JPH06196292A - X-ray high-voltage device - Google Patents
X-ray high-voltage deviceInfo
- Publication number
- JPH06196292A JPH06196292A JP10219993A JP10219993A JPH06196292A JP H06196292 A JPH06196292 A JP H06196292A JP 10219993 A JP10219993 A JP 10219993A JP 10219993 A JP10219993 A JP 10219993A JP H06196292 A JPH06196292 A JP H06196292A
- Authority
- JP
- Japan
- Prior art keywords
- voltage
- circuit
- ray
- charging
- inverter
- 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.)
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- X-Ray Techniques (AREA)
Abstract
Description
【０００１】[0001]
【産業上の利用分野】本発明は、小容量電源設備のもと
で使用されるＸ線高電圧装置、特に、車載用に適したイ
ンバータ式Ｘ線高電圧装置に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an X-ray high-voltage device used under a small-capacity power supply facility, and more particularly to an inverter type X-ray high-voltage device suitable for vehicle installation.
【０００２】[0002]
【従来の技術】従来より車載用のＸ線高電圧装置として
一般に、コンデンサ方式Ｘ線高電圧装置が使用されてお
り、Ｘ線管電圧（以下単に管電圧という）は高圧コンデ
ンサの充電電圧により決まり、管電圧の制御は、高圧コ
ンデンサの充電電圧を可変に制御することにより行なわ
れる。大電力制御用のパワートランジスタ等の半導体素
子の発達により、交流電源電圧を整流平滑して大容量コ
ンデンサを充電することで直流電圧に変換し、インバー
タにより高周波の交流電圧を得て、高圧トランスに加え
るインバータ方式のＸ線高電圧装置が、近年用いられる
ようになってきた。2. Description of the Related Art Conventionally, a capacitor type X-ray high voltage device has been generally used as an on-vehicle X-ray high voltage device, and an X-ray tube voltage (hereinafter simply referred to as a tube voltage) is determined by a charging voltage of a high voltage capacitor. The tube voltage is controlled by variably controlling the charging voltage of the high voltage capacitor. With the development of semiconductor devices such as power transistors for high power control, the AC power supply voltage is rectified and smoothed, and a large capacity capacitor is charged to convert it to a DC voltage. Inverter-type X-ray high-voltage devices to be added have been used in recent years.
【０００３】この種インバータ式Ｘ線高電圧装置におい
て、管電圧の制御のほとんどは、負荷の大小に応じて高
圧トランスの一次側に介在する大容量コンデンサの充電
電圧をチョッパ等のスイッチングレギュレータを用いて
制御し、その後、インバータを固定周波数で動かすもの
である。In this type of inverter type X-ray high voltage apparatus, most of the tube voltage control uses a switching regulator such as a chopper to charge the charging voltage of a large capacity capacitor located on the primary side of the high voltage transformer according to the size of the load. Control is performed, and then the inverter is operated at a fixed frequency.
【０００４】図３は従来のインバータ式Ｘ線高電圧装置
の構成を示す回路図である。図において、１′は交流電
源、２は電源トランス、３は電源トランス２の一次側回
路に挿入されたソリッドステートリレ（トライアッ
ク）、４は整流器、５は整流回路の出力端に接続された
充電コンデンサ、６は充電コンデンサ５の充電電圧を検
出する充電電圧検出抵抗、７は充電電圧制御回路、８′
は図示しないインバータ駆動回路で一定の固定周波数で
駆動されるインバータ回路、９はチョッパを構成するス
イッチング素子（トランジスタ）、１０はスイッチング
素子９のスイッチング時のノイズ吸収用インダクタン
ス、１１はスイッチング素子９の保護用ダイオード、１
２は平滑コンデンサ、１３は高圧トランス、１４は高圧
トランス１３の二次側に接続された高圧整流器、１５は
管電圧検出抵抗、１６は高圧平滑コンデンサ、１７はＸ
線管、１８は管電圧制御回路、１９はチョッパ制御回路
である。FIG. 3 is a circuit diagram showing the configuration of a conventional inverter type X-ray high voltage device. In the figure, 1'is an AC power source, 2 is a power transformer, 3 is a solid state relay (triac) inserted in the primary side circuit of the power transformer 2, 4 is a rectifier, 5 is charging connected to the output end of the rectifier circuit. A capacitor, 6 is a charging voltage detecting resistor for detecting the charging voltage of the charging capacitor 5, 7 is a charging voltage control circuit, and 8 '.
Is an inverter circuit driven at a constant fixed frequency by an inverter drive circuit (not shown), 9 is a switching element (transistor) that constitutes a chopper, 10 is a noise absorbing inductance when the switching element 9 is switching, and 11 is a switching element 9. Protective diode, 1
2 is a smoothing capacitor, 13 is a high voltage transformer, 14 is a high voltage rectifier connected to the secondary side of the high voltage transformer 13, 15 is a tube voltage detection resistor, 16 is a high voltage smoothing capacitor, 17 is X
A line tube, 18 is a tube voltage control circuit, and 19 is a chopper control circuit.
【０００５】上記構成において、高圧トランス１３の一
次側に介在するコンデンサ５の充電電圧は検出抵抗６で
検出され、コンデンサ５の充電電圧が所定値になるよう
に充電電圧制御回路７はソリッドステートリレー３を制
御する。一方、撮影中の管電圧は管電圧検出抵抗１５で
検出され、管電圧制御回路１８は検出管電圧に応じて設
定管電圧になるようにチョッパ制御回路１９に制御信号
を与え、チョッパ制御回路１９はスイッチング素子９の
デューティー比を制御し、固定周波数で駆動しているイ
ンバータ回路８′の入力電圧を負荷を供給するために必
要な一定電圧になるように制御する。In the above structure, the charging voltage of the capacitor 5 interposed on the primary side of the high voltage transformer 13 is detected by the detection resistor 6, and the charging voltage control circuit 7 is a solid state relay so that the charging voltage of the capacitor 5 becomes a predetermined value. Control 3 On the other hand, the tube voltage during photography is detected by the tube voltage detection resistor 15, and the tube voltage control circuit 18 gives a control signal to the chopper control circuit 19 so that the set tube voltage is reached according to the detected tube voltage, and the chopper control circuit 19 Controls the duty ratio of the switching element 9 so that the input voltage of the inverter circuit 8'driven at a fixed frequency becomes a constant voltage required to supply a load.
【０００６】[0006]
【発明が解決しようとする課題】上記構成の従来のイン
バータ式Ｘ線高電圧装置では、電源トランス、スイッチ
ング素子、チョッパ制御回路等を必要とするので部品点
数も多くなり、複雑となり、且つ、電源トランスの一次
側にチョッパ等のスイッチングレギュレータを用いるの
で装置が大型になる。このように大型になると、車載用
のＸ線高電圧装置の様に、機器の設置スペースが狭く、
スペースに制限がある場合には、不向きである。The conventional inverter type X-ray high-voltage device having the above-mentioned structure requires a power transformer, a switching element, a chopper control circuit, etc., and therefore has a large number of parts and is complicated, and the power source is complicated. Since a switching regulator such as a chopper is used on the primary side of the transformer, the device becomes large. With such a large size, the installation space of the equipment is small, like the in-vehicle X-ray high-voltage equipment,
Not suitable if space is limited.
【０００７】また、スイッチングレギュレータを用い、
このスイッチングレギュレータがＸ線曝射中インバータ
回路の入力電圧を常に制御しており、且つ、充電電圧制
御回路もＸ線曝射中作動しているので、特に撮影中は電
源から大電流負荷をとり、電源電圧の降下をきたすこと
から、車載用のように電源設備が小容量の場合には不向
きであり、従来のコンデンサ方式に比べ、大容量の電源
設備が必要になる。Also, using a switching regulator,
Since this switching regulator constantly controls the input voltage of the inverter circuit during X-ray exposure, and the charging voltage control circuit also operates during X-ray exposure, a large current load is taken from the power supply especially during photography. Since the power supply voltage drops, it is not suitable when the power supply equipment has a small capacity such as a vehicle-mounted one, and a large-capacity power supply equipment is required as compared with the conventional capacitor system.
【０００８】本発明は上記に鑑み、回路構成が簡単で且
つ、装置が小型化できると共に小容量の電源設備で使用
可能な、主として車載用に適したインバータ式Ｘ線高電
圧装置を提供することを目的とする。In view of the above, the present invention provides an inverter type X-ray high-voltage device which has a simple circuit configuration, can be downsized, and can be used in a small-capacity power supply facility, and which is mainly suitable for vehicle installation. With the goal.
【０００９】[0009]
【課題を解決するための手段】本発明は、上記目的を達
成するために、管電圧の制御をインバータ回路の動作周
波数を可変することで行なうようにし、Ｘ線曝射中平滑
回路のコンデンサの充電を停止するようにしたことを特
徴とする。In order to achieve the above object, the present invention controls the tube voltage by varying the operating frequency of the inverter circuit, and the capacitor of the smoothing circuit during X-ray irradiation is controlled. The feature is that the charging is stopped.
【００１０】[0010]
【作用】高圧トランスの一次側に介在する平滑回路の大
容量コンデンサの充電電圧は、充電電圧制御回路で所定
値に制御され、特に、大負荷をとる撮影時のＸ線曝射中
はコンデンサの充電は停止される。撮影時のＸ線曝射中
コンデンサの充電電圧がインバータ回路に入力される。
また、Ｘ線曝射中のＸ線管に加えられた電圧（管電圧）
がフィードバックされ、フィードバック電圧、すなわ
ち、使用するＸ線負荷に応じてインバータ回路の発振
（動作）周波数が変化することにより、管電圧は一定に
保たれる。The charging voltage of the large-capacity capacitor of the smoothing circuit interposed on the primary side of the high-voltage transformer is controlled to a predetermined value by the charging voltage control circuit. Charging is stopped. The charging voltage of the capacitor during X-ray exposure at the time of photographing is input to the inverter circuit.
Also, the voltage (tube voltage) applied to the X-ray tube during X-ray exposure.
Are fed back, and the tube voltage is kept constant by changing the feedback voltage, that is, the oscillation (operating) frequency of the inverter circuit according to the X-ray load used.
【００１１】したがって、Ｘ線曝射中はコンデンサの充
電は停止されており、且つ、図３の従来の装置のように
チョッパ等のスイッチングレギュレータで高圧トランス
の一次側に介在するコンデンサの充電電圧の制御を行な
わないために、電源から大電流負荷をとらないので、大
容量の電源設備を必要としない。また、透視時のＸ線曝
射中は充電回路が平滑コンデンサを所定値に充電する。
この際透視時は負荷が小さく、且つ、スイッチングレギ
ュレータを用いないので電源より大電流をとらない。Therefore, the charging of the capacitor is stopped during the X-ray irradiation, and the charging voltage of the capacitor interposed on the primary side of the high voltage transformer is switched by the switching regulator such as the chopper as in the conventional device of FIG. Since no control is performed and a large current load is not taken from the power supply, a large capacity power supply facility is not required. Further, the charging circuit charges the smoothing capacitor to a predetermined value during X-ray irradiation during fluoroscopy.
At this time, the load is small during the see-through, and since a switching regulator is not used, a larger current than the power supply is not taken.
【００１２】充電回路にヒステリシスを持たせておくと
ＯＮ／ＯＦＦ制御で平滑コンデンサを所定値に充電する
ので、小負荷と相俟って、より電源設備の小容量化がで
きる。さらに、スイッチングレギュレータを用いないの
で、装置構成が簡単となり、小型化できる。If the charging circuit is provided with hysteresis, the smoothing capacitor is charged to a predetermined value by ON / OFF control, so that the capacity of the power supply equipment can be further reduced in combination with a small load. Further, since the switching regulator is not used, the device configuration is simple and the size can be reduced.
【００１３】[0013]
【実施例】以下、図面を参照してこの発明の一実施例を
説明する。図１はこの発明の一実施例に係るＸ線高電圧
装置の回路図で、図２は図１の動作説明用波形図であ
る。なお、図１において、図３と同一部品ないし同一機
能を有する部品には、同一符号を付し、その説明を省略
する。DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS An embodiment of the present invention will be described below with reference to the drawings. 1 is a circuit diagram of an X-ray high voltage apparatus according to an embodiment of the present invention, and FIG. 2 is a waveform diagram for explaining the operation of FIG. In FIG. 1, the same parts or parts having the same functions as those in FIG. 3 are designated by the same reference numerals, and the description thereof will be omitted.
【００１４】図１において、１は小容量（2KVA程度）の
単相電源、２０は充電電流抑制抵抗、２１は充電電流抑
制抵抗２０の短絡用のマグネットスイッチ、８はインバ
ータ回路、２２は共振用コンデンサ、２３は共振用イン
ダクタンス、２４はインバータ回路８の動作周波数を制
御するインバータ駆動回路、２５はＸ線曝射信号に基づ
き作動する制御回路で、充電電圧制御回路７を制御す
る。In FIG. 1, 1 is a small-capacity (about 2 KVA) single-phase power supply, 20 is a charging current suppressing resistor, 21 is a magnet switch for short-circuiting the charging current suppressing resistor 20, 8 is an inverter circuit, and 22 is for resonance. A capacitor, 23 is a resonance inductance, 24 is an inverter drive circuit that controls the operating frequency of the inverter circuit 8, and 25 is a control circuit that operates based on an X-ray exposure signal, and controls the charging voltage control circuit 7.
【００１５】つぎに、図１の回路の動作を図２との関連
において説明する。コンデンサ５は、充電電圧制御回路
７で制御されるソリッドステートリレー３により整流器
４を通して所定値に充電される。電源投入時等、コンデ
ンサ５の電荷が無い場合は、充電電流抑制抵抗２０を通
して充電され、ある一定値Ｖ1 （図２参照）に達すると
マグネットスイッチ２１が短絡し、抵抗２０をバイパス
し、コンデンサ５を所定値Ｖ2 （図２参照）に充電す
る。Next, the operation of the circuit shown in FIG. 1 will be described with reference to FIG. The capacitor 5 is charged to a predetermined value through the rectifier 4 by the solid state relay 3 controlled by the charging voltage control circuit 7. When there is no charge in the capacitor 5 such as when the power is turned on, the capacitor 5 is charged through the charging current suppressing resistor 20, and when a certain constant value V 1 (see FIG. 2) is reached, the magnet switch 21 is short-circuited and the resistor 20 is bypassed. 5 is charged to a predetermined value V 2 (see FIG. 2).
【００１６】これらの制御は、検出抵抗６の検出電圧に
基づき充電電圧制御回路７が行なう。撮影のＸ線曝射信
号が制御回路２５に与えられると、制御回路２５はＸ線
曝射中充電電圧制御回路７の動作を不能にし、ソリッド
ステートリレー３の動作を停止させ、Ｘ線管負荷はすべ
てコンデンサ５の蓄積エネルギーで供給する。These controls are performed by the charging voltage control circuit 7 based on the detection voltage of the detection resistor 6. When the X-ray exposure signal for imaging is given to the control circuit 25, the control circuit 25 disables the operation of the charging voltage control circuit 7 during X-ray exposure, stops the operation of the solid state relay 3, and loads the X-ray tube load. Are supplied by the stored energy of the capacitor 5.
【００１７】充電電圧制御回路７はコンデンサ５の電圧
を所定の一定値に保つよう制御を行い、Ｘ線曝射中は充
電を停止するが、それ以外の時は図２に示すように所定
値（スレッシュホールド値）Ｖ2 を中心にあるヒステリ
シスを持った状態で、ソリッドステートリレー３をON/O
FFさせる。コンデンサ５の直流電圧がインバータ回路８
に入力され、共振用コンデンサ２２および共振用インダ
クタンス２３を通して高圧トランス１３に入力され、昇
圧される。The charging voltage control circuit 7 controls the voltage of the capacitor 5 so as to keep it at a predetermined constant value, and stops the charging during X-ray irradiation, but at other times, as shown in FIG. (Threshold value) Turn ON / O the solid state relay 3 with a hysteresis centered on V 2.
FF. The DC voltage of the capacitor 5 is the inverter circuit 8
Is input to the high voltage transformer 13 through the resonance capacitor 22 and the resonance inductance 23, and is boosted.
【００１８】昇圧された高周波交流電圧は高圧整流器１
４により整流され、Ｘ線管１７に印加される。Ｘ線曝射
中の管電圧は管電圧検出抵抗１５で検出され、管電圧制
御回路１８にフィードバックされ、さらにインバータ駆
動回路２４に入力される。インバータ駆動回路２４は、
Ｘ線管負荷の大小に応じてインバータ回路８の発振（動
作）周波数を可変に制御することにより、図２の波形図
に示すようにＸ線曝射中のコンデンサ５の充電電圧の低
減にかかわらず、Ｘ線管の印加電圧（管電圧）を一定に
保つよう制御を行う。The boosted high frequency AC voltage is applied to the high voltage rectifier 1
4 is rectified and applied to the X-ray tube 17. The tube voltage during X-ray exposure is detected by the tube voltage detection resistor 15, fed back to the tube voltage control circuit 18, and further input to the inverter drive circuit 24. The inverter drive circuit 24 is
By variably controlling the oscillation (operating) frequency of the inverter circuit 8 according to the magnitude of the load of the X-ray tube, it is possible to reduce the charging voltage of the capacitor 5 during X-ray irradiation as shown in the waveform diagram of FIG. Instead, control is performed so that the applied voltage (tube voltage) to the X-ray tube is kept constant.
【００１９】また、透視時のＸ線曝射信号が制御信号２
５に与えられると、制御回路２５は透視Ｘ線曝射中充電
電圧制御回路７を動作させる。充電電圧制御回路７はソ
リットステートリレ３を動作させ続け、Ｘ線管負荷はコ
ンデンサ５の蓄積エネルギーおよび電源からコンデンサ
５に充電されるエネルギの両方で供給する。この際、透
視管電圧の制御は、撮影時と同様に管電圧検出抵抗１５
の検出信号が管電圧制御回路１８にフィードバックさ
れ、インバータ駆動回路２４がインバータ回路８の発振
（動作）周波数を可変制御することにより行われる。The X-ray exposure signal during fluoroscopy is the control signal 2.
5, the control circuit 25 operates the charging voltage control circuit 7 during fluoroscopic X-ray exposure. The charging voltage control circuit 7 continues to operate the solit state relay 3, and the X-ray tube load supplies both the stored energy of the capacitor 5 and the energy charged in the capacitor 5 from the power supply. At this time, the control of the fluoroscopy tube voltage is performed by the tube voltage detection resistor 15 as in the case of photographing.
Is fed back to the tube voltage control circuit 18, and the inverter drive circuit 24 variably controls the oscillation (operating) frequency of the inverter circuit 8.
【００２０】[0020]
【効果】本発明は、大負荷をとる撮影時のＸ線曝射中整
流平滑回路の平滑（高圧）コンデンサの充電を停止し、
Ｘ線曝射中の管電圧を検出抵抗を介して、インバータ回
路にフィードバックし、フィードバック電圧に応じてイ
ンバータ回路の動作周波数を変化することにより、予定
した管電圧がＸ線管に加えられるようにしたので、チョ
ッパ等のイスッチングレギュレータを用いないため、装
置構成が簡単で、小型化でき、また、電源に負担を与え
ないため、従来のコンデンサ方式と同程度の電源設備で
も使用できる車載用に適したインバータ式Ｘ線高電圧装
置を実現することができる。[Effect] The present invention stops charging of the smoothing (high-voltage) capacitor of the rectifying and smoothing circuit during X-ray exposure at the time of photographing with a heavy load,
The tube voltage during X-ray irradiation is fed back to the inverter circuit via the detection resistor, and the operating frequency of the inverter circuit is changed according to the feedback voltage so that the planned tube voltage is applied to the X-ray tube. Since the switching regulator such as a chopper is not used, the device configuration is simple and can be downsized, and since it does not burden the power supply, it can be used with the same power supply equipment as the conventional capacitor system for in-vehicle use. It is possible to realize an inverter type X-ray high voltage device suitable for.
【００２１】また、透視時は充電回路によりコンデンサ
を充電し、コンデンサの蓄積エネルギと電源からのコン
デンサに充電されるエネルギの両方がＸ線管に与えられ
るので、長時間の透視が可能になる。Further, during the fluoroscopy, the capacitor is charged by the charging circuit, and both the energy stored in the capacitor and the energy charged in the capacitor from the power supply are given to the X-ray tube, so that the fluoroscopy can be performed for a long time.
【図１】本発明の一実施例に係るＸ線高電圧装置の構成
を示す回路図である。FIG. 1 is a circuit diagram showing a configuration of an X-ray high voltage device according to an embodiment of the present invention.
【図２】図１の動作説明用の波形図である。FIG. 2 is a waveform diagram for explaining the operation of FIG.
【図３】従来のインバータ式Ｘ線高電圧装置の構成を示
す回路図である。FIG. 3 is a circuit diagram showing a configuration of a conventional inverter type X-ray high voltage device.
１…交流電源 ３…ソリッドステートリレー
４…整流器 ５…コンデンサ ６…充電電圧検出抵抗 ７…
充電電圧制御回路 ８…インバータ回路 １３…高圧トランス １
４…高圧整流器 １５…管電圧検出抵抗 １７…Ｘ線管 １８…
管電圧制御回路 ２０…充電電流抑制抵抗 ２１…マグネットスイッ
チ ２２…共振用コンデンサ ２３…共振用インダクタ
ンス ２４…インバータ制御回路 ２５…制御回路1 ... AC power supply 3 ... Solid state relay
4 ... Rectifier 5 ... Capacitor 6 ... Charging voltage detection resistor 7 ...
Charging voltage control circuit 8 ... Inverter circuit 13 ... High voltage transformer 1
4 ... High-voltage rectifier 15 ... Tube voltage detection resistor 17 ... X-ray tube 18 ...
Tube voltage control circuit 20 ... Charging current suppressing resistor 21 ... Magnet switch 22 ... Resonance capacitor 23 ... Resonance inductance 24 ... Inverter control circuit 25 ... Control circuit
Claims (2)
ンバータ回路で高周波の交流電圧に変換し、変換された
高周波電圧を高圧トランスで昇圧し、Ｘ線管に印加する
高電圧を発生するＸ線高電圧装置において、前記整流・
平滑回路の平滑コンデンサを所定値に充電する充電回路
と、前記Ｘ線管の印加電圧を検出し、検出電圧に応じて
前記インバータ回路の動作周波数を制御するインバータ
制御回路と、Ｘ線曝射信号に基づき、Ｘ線曝射中前記充
電回路の動作を停止させる制御回路とを備えたことを特
徴とするＸ線高電圧装置。1. A DC voltage obtained by a rectifying / smoothing circuit is converted into a high frequency AC voltage by an inverter circuit, and the converted high frequency voltage is boosted by a high voltage transformer to generate a high voltage to be applied to an X-ray tube. In the X-ray high voltage device, the rectification /
A charging circuit that charges the smoothing capacitor of the smoothing circuit to a predetermined value, an inverter control circuit that detects the applied voltage of the X-ray tube, and controls the operating frequency of the inverter circuit according to the detected voltage, and an X-ray exposure signal. And a control circuit for stopping the operation of the charging circuit during X-ray irradiation.
ンバータ回路で高周波の交流電圧に変換し、変換された
高周波電圧を高圧トランスで昇圧し、Ｘ線管に印加する
高電圧を発生するＸ線高電圧装置において、前記整流・
平滑回路の平滑コンデンサをヒステリシスを持った所定
値に充電する充電回路と、前記Ｘ線管の印加電圧を検出
し、検出電圧に応じて前記インバータ回路の動作周波数
を制御するインバータ制御回路と、撮影信号に基づき、
撮影Ｘ線曝射中前記充電回路の動作を停止させると共に
透視信号に基づき、透視Ｘ線曝射中前記充電回路を動作
させる制御回路とを備えたことを特徴とするＸ線高電圧
装置。2. A DC voltage obtained by the rectifying / smoothing circuit is converted into a high frequency AC voltage by an inverter circuit, and the converted high frequency voltage is boosted by a high voltage transformer to generate a high voltage to be applied to the X-ray tube. In the X-ray high voltage device, the rectification /
A charging circuit for charging the smoothing capacitor of the smoothing circuit to a predetermined value with hysteresis, an inverter control circuit for detecting an applied voltage to the X-ray tube, and controlling the operating frequency of the inverter circuit according to the detected voltage, and Based on the signal
An X-ray high-voltage device comprising: a control circuit that stops the operation of the charging circuit during exposure to radiographic X-rays and that operates the charging circuit during exposure to fluoroscopic X-rays.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP5102199A JP2674464B2 (en) | 1992-10-30 | 1993-04-28 | X-ray high voltage equipment |
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP29290492 | 1992-10-30 | ||
| JP4-292904 | 1992-10-30 | ||
| JP5102199A JP2674464B2 (en) | 1992-10-30 | 1993-04-28 | X-ray high voltage equipment |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH06196292A true JPH06196292A (en) | 1994-07-15 |
| JP2674464B2 JP2674464B2 (en) | 1997-11-12 |
Family
ID=26442930
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP5102199A Expired - Fee Related JP2674464B2 (en) | 1992-10-30 | 1993-04-28 | X-ray high voltage equipment |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2674464B2 (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2014113310A (en) * | 2012-12-10 | 2014-06-26 | Hitachi Medical Corp | X-ray diagnostic imaging apparatus |
| CN109905033A (en) * | 2017-11-23 | 2019-06-18 | 西门子医疗保健有限责任公司 | Transformer unit and method for operating transformer unit |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH02126600A (en) * | 1988-11-04 | 1990-05-15 | Hitachi Medical Corp | Inverter type x-ray generating power source |
| JPH0364999A (en) * | 1989-08-03 | 1991-03-20 | Matsushita Electric Ind Co Ltd | Printed board |
-
1993
- 1993-04-28 JP JP5102199A patent/JP2674464B2/en not_active Expired - Fee Related
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH02126600A (en) * | 1988-11-04 | 1990-05-15 | Hitachi Medical Corp | Inverter type x-ray generating power source |
| JPH0364999A (en) * | 1989-08-03 | 1991-03-20 | Matsushita Electric Ind Co Ltd | Printed board |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2014113310A (en) * | 2012-12-10 | 2014-06-26 | Hitachi Medical Corp | X-ray diagnostic imaging apparatus |
| CN109905033A (en) * | 2017-11-23 | 2019-06-18 | 西门子医疗保健有限责任公司 | Transformer unit and method for operating transformer unit |
| CN109905033B (en) * | 2017-11-23 | 2021-04-02 | 西门子医疗保健有限责任公司 | Transformer unit and method for operating a transformer unit |
Also Published As
| Publication number | Publication date |
|---|---|
| JP2674464B2 (en) | 1997-11-12 |
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