JP2014130732A5 - - Google Patents
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- JP2014130732A5 JP2014130732A5 JP2012287757A JP2012287757A JP2014130732A5 JP 2014130732 A5 JP2014130732 A5 JP 2014130732A5 JP 2012287757 A JP2012287757 A JP 2012287757A JP 2012287757 A JP2012287757 A JP 2012287757A JP 2014130732 A5 JP2014130732 A5 JP 2014130732A5
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- 238000000605 extraction Methods 0.000 description 20
- 238000003384 imaging method Methods 0.000 description 2
- 238000001514 detection method Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
Description
本発明の放射線発生ユニットによれば、カソードヒーター電源の正極がカソードに接続され、引き出し電極電源の正極が引き出し電極に接続されており、カソードヒーター電源の負極と引き出し電極電源の負極が接続されている。 According to the radiation generating unit of the present invention, the positive electrode of the cathode heater power supply is connected to the cathode, the positive electrode of the extraction electrode power supply is connected to the extraction electrode, and the negative electrode of the cathode heater power supply and the negative electrode of the extraction electrode power supply are connected. Yes.
放射線発生管2は、図2で示すように、真空容器17内に、陰極となるカソード5と、カソード5の近傍に配置されるカソードヒーター4と、カソード5に対向して配置される陽極となる放射線発生ターゲット3とを備えている。図示される放射線発生ターゲット3は、真空容器17の壁面の一部を構成するように配置されている。しかし、真空容器17の内部と外部に連通して筒状の放射線遮蔽部材(図示されていない)を配置し、この放射線遮蔽部材の内部空間を横断して、真空容器17内を密閉できるように放射線発生ターゲット3を配置した構成とすることもできる。また、真空容器17内のカソード5と放射線発生ターゲット3の間に、引き出し電極6とレンズ電極7をも備えている。引き出し電極6はカソード5側に設けられ、レンズ電極7は放射線発生ターゲット3と引き出し電極7の間に設けられている。さらに、放射線発生管2を駆動するための電源類が制御回路30の内部に設置されており、この実施形態では図1および図2で示すように、放射線発生ターゲット3が一の駆動電源13と他の駆動電源12とを介してカソード5と接続されている。また、レンズ電極電源11の正極はレンズ電極7に接続され、レンズ電極電源11の負極は駆動電源12の負極に接続されている。引き出し電極6は引き出し電極電源10の正極と接続されている。さらに、カソードヒーター4は、カソードヒーター電源9と接続されている。 As shown in FIG. 2, the radiation generating tube 2 includes a cathode 5 serving as a cathode, a cathode heater 4 disposed in the vicinity of the cathode 5, and an anode disposed so as to face the cathode 5. The radiation generation target 3 is provided. The illustrated radiation generation target 3 is disposed so as to constitute a part of the wall surface of the vacuum vessel 17. However, a cylindrical radiation shielding member (not shown) is provided in communication with the inside and outside of the vacuum vessel 17 so that the inside of the vacuum vessel 17 can be sealed across the internal space of the radiation shielding member. It can also be set as the structure which has arrange | positioned the radiation generation target 3. FIG. Further, an extraction electrode 6 and a lens electrode 7 are also provided between the cathode 5 in the vacuum container 17 and the radiation generation target 3. The extraction electrode 6 is provided on the cathode 5 side, and the lens electrode 7 is provided between the radiation generation target 3 and the extraction electrode 7. Further, power sources for driving the radiation generating tube 2 are installed inside the control circuit 30. In this embodiment, as shown in FIGS. 1 and 2, the radiation generating target 3 is a single driving power source 13 and It is connected to the cathode 5 via another driving power source 12. The positive electrode of the lens electrode power source 11 is connected to the lens electrode 7, the negative lens electrode power source 11 is connected to the negative electrode of the driving power source 12. The extraction electrode 6 is connected to the positive electrode of the extraction electrode power supply 10. Further, the cathode heater 4 is connected to a cathode heater power source 9.
本発明の放射線発生ユニット1では、図2で示すように、引き出し電極電源10の負極がカソードヒーター電源9の負極に接続され、カソードヒーター電源9の正極がカソード5側に接続されている。本発明は、これらにより、カソードヒーター電源9と引き出し電極電源10が直列に接続されていることに特徴がある。 In the radiation generating unit 1 of the present invention, as shown in FIG. 2, the negative electrode of the extraction electrode power supply 10 is connected to the negative electrode of the cathode heater power supply 9, and the positive electrode of the cathode heater power supply 9 is connected to the cathode 5 side. . Thus, the present invention is characterized in that the cathode heater power source 9 and the extraction electrode power source 10 are connected in series.
(2)放射線放射オンの場合
(1)で述べたようにカソードヒーター電源9は、常にオンにして一定の電圧を維持しているが、これに対して、引き出し電極電源10の出力はカソードヒーター電源9の維持電圧よりも大きい所定の正の電圧に設定される。本発明において、カソードヒーター電源9の正極は、カソード5側、負極は引き出し電極6側に接続されているために、引き出し電極6には、V3 +(V1−V2)の電圧が印加され、引き出し電極6のカソード5に対する電位は正となる。
(2) When radiation emission is on As described in (1), the cathode heater power supply 9 is always turned on to maintain a constant voltage, whereas the output of the extraction electrode power supply 10 is the cathode heater. It is set to a predetermined positive voltage that is higher than the sustain voltage of the power source 9. In the present invention, the cathode heater power supply 9 has a positive electrode connected to the cathode 5 side and a negative electrode connected to the extraction electrode 6 side. Therefore, a voltage of V 3 + (V 1 −V 2 ) is applied to the extraction electrode 6. Thus, the potential of the extraction electrode 6 with respect to the cathode 5 becomes positive.
つまり、引き出し電極電位[V3 +(V1−V2)]>カソード電位(V1)の関係が成り立ち、カソード5から熱電子を十分に引き出すことができる。よって、放射線発生ターゲット3に衝突する電子を十分確保することができる。カソード5から引き出された十分な量の熱電子は、放射線発生ターゲット3に衝突し、十分な放射線を発生させることができ、放射線照射を確実に行うことができる。 That is, the relationship of extraction electrode potential [V 3 + (V 1 −V 2 )]> cathode potential (V 1 ) is established, and the thermal electrons can be sufficiently extracted from the cathode 5. Therefore, it is possible to secure sufficient electrons that collide with the radiation generation target 3. A sufficient amount of thermionic electrons extracted from the cathode 5 can collide with the radiation generation target 3 to generate sufficient radiation, and radiation irradiation can be reliably performed.
例えば、放射線照射オン時の引き出し電極電位は、V3 +(V1−V2)で表される。つまり上記数値を代入すると、120V+(−50kV−5V)=−49885Vであり、この電圧が引き出し電極6に印加される。また、カソード電位はV1がそのまま印加されるため、−50000Vが印加される。したがって、引き出し電極電位(−49885V)>カソード電位(−50000V)の関係が成り立つ。よって、放射線照射オンの状態で線量を測定したところ十分な放射線量が得られる構成となる。 For example, the extraction electrode potential when radiation irradiation is on is represented by V 3 + (V 1 −V 2 ). That is, when the above numerical values are substituted, 120V + (−50 kV−5 V) = − 49885 V, and this voltage is applied to the extraction electrode 6. Further, since V 1 is applied as it is, the cathode potential is −50000V. Therefore, the relationship of extraction electrode potential ( −49885 V)> cathode potential ( −50000 V) is established. Therefore, when the dose is measured in a state where radiation irradiation is on, a sufficient radiation dose can be obtained.
また、放射線照射オン時には、引き出し電極電位[V3 +(V1−V2)]>カソード電位(V1)の関係が成り立ち、カソード5から熱電子を十分に引き出すことができる。 In addition, when radiation irradiation is on, the relationship of extraction electrode potential [V 3 + (V 1 −V 2 )]> cathode potential (V 1 ) is established, and thermal electrons can be sufficiently extracted from the cathode 5.
また、放射線照射オン時には、引き出し電極電位[V3 +(−V2)]>カソード電位(0V)の関係が成り立ち、カソード5から熱電子を十分に引き出すことができる。 In addition, when radiation irradiation is on, the relationship of extraction electrode potential [V 3 + (− V 2 )]> cathode potential (0 V) is established, and thermoelectrons can be sufficiently extracted from the cathode 5.
〔放射線撮影システムの一実施形態〕
図9は本発明の放射線撮影システムの構成図である。システム制御装置33は、放射線発生ユニット1と放射線検出装置31とを連携制御する。電圧制御部30は、システム制御装置33による制御の下に、放射線発生管2に各種の制御信号を出力する。制御信号により、放射線発生ユニット1から放出される放射線の放出状態が制御される。放射線発生ユニット1から放出された放射線は、被検体35を透過して検出器31で検出される。検出器31は、検出した放射線を画像信号に変換して信号処理部32に出力する。信号処理部32は、システム制御装置33による制御の下に、画像信号に所定の信号処理を施し、処理された画像信号をシステム制御装置33に出力する。システム制御装置3は、処理された画像信号に基いて、表示装置34に画像を表示させるための表示信号を表示装置34に出力する。表示装置34は、表示信号に基く画像を、被検体35の撮影画像としてスクリーンに表示する。これにより、照射される放射線の斑を低減させることが可能となる。
[One Embodiment of Radiation Imaging System]
FIG. 9 is a block diagram of the radiation imaging system of the present invention. The system control device 33 controls the radiation generation unit 1 and the radiation detection device 31 in a coordinated manner. The voltage control unit 30 outputs various control signals to the radiation generating tube 2 under the control of the system control device 33. The emission state of the radiation emitted from the radiation generation unit 1 is controlled by the control signal. The radiation emitted from the radiation generating unit 1 passes through the subject 35 and is detected by the detector 31. The detector 31 converts the detected radiation into an image signal and outputs the image signal to the signal processing unit 32. The signal processing unit 32 performs predetermined signal processing on the image signal under the control of the system control device 33 and outputs the processed image signal to the system control device 33. The system control device 3 outputs a display signal for displaying an image on the display device 34 to the display device 34 based on the processed image signal. The display device 34 displays an image based on the display signal on the screen as a captured image of the subject 35. Thereby, it becomes possible to reduce the spot of the irradiated radiation.
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JP2012287757A JP6168770B2 (en) | 2012-12-28 | 2012-12-28 | Radiation generation unit and radiography system |
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JP2012287757A JP6168770B2 (en) | 2012-12-28 | 2012-12-28 | Radiation generation unit and radiography system |
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JP2014130732A JP2014130732A (en) | 2014-07-10 |
JP2014130732A5 true JP2014130732A5 (en) | 2016-02-18 |
JP6168770B2 JP6168770B2 (en) | 2017-07-26 |
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CN1279795C (en) * | 2001-08-29 | 2006-10-11 | 株式会社东芝 | X-ray generator |
JP4619176B2 (en) * | 2005-03-31 | 2011-01-26 | 株式会社日立メディコ | Microfocus X-ray tube |
JP4984234B2 (en) * | 2007-03-30 | 2012-07-25 | 国立大学法人長岡技術科学大学 | X-ray generator |
JP2012109186A (en) * | 2010-11-19 | 2012-06-07 | Toshiba Corp | Power supply unit and x-ray device |
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