであれば、第１シャッタ３０ａを使用しなくてもよく、光源切り替え部３０は、励起光を発する第２光源部２７と白色光を発するＬＥＤなどの光源とを交互にオンオフ切り替え制御ができる機能があればよい。   Note that the light source switching unit 30 that switches the light source for irradiating the living tissue to either white light or excitation light has been described as using the first and second shutters 30a and 30b, but this is like a discharge lamp. This is effective when the light cannot be turned on and off instantaneously by an on / off signal. If the white light source can be turned on and off instantaneously, such as an LED, the first shutter 30a may not be used, and the light source switching unit 30 emits white light with the second light source unit 27 that emits excitation light. It is only necessary to have a function capable of performing on / off switching control alternately with a light source such as an LED.

また、第１、第２画像信号を一時記録するメモリとして第１、第２画像メモリ部２１ｃ、２１ｄとを有する形態を説明したが、先に照射する光に対応した画像信号（本実施形態では第１画像信号に相当）だけ一時記録し、後で照射する光に対応した画像信号（本実施形態では第２画像信号に相当）は一時記録せず、直接後段映像信号処理回路２１ｅに転送して先に照射する光に対応した画像信号と合成する形態であってもよい。   Moreover, although the form which has the 1st, 2nd image memory part 21c, 21d as a memory which records a 1st, 2nd image signal temporarily was demonstrated, the image signal (in this embodiment) corresponding to the light irradiated previously. (Corresponding to the first image signal) is temporarily recorded, and the image signal corresponding to the light to be irradiated later (corresponding to the second image signal in this embodiment) is not temporarily recorded, but directly transferred to the subsequent video signal processing circuit 21e. Alternatively, it may be combined with an image signal corresponding to the previously irradiated light.

一般的なＣＣＤにおけるフィルタの分光特性と、青色レーザー光の波長帯域をグラフで示す。A spectral characteristic of a filter in a general CCD and a wavelength band of blue laser light are shown in a graph. 内視鏡装置の構成図を示す。The block diagram of an endoscope apparatus is shown. 照射する光の波長と、光の到達する生体組織表面から深さの関係を示す。The relationship between the wavelength of the irradiated light and the depth from the surface of the living tissue to which the light reaches is shown. 白色光照射による生体組織表面から深い領域を撮像した画像例を示す。The example of an image which imaged the deep area | region from the biological tissue surface by white light irradiation is shown. 励起光照射による生体組織表面から浅い領域を撮像した画像例を示す。The example of an image which imaged the shallow area | region from the biological tissue surface by excitation light irradiation is shown. 白色光照射による画像例と、励起光照射による画像例の合成した画像例を示す。An image example in which an image example by white light irradiation and an image example by excitation light irradiation are combined is shown. 白色光、励起光照射による２つの画像を合成する手順のフローチャートを示す。The flowchart of the procedure which synthesize | combines two images by white light and excitation light irradiation is shown.

符号の説明Explanation of symbols

１０ 電子スコープ
１１ 撮像部
１２ 照明部
２０ カラープロセッサ
２１ 映像信号処理部
２４ 制御回路
２６ 第１光源部
２７ 第２光源部
３０ 光源切り替え部
４０ カラーモニタ

DESCRIPTION OF SYMBOLS 10 Electronic scope 11 Imaging part 12 Illumination part 20 Color processor 21 Video signal processing part 24 Control circuit 26 1st light source part 27 2nd light source part 30 Light source switching part 40 Color monitor

Claims (5)

白色光を照射する第１光源部と、
前記白色光よりも実質的に波長が短く且つ前記白色光よりも波長帯域が狭い光を照射する第２光源部と、
前記第１光源部及び前記第２光源部が照射した光のうち、いずれか一方を観察面に照射する光源切り替え部と、
前記第２光源部が照射した光を用いて撮像した狭帯域光画像信号を構成する画素信号のそれぞれにおいて、それぞれの画素の輝度値と隣接画素の輝度値の平均値との差分値を求め、前記差分値で構成される画像信号を第２画像信号として出力する映像信号処理部と、
前記第１光源部が照射した白色光を用いて撮像した第１画像信号と前記第２画像信号とのうち先に得られた画像信号を一時記録する第１画像メモリ部と、
前記第２画像信号を前記第１画像信号と合成する映像信号合成部とを備え、
前記光源切り替え部は、第１、第２シャッタ、及びハーフミラーを有し、
前記第１シャッタは、オープン状態の時に前記第１光源部からの光を前記ハーフミラーに到達させ、クローズ状態の時に前記第１光源部からの光を遮光し、
前記第２シャッタは、オープン状態の時に前記第２光源部からの光を前記ハーフミラーに到達させ、クローズ状態の時に前記第２光源部からの光を遮光し、
前記第１光源部からの光と、前記第２光源部からの光のいずれか一方は、前記ハーフミラーを透過し、他方は、前記ハーフミラーを反射し、
前記第１光源部からの光と、前記第２光源部からの光は、前記ハーフミラーの同じ側から出射して、前記観察面に照射されることを特徴とする内視鏡装置。 A first light source that emits white light;
A second light source unit that emits light having a wavelength that is substantially shorter than that of the white light and a wavelength band that is narrower than that of the white light ;
One of the first light source unit and the light which the second light source unit irradiates a light source switching section for irradiating the observation surface either,
In each of the pixel signals constituting the narrowband light image signal imaged using the light emitted by the second light source unit, a difference value between the luminance value of each pixel and the average value of the luminance values of adjacent pixels is obtained, A video signal processing unit that outputs an image signal composed of the difference values as a second image signal;
A first image memory unit that temporarily records an image signal obtained first of the first image signal and the second image signal captured using white light emitted by the first light source unit ;
A video signal combining unit that combines the second image signal with the first image signal ;
The light source switching unit includes first and second shutters and a half mirror.
The first shutter causes the light from the first light source unit to reach the half mirror when in the open state, and blocks the light from the first light source unit when in the closed state,
The second shutter causes the light from the second light source unit to reach the half mirror when in the open state, and blocks the light from the second light source unit when in the closed state,
Either one of the light from the first light source unit and the light from the second light source unit transmits the half mirror, and the other reflects the half mirror,
The endoscope apparatus according to claim 1, wherein the light from the first light source unit and the light from the second light source unit are emitted from the same side of the half mirror and irradiated on the observation surface. 前記第１、第２画像信号のうち後に照射して得られた画像信号を一時記録する第２画像メモリ部をさらに備えた請求項１に記載の内視鏡装置。   The endoscope apparatus according to claim 1, further comprising a second image memory unit that temporarily records an image signal obtained by subsequent irradiation of the first and second image signals. 前記第１光源部は、放電ランプによる白色光源を有することを特徴とする請求項１に記載の内視鏡装置。   The endoscope apparatus according to claim 1, wherein the first light source unit includes a white light source using a discharge lamp. 前記第２光源部は、レーザーによる青色光源を有することを特徴とする請求項１に記載の内視鏡装置。   The endoscope apparatus according to claim 1, wherein the second light source unit includes a blue light source using a laser. 前記第２光源部が発する光の波長帯域は、４００ｎｍから４２０ｎｍであることを特徴とする請求項１に記載の内視鏡装置。   The endoscope apparatus according to claim 1, wherein a wavelength band of light emitted from the second light source unit is 400 nm to 420 nm.
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