JPH0723265A - Image pickup device - Google Patents
Image pickup deviceInfo
- Publication number
- JPH0723265A JPH0723265A JP5163616A JP16361693A JPH0723265A JP H0723265 A JPH0723265 A JP H0723265A JP 5163616 A JP5163616 A JP 5163616A JP 16361693 A JP16361693 A JP 16361693A JP H0723265 A JPH0723265 A JP H0723265A
- Authority
- JP
- Japan
- Prior art keywords
- signal
- ccd
- high frequency
- treatment
- frequency current
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
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- Endoscopes (AREA)
Abstract
Description
【0001】[0001]
【産業上の利用分野】本発明は撮像装置に係り、特に電
子シャッタ動作可能な固体撮像素子を有し、かつ固体撮
像素子のノイズ信号となる高周波電流やレーザ光等の処
置用信号を出力する処置機器と併用される撮像装置に関
する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an image pickup device, and more particularly to a solid-state image pickup device capable of operating an electronic shutter and outputting a treatment signal such as a high-frequency current or a laser beam which is a noise signal of the solid-state image pickup device. The present invention relates to an imaging device used together with a treatment device.
【0002】[0002]
【従来の技術】この種の撮像装置としては、高周波焼灼
電源装置やYAGレーザ装置等と併用される電子内視鏡
装置がある。一般に、電子内視鏡の挿入部先端には撮像
レンズ及び固体撮像素子(CCD)等が設けられてお
り、観察像は撮像レンズを介してCCDに結像され、こ
こで光電変換される。光電変換された観察像を示す電気
信号は、プロセッサで適宜信号処理されたのちモニタT
Vに出力される。これによりモニタTVに観察像を表示
させることができる。2. Description of the Related Art As an image pickup apparatus of this type, there is an electronic endoscope apparatus used together with a high frequency ablation power supply apparatus, a YAG laser apparatus and the like. Generally, an imaging lens, a solid-state imaging device (CCD), and the like are provided at the tip of the insertion portion of the electronic endoscope, and an observation image is formed on the CCD through the imaging lens and photoelectrically converted there. The electric signal showing the observed image that has been photoelectrically converted is subjected to appropriate signal processing by the processor, and then the monitor T
Output to V. Thereby, the observation image can be displayed on the monitor TV.
【0003】一方、従来から上記モニタTVに映し出さ
れた画像を見ながら、電子内視鏡の処置具挿通チャンネ
ルに高周波止血具、高周波スネア、高周波ナイフ等の高
周波処置具を挿入し、高周波焼灼電源装置から高周波処
置具に高周波電流を流することにより患部の止血/カッ
ト等の治療が行われている。例えば、止血治療をする場
合には、高周波焼灼電源装置から高周波止血具に300
KHz〜5MHz の範囲の高周波電流を間欠的に流すよ
うにしている(図4参照)On the other hand, while observing the image displayed on the monitor TV, a high-frequency treatment tool such as a high-frequency hemostat, a high-frequency snare, a high-frequency knife or the like is inserted into the treatment instrument insertion channel of the electronic endoscope, and a high-frequency cautery power supply is used. Treatment such as hemostasis / cutting of an affected area is performed by applying a high-frequency current from the device to a high-frequency treatment tool. For example, when hemostasis treatment is performed, a high-frequency hemostatic device is connected to a high-frequency hemostatic device at 300 times.
A high-frequency current in the range of KHz to 5 MHz is made to flow intermittently (see FIG. 4).
【0004】[0004]
【発明が解決しようとする課題】しかしながら、止血治
療中に高周波止血具の先端の導線部及び患部を流れる高
周波電流による電磁波のエネルギがCCDに加わり、C
CD出力信号にノイズ信号として重畳されるため、モニ
タTVの画像が著しく低下するという問題があった。However, during the hemostatic treatment, the energy of the electromagnetic waves due to the high-frequency current flowing through the conducting wire at the tip of the high-frequency hemostatic device and the affected area is added to the CCD, and C
Since it is superimposed on the CD output signal as a noise signal, there is a problem that the image on the monitor TV is significantly deteriorated.
【0005】従来、これを防ぐために挿入部先端や、C
CDとその周辺回路の電磁シールドを強化したり、ノイ
ズ対策用コイル類を付加したりしていたが、このような
対策は、挿入部先端の太さを増大させることになり、患
者の苦痛を少なくするためのスコープ先端の細径化傾向
に逆行することになる。一方、高周波電流によるノイズ
が映像信号に重畳されても、画質に影響しないように映
像信号の垂直同期信号に同期して高周波電流を流すよう
にした装置が提案されている(特開昭59−69069
号公報)。Conventionally, in order to prevent this, the tip of the insertion portion or C
Although the electromagnetic shield of the CD and its peripheral circuits has been strengthened and noise countermeasure coils have been added, such countermeasures increase the thickness of the tip of the insertion portion and cause patient distress. It goes against the tendency of the tip diameter of the scope to be reduced in order to reduce the number. On the other hand, a device has been proposed in which a high frequency current is passed in synchronization with a vertical synchronizing signal of a video signal so that the image quality is not affected even when noise due to the high frequency current is superimposed on the video signal (Japanese Patent Laid-Open No. 59-59-59). 69069
Issue).
【0006】しかしながら、この場合には垂直同期信号
の期間が短いため、この期間に出力される高周波電流の
みでは有効な治療ができないという問題がある。また、
映像信号に重畳されたノイズが後段の信号処理において
悪影響を及ぼすという問題もある。本発明はこのような
事情に鑑みてなされたもので、固体撮像素子に対してノ
イズ信号となる高周波電流やレーザ光等が発せられて
も、そのノイズ信号が固体撮像素子の出力信号に重畳さ
れないようにすることができ、これにより高周波電流や
レーザ光等を用いた処置中にも良好な画像を見ることが
できる撮像装置を提供することを目的とする。However, in this case, since the period of the vertical synchronizing signal is short, there is a problem that effective treatment cannot be performed only with the high frequency current output during this period. Also,
There is also a problem that noise superimposed on a video signal adversely affects signal processing in the subsequent stage. The present invention has been made in view of such circumstances, and even if a high-frequency current or a laser beam that becomes a noise signal is emitted to the solid-state image sensor, the noise signal is not superimposed on the output signal of the solid-state image sensor. Therefore, it is an object of the present invention to provide an image pickup apparatus capable of viewing a good image even during treatment using high-frequency current, laser light, or the like.
【0007】[0007]
【課題を解決するための手段】本発明は前記目的を達成
するために、電子シャッタ動作可能な固体撮像素子を有
し、該固体撮像素子のノイズ信号となる処置用信号を出
力する処置機器と併用される撮像装置において、電子シ
ャッタ動作時に前記固体撮像素子に蓄積される不要電荷
の蓄積期間を示す信号を出力する手段と、前記不要電荷
の蓄積期間を示す信号に基づいて該不要電荷の蓄積期間
中のみに前記処置機器から処置用信号を出力させる手段
と、備えたことを特徴としている。In order to achieve the above object, the present invention provides a treatment device having a solid-state image pickup device capable of operating an electronic shutter, and outputting a treatment signal which is a noise signal of the solid-state image pickup device. In an image pickup device used together, means for outputting a signal indicating a storage period of unnecessary charges accumulated in the solid-state image sensor during electronic shutter operation, and accumulation of the unnecessary charges based on the signal indicating the accumulation period of the unnecessary charges It is characterized in that it is provided with means for outputting a treatment signal from the treatment device only during the period.
【0008】[0008]
【作用】本発明は電子シャッタ動作可能な固体撮像素子
を使用し、電子シャッタ動作時に固体撮像素子において
蓄積される不要電荷の蓄積期間を利用して、処置用信号
を加えるようにしている。即ち、高周波電流又はレーザ
光等の処置用信号は固体撮像素子に対してノイズ信号と
なるが、これらのノイズ信号は固体撮像素子に不要電荷
として蓄積され、不要電荷とともに掃き出されるため、
固体撮像素子から出力される信号電荷中には含まれなく
なる。これにより、高周波電流やレーザ光等を用いた処
置中にも画質が低下することがなくなる。According to the present invention, the solid-state image pickup device capable of operating the electronic shutter is used, and the treatment signal is applied by utilizing the accumulation period of the unnecessary charges accumulated in the solid-state image pickup device during the operation of the electronic shutter. That is, a treatment signal such as a high-frequency current or laser light becomes a noise signal for the solid-state image sensor, but these noise signals are accumulated as unnecessary charges in the solid-state image sensor and are swept out together with the unnecessary charges.
It is not included in the signal charge output from the solid-state image sensor. As a result, the image quality does not deteriorate even during the treatment using the high-frequency current or the laser light.
【0009】[0009]
【実施例】以下添付図面に従って本発明に係る撮像装置
の好ましい実施例を詳説する。図1は本発明に係る撮像
装置が適用された電子内視鏡装置の一実施例を示すブロ
ック図であり、高周波焼灼電源装置を用いて止血治療を
行っている場合に関して示している。DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT A preferred embodiment of an image pickup apparatus according to the present invention will be described in detail below with reference to the accompanying drawings. FIG. 1 is a block diagram showing an embodiment of an electronic endoscope apparatus to which the image pickup apparatus according to the present invention is applied, and shows a case where hemostasis treatment is performed by using a high frequency ablation power supply apparatus.
【0010】この電子内視鏡装置の挿入部先端10に
は、撮像レンズ12及び電子シャッタ動作可能なCCD
14が配設されている。撮像レンズ12は、図示しない
ライトガイドを介して照明された患部16を撮像し、こ
れをCCD14の受光部に結像し、CCD14は入射光
を光電変換してCCD出力をプロセッサ18に出力す
る。At the tip 10 of the insertion portion of this electronic endoscope apparatus, an image pickup lens 12 and a CCD capable of operating an electronic shutter are provided.
14 are provided. The imaging lens 12 images the affected area 16 illuminated via a light guide (not shown), forms an image on the light receiving portion of the CCD 14, and the CCD 14 photoelectrically converts the incident light and outputs a CCD output to the processor 18.
【0011】プロセッサ18はCCD14を駆動制御す
る信号をCCD14に出力するとともに、CCD14か
ら出力されるCCD出力信号を入力し、これを信号処理
して映像信号を生成し、この映像信号をモニタTV20
に出力する。これにより、モニタTVには患部16の画
像が映し出される。一方、高周波止血具22は内視鏡の
処置具挿通チャンネル(図示せず)に挿入され、この高
周波止血具22の先端は、上記モニタTV20に映し出
された画像を見ながら挿入部先端10からは患部16に
向けて延出される。また、高周波止血具22は、高周波
焼灼電源装置24と電気的に接続されている。The processor 18 outputs a signal for driving and controlling the CCD 14 to the CCD 14, inputs the CCD output signal output from the CCD 14, processes the signal to generate a video signal, and the video signal is monitored by the monitor TV 20.
Output to. As a result, the image of the affected area 16 is displayed on the monitor TV. On the other hand, the high-frequency hemostat 22 is inserted into a treatment instrument insertion channel (not shown) of the endoscope, and the tip of the high-frequency hemostat 22 is seen from the tip 10 of the insertion portion while watching the image displayed on the monitor TV 20. It is extended toward the affected part 16. Further, the high-frequency hemostatic device 22 is electrically connected to the high-frequency cautery power supply device 24.
【0012】高周波焼灼電源装置24には、プロセッサ
18から止血/カットを許可する信号が加えられるとと
もに、フットスイッチ26から治療指令パルスが適宜加
えられるようになっており、高周波焼灼電源装置24は
これらの入力信号に基づいて止血又はカットの治療内容
に応じた高周波の止血/カット動作信号を高周波処置具
に出力する。尚、この高周波焼灼電源装置24から出力
される止血/カット動作信号の詳細については後述す
る。また、28は電極プレートである。The induction cautery power supply 24 is provided with a signal for permitting hemostasis / cutting from the processor 18, and a treatment command pulse is appropriately applied from the foot switch 26. A high frequency hemostatic / cut operation signal corresponding to the content of the hemostasis or cut treatment is output to the high frequency treatment instrument based on the input signal of. The details of the hemostasis / cut operation signal output from the high frequency ablation power supply device 24 will be described later. 28 is an electrode plate.
【0013】次に、上記構成の電子内視鏡装置の作用に
ついて図2に示すタイミングチャートを参照しながら説
明する。プロセッサ18は、垂直同期信号VD(図2
(A))を含む同期信号に基づいてCCD14を含む各
回路の同期をとって所要の信号処理を行うもので、CC
D14には転送ゲートパルスP1,P2 (図2(B)及び
(C))を含む各種の駆動パルスを出力する。図2
(B)は電子シャッタ未使用時のタイミングチャートで
あり、CCD14の光電変換素子に電荷蓄積される信号
電荷は、垂直同期信号VDに同期した1/60秒毎の転
送ゲートパルスP1 によってV−CCDに転送される。
尚、この転送によって光電変換素子はリセットされる。
また、V−CCDに転送された信号電荷は、1ラインず
つH−CCDに転送されてCCD出力信号として取り出
される。Next, the operation of the electronic endoscope apparatus having the above configuration will be described with reference to the timing chart shown in FIG. The processor 18 uses the vertical synchronization signal VD (see FIG.
(A)) is used to perform required signal processing by synchronizing each circuit including the CCD 14 based on a synchronizing signal including CC.
Various drive pulses including transfer gate pulses P 1 and P 2 (FIGS. 2B and 2C) are output to D14. Figure 2
(B) is a timing chart when the electronic shutter is not used, and the signal charge accumulated in the photoelectric conversion element of the CCD 14 is V- by the transfer gate pulse P 1 every 1/60 seconds synchronized with the vertical synchronization signal VD. Transferred to CCD.
The photoelectric conversion element is reset by this transfer.
The signal charges transferred to the V-CCD are transferred line by line to the H-CCD and taken out as a CCD output signal.
【0014】一方、図2(C)は電子シャッタ動作時の
タイミングチャートであり、CCD14の光電変換素子
に電荷蓄積される信号電荷は、上記と同様に転送ゲート
パルスP1,P2 によってV−CCDに転送されるが、転
送ゲートパルスP2 によってV−CCDに転送された信
号電荷(不要電荷)は、H−CCDとは逆の方向へ高速
転送され、掃出しドレインから全て排出される。On the other hand, FIG. 2C is a timing chart at the time of the electronic shutter operation. The signal charge accumulated in the photoelectric conversion element of the CCD 14 is V- by the transfer gate pulses P 1 and P 2 as in the above. The signal charges (unnecessary charges), which are transferred to the CCD but transferred to the V-CCD by the transfer gate pulse P 2 , are transferred at a high speed in a direction opposite to that of the H-CCD, and are all discharged from the sweep drain.
【0015】従って、転送ゲートパルスP2 からP1 ま
での期間が、CCD出力信号となる信号電荷の電荷蓄積
時間となり、この時間を調整することにより実質的な露
出時間が制御される。さて、プロセッサ18は上記不要
電荷が蓄積される期間のみONとなるパルスdを高周波
焼灼電源装置24に出力する(図2(D))。尚、プロ
セッサ18は、治療期間中を示す図示しないスイッチ入
力又は高周波焼灼電源装置24からの信号等に基づい
て、不要電荷の蓄積時間を強制的に所定時間に設定する
設定回路を有している。Therefore, the period from the transfer gate pulse P 2 to P 1 becomes the charge accumulation time of the signal charge which becomes the CCD output signal, and the substantial exposure time is controlled by adjusting this time. Now, the processor 18 outputs a pulse d to the high frequency ablation power supply device 24, which is turned on only during the period when the unnecessary charges are accumulated (FIG. 2D). The processor 18 has a setting circuit for forcibly setting the accumulation time of unnecessary charges to a predetermined time based on a switch input (not shown) indicating a treatment period or a signal from the high frequency ablation power supply 24. .
【0016】フットスイッチ26は足によって操作され
るもので、高周波焼灼電源装置24から止血/カット動
作信号を高周波処置具に出力させるときに押下され、そ
の押下期間だけONとなる治療指令パルスeを出力する
(図2(E))。高周波焼灼電源装置24は、上記プロ
セッサ18から加えられる不要電荷蓄積期間を示すパル
スdと治療指令パルスeとのアンド条件をとって出力制
御パルスfを生成する。そして、図4に示す従来の止血
動作時に出力され間欠的な高周波電流を、上記出力制御
パルスfによってゲート制御し、これにより図2(G)
に示す止血動作信号を高周波止血具22に出力する。The foot switch 26 is operated by a foot, and is pressed when a high frequency treatment device outputs a hemostatic / cutting operation signal to the high frequency treatment instrument. It is output (FIG. 2 (E)). The high frequency ablation power supply device 24 generates an output control pulse f by taking an AND condition between the pulse d indicating the unnecessary charge accumulation period added from the processor 18 and the treatment command pulse e. Then, the intermittent high-frequency current output during the conventional hemostatic operation shown in FIG. 4 is gate-controlled by the output control pulse f, so that FIG.
The hemostatic operation signal shown in is output to the high frequency hemostatic device 22.
【0017】このようにして止血動作信号が加えられた
高周波止血具22は、その先端の導線部等からノイズ信
号を発生し、このノイズ信号はCCD14に電荷蓄積さ
れるが、このノイズ信号は不要電荷とともに掃き出され
るため、CCD14からプロセッサ18に出力される信
号中には含まれなくなる。これにより、高周波電流を用
いた治療中にも画質が低下することがなくなる。The high-frequency hemostatic device 22 to which the hemostatic operation signal is added in this way generates a noise signal from the conductor portion at the tip thereof, and this noise signal is accumulated in the CCD 14, but this noise signal is unnecessary. It is not included in the signal output from the CCD 14 to the processor 18 because it is swept out together with the charges. As a result, the image quality does not deteriorate even during the treatment using the high frequency current.
【0018】図3はポリープ17を高周波スネア29に
よってカットする場合について示している。尚、図1に
示した止血時とは、高周波処置具のみが相違している。
ポリープ17を高周波スネア29によってカットする場
合には、高周波焼灼電源装置24の出力をカット用に切
り換える。尚、カット動作時には、連続的で、止血時よ
りも大きな高周波電流が生成される。FIG. 3 shows a case where the polyp 17 is cut by the high frequency snare 29. Note that only the high-frequency treatment tool is different from that at the time of hemostasis shown in FIG.
When the polyp 17 is cut by the high frequency snare 29, the output of the high frequency ablation power supply device 24 is switched for cutting. In addition, during the cutting operation, a high-frequency current that is continuous and larger than that during hemostasis is generated.
【0019】そして、このカット動作時に生成される高
周波電流は、止血動作時と同様に出力制御パルスfによ
ってゲート制御し、これにより図2(H)に示すカット
動作信号が高周波スネア29に出力される。尚、上記実
施例では、高周波焼灼電源装置24及び高周波止血具2
2、高周波スネア29等の高周波処置具を用いた場合に
ついて説明したが、これに限らず、レーザ治療装置を使
用する場合にも本発明は適用できる。The high-frequency current generated during the cutting operation is gate-controlled by the output control pulse f as in the hemostasis operation, so that the cutting operation signal shown in FIG. 2 (H) is output to the high-frequency snare 29. It In the above embodiment, the high frequency cautery power supply device 24 and the high frequency hemostatic device 2 are used.
2. The case of using a high-frequency treatment tool such as the high-frequency snare 29 has been described, but the present invention is not limited to this and the present invention can be applied to the case of using a laser treatment apparatus.
【0020】即ち、YAGレーザ光を処置具挿通チャン
ネルに挿通されるライトガイドを介して内視鏡の挿入部
先端から患部に照射する場合には、そのレーザ光の反射
光が撮像レンズ12を介して直接CCD14に入射し、
これがノイズとなる。従って、このようなレーザ治療装
置を使用する場合には、上記と同様に、出力制御パルス
fのONの期間だけレーザ光を、処置具挿通チャンネル
に挿通されるライトガイドに入射するように制御すれば
よい。That is, when the YAG laser light is applied to the affected area from the distal end of the insertion portion of the endoscope through the light guide inserted through the treatment instrument insertion channel, the reflected light of the laser light is passed through the imaging lens 12. Directly into the CCD 14,
This becomes noise. Therefore, when using such a laser treatment apparatus, it is possible to control the laser light to enter the light guide inserted through the treatment instrument insertion channel only during the ON period of the output control pulse f as in the above. Good.
【0021】更に、本発明は電子内視鏡装置に限らず、
例えば、溶接作業を行う機器等にも適用でき、要は固体
撮像素子からの信号に基づいて被写体をモニタTVに表
示し、その画像を見ながら作業を行うものであれば、如
何なるものにも適用できる。Further, the present invention is not limited to the electronic endoscope apparatus,
For example, it can be applied to equipment for welding work, and in short, it can be applied to any object as long as the subject is displayed on the monitor TV based on the signal from the solid-state image sensor and the work is performed while watching the image. it can.
【0022】[0022]
【発明の効果】以上説明したように本発明に係る撮像装
置によれば、電子シャッタ動作時に固体撮像素子におい
て蓄積される不要電荷の蓄積期間を利用し、その不要電
荷の蓄積期間のみに高周波電流又はレーザ光等を発する
ようにしたため、これらの高周波電流又はレーザ光等に
伴うノイズ信号が固体撮像素子の出力信号に重畳されな
いようにすることができ、これにより高周波電流やレー
ザ光等を用いた処置中にも良好な画像を見ることができ
る。As described above, according to the image pickup apparatus of the present invention, the accumulation period of the unnecessary charges accumulated in the solid-state image pickup device during the operation of the electronic shutter is utilized, and the high frequency current is generated only during the accumulation period of the unnecessary charges. Alternatively, since the laser light or the like is emitted, it is possible to prevent noise signals associated with these high-frequency current or laser light from being superimposed on the output signal of the solid-state imaging device, and thus high-frequency current or laser light is used. Good images can be seen during the procedure.
【図1】図1は本発明に係る撮像装置が適用された電子
内視鏡装置の一実施例を示す全体構成図である。FIG. 1 is an overall configuration diagram showing an embodiment of an electronic endoscope apparatus to which an image pickup apparatus according to the present invention is applied.
【図2】図2は図1の電子内視鏡装置の作用を説明する
ために用いたタイミングチャートである。FIG. 2 is a timing chart used for explaining the operation of the electronic endoscope apparatus of FIG.
【図3】図3は図1の電子内視鏡装置における処置具と
して高周波スネアを使用した場合の要部構成図である。3 is a configuration diagram of main parts when a high-frequency snare is used as a treatment tool in the electronic endoscope apparatus of FIG.
【図4】図4は従来の止血動作時に使用される高周波電
流の一例を示す波形図である。FIG. 4 is a waveform diagram showing an example of a high-frequency current used in a conventional hemostasis operation.
10…挿入部先端 12…撮像レンズ 14…CCD 16、17…患部 18…プロセッサ 20…モニタTV 22…高周波止血具 24…高周波焼灼電源装置 26…フットスイッチ 28…電極プレート 29…高周波スネア 10 ... Tip of insertion part 12 ... Imaging lens 14 ... CCD 16, 17 ... Affected part 18 ... Processor 20 ... Monitor TV 22 ... High frequency hemostatic device 24 ... Induction cauterization power supply device 26 ... Foot switch 28 ... Electrode plate 29 ... High frequency snare
Claims (2)
有し、該固体撮像素子のノイズ信号となる処置用信号を
出力する処置機器と併用される撮像装置において、 電子シャッタ動作時に前記固体撮像素子に蓄積される不
要電荷の蓄積期間を示す信号を出力する手段と、 前記不要電荷の蓄積期間を示す信号に基づいて該不要電
荷の蓄積期間中のみに前記処置機器から処置用信号を出
力させる手段と、 を備えたことを特徴とする撮像装置。1. An imaging device having a solid-state image sensor capable of operating an electronic shutter, which is used together with a treatment device for outputting a treatment signal which is a noise signal of the solid-state image sensor, wherein the solid-state image sensor is operated during the operation of the electronic shutter. Means for outputting a signal indicating the accumulation period of the unnecessary charges accumulated in, and means for outputting a treatment signal from the treatment device only during the accumulation period of the unnecessary charges based on the signal indicating the accumulation period of the unnecessary charges An image pickup device comprising:
体撮像素子における不要電荷の蓄積時間を強制的に所定
時間に設定する設定手段を有することを特徴とする請求
項1の撮像装置。2. The image pickup apparatus according to claim 1, further comprising setting means for forcibly setting an accumulation time of unnecessary charges in the solid-state image pickup device to a predetermined time during a treatment period by the treatment device.
Priority Applications (1)
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JP16361693A JP3339113B2 (en) | 1993-07-01 | 1993-07-01 | Imaging device |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP16361693A JP3339113B2 (en) | 1993-07-01 | 1993-07-01 | Imaging device |
Publications (2)
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JPH0723265A true JPH0723265A (en) | 1995-01-24 |
JP3339113B2 JP3339113B2 (en) | 2002-10-28 |
Family
ID=15777317
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JP16361693A Expired - Lifetime JP3339113B2 (en) | 1993-07-01 | 1993-07-01 | Imaging device |
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Cited By (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5917531A (en) * | 1996-02-13 | 1999-06-29 | Rohm Co., Ltd. | Thermal head and method of manufacturing the same |
JP2006130183A (en) * | 2004-11-09 | 2006-05-25 | Pentax Corp | Endoscope system |
JP2008125821A (en) * | 2006-11-21 | 2008-06-05 | Pentax Corp | Electronic endoscope apparatus |
EP2433556A1 (en) * | 2010-09-24 | 2012-03-28 | Fujifilm Corporation | Electronic endoscope system |
WO2013021780A1 (en) * | 2011-08-09 | 2013-02-14 | オリンパス株式会社 | Endoscopic apparatus |
JP2013506498A (en) * | 2009-09-30 | 2013-02-28 | ボストン サイエンティフィック サイムド,インコーポレイテッド | Systems and methods for imaging during medical procedures |
-
1993
- 1993-07-01 JP JP16361693A patent/JP3339113B2/en not_active Expired - Lifetime
Cited By (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5917531A (en) * | 1996-02-13 | 1999-06-29 | Rohm Co., Ltd. | Thermal head and method of manufacturing the same |
JP2006130183A (en) * | 2004-11-09 | 2006-05-25 | Pentax Corp | Endoscope system |
JP4648683B2 (en) * | 2004-11-09 | 2011-03-09 | Hoya株式会社 | Endoscope system |
JP2008125821A (en) * | 2006-11-21 | 2008-06-05 | Pentax Corp | Electronic endoscope apparatus |
JP2013506498A (en) * | 2009-09-30 | 2013-02-28 | ボストン サイエンティフィック サイムド,インコーポレイテッド | Systems and methods for imaging during medical procedures |
US8803962B2 (en) | 2009-09-30 | 2014-08-12 | Boston Scientific Scimed, Inc. | System and method for imaging during a medical procedure |
US9265408B2 (en) | 2009-09-30 | 2016-02-23 | Boston Scientific Scimed, Inc. | System and method for imaging during a medical procedure |
EP2433556A1 (en) * | 2010-09-24 | 2012-03-28 | Fujifilm Corporation | Electronic endoscope system |
WO2013021780A1 (en) * | 2011-08-09 | 2013-02-14 | オリンパス株式会社 | Endoscopic apparatus |
Also Published As
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JP3339113B2 (en) | 2002-10-28 |
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