US3564243A

US3564243A - Power supply circuit for use with x-ray generating device for cine-radiography

Info

Publication number: US3564243A
Application number: US710227A
Authority: US
Inventors: Yoshito Takao; Haruyuki Kusagaya; Shigenobu Yanaka; Kouichi Koike
Original assignee: Hitachi Ltd
Current assignee: Hitachi Ltd
Priority date: 1968-03-04
Filing date: 1968-03-04
Publication date: 1971-02-16
Anticipated expiration: 1988-02-16

Abstract

Cineradiography wherein an AC sinusoidal input is converted by an inverter using controlled rectifiers into rectangular pulses in synchronism with shutter opening signals provided by a cinecamera, and the rectangular pulses in turn are boosted to high voltage pulses which are applied to the anode of an X-ray tube so as to produce pulselike X-rays of optional time-width required for photographing only during the period when the shutter is opened, thereby minimizing the dosage to which a patient is exposed. Thus, the device described herein is advantageous over the conventional devices in which pulse-like Xrays are generated under the control of the grid of an X-ray tube, in that the former can be constructed at lower cost, and that high-speed cinephotography can be carried out since the number of frames per second can be selected irrespective of the frequency of the power source.

Description

United States Patent Yoshito Takao Nagasaki-shi;

l-laruyuki Kusagaya, Koganei-shi; Shigenobu Yanaka, Tokyo; Kouichi Koike,

Inventors POWER SUPPLY CIRCUIT FOR USE WITH X-RAY GENERATING DEVICE FOR CINE-RADlOGRAPI-IY 8 Claims, 22 Drawing Figs.

us. or. 250/65; 250/102 Int. Cl H05g 1/14, HOSg 1/60 Field ol'Search ..250/65, 102

[56] References Cited UNITED STATES PATENTS 2,962,594 11/1960 Duffy, Jr 250/102X 3,109,093 10/1963 Arrison, Jr. et a1. 250/65 3,424,901 l/l 969 Kok 250/65X Primary ExaminerWilliam F Lindquist Attorney-Craig, Antonelli, Stewart & Hill ABSTRACT: Cineradiography wherein an AC sinusoidal input is converted by an inverter using controlled rectifiers into rectangular pulses in synchronism with shutter opening signals provided by a cinecamera, and the rectangular pulses in turn are boosted to high voltage pulses which are applied to the anode of an X-ray tube so as to produce pulselike X-rays of optional time'width required for photographing only during the period when the shutter is opened, thereby minimizing the dosage to which a patient is exposed. Thus, the device described herein is advantageous over the conventional devices in which pulse like X-rays are generated under the control of the grid of an X-ray tube, in that the former can be constructed at lower cost, and that high-speed cinephotographying can be carried out since the number of frames per second can be selected irrespective of the frequency of the power source.

POWER SUPPLY CIRCUIT FOR USE WITH X-RAY GENERATING DEVICE FOR CINE-RADIOGRAPHY This invention relates to an X-ray generating device for cine-radiography and more particularly pertains to improvements in the power supply circuit for use with such device for generating pulse-like X-rays of short duration only during the time when the shutter of a cine-camera is opened.

In an attempt to achieve cine-radiography of moving internal organs such as the heart, it has long been desired to be able to decrease the dosage to which a patient is exposed. Recently, there has been developed a device using a threeelectrode X-ray tube and so designed that by intermittently effecting X-ray irradiation in synchronism with the opening of the shutter of a cine-camera, the time of irradiation can be decreased so as to be of the order of milliseconds irrespective of the number of frames to be photographed per second. Consequently, it is possible to prevent X-rays from being wastefully irradiated during the time when the shutter is closed so that the dosage can be reduced by half or more, and it is also possible to reduce the possibility that the photograph becomes blurred due to movement of the object to be photographed.

In order to operate a three-electrode X-ray tube in an ordinary full-wave rectification type high voltage generating device, however, it is required that the grid control signal for effecting intermittent X-ray irradiation be in synchronism with the phase of the power source. This restricts the number of frames to be photographed per seconds, and in addition it is very difficult to achieve such synchronism without using a special camera adapted to be driven by means of a synchronous motor. By adopting a method of applying to the X-ray tube a rectified voltage smoothed out by a high voltage condenser additionally provided in the full-wave rectifier circuit, it is possible to generate pulselike X-rays of an optional cyclic period irrespective of the phase of the power source and avoid the restriction described above. However, the high voltage condenser is required in addition to the three-electrode X-ray tube, which increases the cost of the device correspondingly.

An object of this invention is to provide a practical device for generating pulselike X-rays in synchronism with external signals such as the shutter opening signals provided by a cinecamera, said device comprising rectifier-smoother circuit means for converting an AC sinusoidal input from a commercial AC power source into a DC voltage, DC chopper circuit means composed of controlled rectifiers and connected with the output of said rectifier-smoother circuit means, means for supplying a control signal to said DC chopper circuit means in accordance with shutter opening signals provided by the cinecamera so as to produce rectangular pulses in synchronism with said shutter opening signals at the output side of said DC chopper circuit means, and means for boosting the output pulses of said DC chopper circuit means to high voltage pulses and applying the latter to the anode of an X-ray tube, wherein pulselike X-rays of optional time-width can be produced with the application of said high voltage pulses every time when the shutter of the cine-camera is opened.

FIGS. 1 to 3 are circuit diagrams showing embodiments of this invention.

FIG. 4 is a block diagram showing the control signal circuit for operating the devices shown in FIGS. 1 to 3.

FIGS. 50 to 5s are graphs showing voltage waveforms.

In the arrangement shown in FIG. 1, the portion enclosed by a dotted line is an inverter for converting an AC sinusoidal input into rectangular pulses which comprises a pair of DC chopper circuits one of which is constructed by connecting controlled rectifiers SCR, and SCR a bypass capacitor C a rectifier D and a resistor R to the output of a rectifiersmoother circuit consisting of bridge-connected rectifiers D to 0,, a smoothing capacitor C, and a resistor R, as shown in the drawing, and the other chopper circuit being constructed similarly by connecting controlled rectifiers SCR, and SCR a bypass capacitor Cga rectifier D and a resistor R to the output of a rectifier-smoother circuit consisting of rectifiers D to D a capacitor C, and a resistor R The output terminals of said pair of DC chopper circuits are connected with primary terminals t, and of a high voltage transfonner T, in opposite polarity relationship with each other, and the inputs of the rectifiers D to D and D, to D are connected with output terminals t and t., of a tube voltage regulator T through an isolating transformer T That is, said pair of DC chopper circuits form inverse-parallel circuits each including a separate DC power source. The secondary winding of the high voltage transformer T, is connected across the electrodes of a diode X-ray tube X through an ordinary full-wave rectifier circuit composed of rectifier tubes K, to K.,.

Referring to FIG. 4, there is shown an example of a control signal circuit for operating the inverter. In FIG. 4, the reference numeral 1 represents a contact adapted for interlocking with the opening and closure of a shutter provided in the cine-camera, 2 and 4 differentiating rectifier circuits, 3 a flip-flop circuit, 5 a monostable multivibrator circuit, 6 a differentiating circuit, 7 a rectifier-separating circuit, and 8 and 9 amplifier circuits. A shutter opening signal a produced by the camera contact 1 is differentiated and rectified, and a resulting positive pulse b is supplied to the flip-flop circuit which in turn provides two outputs having a frequency two times as high as that of the shutter-opening signal a and out of phase with the latter. One of the outputs c is differentiated and rectified, and a resultant positive pulse d is supplied to the monostable multivibrator circuit. A rectangular wave output e produced by the monostable multivibrator circuit is differentiated and then resulting positive and negative pulses f are rectified, separated and amplified into trigger signals 8 and h which in turn are supplied to the gates of the controlled rectifiers SCR, and SCR of FIG. 1, respectively. The other of the output j is converted into trigger signals n, p through the same process of kI-m and applied to the gates of the controlled rectifiers SCR, and SCR," of FIG. 1. As shown in FIG. 5, trigger signals g, h and n, p are alternately produced during the period when the shutter opening signal a appears.

Description will now be made of the operation of the inverter which is effected by the trigger signals. If the trigger signal 3 is applied to the gate of the controlled rectifier SC R,, then the latter is rendered conductive so that a positive DC voltage smoothed out by the condenser C 1 appears across the terminals 1?, and At the same time, the bypass capacitor C is charged so that the trigger signal h is subsequently caused to arrive at the gate of the controlled rectifier SCR When the rectifier SCR is rendered conductive, the rectifier SCR is cut off by the voltage of the condenser C,. No voltage will appear on the output side until the rectifier SCR is again rendered conductive.

The rectifier SCR is subsequently rendered conductive, but it is short-circuited through the condenser C at the moment that the rectifier SCR is rendered conductive by the trigger signal 3, so that the rectifier SCR is cut off. Thus, the rectifiers SCR and SCR are alternately made conductive by the trigger signals g and h, with'a result that a positive rectangular pulse is available across the terminals 2, and 1 as shown in FIG. 5i.

In the same way, the rectifiers SCR, and SCR are also alternately rendered conductive by the trigger signals n and p, with a result that a negative rectangular pulse becomes available across the terminals t, and t; as shown in FIG. Sq.

The outputs of the DC chopper circuit formed by the rectifiers SCR, and SCR and that constituted by the rectifiers SCR, and SCR are added each other and applied to the primary side of the high voltage transformer in the form of axially symmetrical rectangular pulses which are alternately reversed in polarity as shown in FIG. 5r. Thus, the voltage applied to the X-ray tube assumes such a waveform as shown in FIG. 5s, so that pulselike X-rays are produced in synchronism with the opening of the shutter of the cine-camera.

The cyclic period of the pulses thus produced depends only upon that of the synchronizing signal (shutter opening signal) irrespective of the phase of the power source, and their width can be optionally selected by changing the time constant of the monostable multivibrator provided in the signal circuit. In the example shown in FIG. 2, a half-wave rectifier circuit comprised of rectifiers D, and D, is provided in the DC power source for the inverter, and the isolating transformer (as indicated by T in FIG. 1) is omitted. Except for this, the em bodiment of FIG. 2 is similar to that of FIG. 1 in respect of construction and operation.

In FIG. 3, there is shown an example in which an inverter is constructed by the use of a rectifier-smoother circuit and bridge-connected DC chopper circuits.

Controlled rectifiers SCR,, SCR and SCR are connected as the respective arms of the bridge in such a manner that the controlled rectifiers SCR, and SCR, form one of the DC chopper circuits and the controlled rectifiers SCR and SCR, constitute the other DC chopper circuit. The respective DC chopper circuits have their inputs connected with the output of the rectifier-smoother circuit formed by rectifiers D, to D,,, smoothing capacitor C, and resistor R, and their outputs connected with the primary terminals t, and t, of the high voltage transformer T, in opposite polarity relationship to each other.

The input of the rectifiers D, to D, is connected across output terminals t and t, of tube voltage regulator T and the secondary winding of the high voltage transformer T is connectedwith the electrodes of the two-electrodes X-ray tube through the full-wave rectifier circuit, as shown in FIG. 1. Symbols C to C, represent bypass capacitors, L, and L, bypass reactors, D to D feedback rectifiers, and R to R feedback resistors.

The control signal circuit as shown in FIG. 3 can be utilized as it is. Thus, the signal g is supplied to the gate of the controlled rectifiers SCR, and SCR,, the signal h to the gate of the controlled rectifier SCR the signal. n to the controlled rectifiers SCR and SCR and the signal p to the gate of the controlled rectifier SCR,.

With the arrangement of FIG. 3, upon arrival of the signal g, the controlled rectifiers SCR, and SCR, are rendered conductive so that a positive voltage such as shown in FIG. 5i appears across the t, and t When the controlled rectifier SCR, is rendered conductive by the subsequent signal h, the capacitor C is caused to discharge so that a voltage is induced across the reactor L,, whereby the controlled rectifiers SCR, and SCR, are cut off. Subsequently, the controlled rectifier SCR, is also cut off. Upon arrival of the signal n, the controlled rectifiers SCR, and SCR are rendered conductive so that a negative voltage such as shown in FIG. Sq appears across the terminals t, and t and when the controlled rectifier SCR, is rendered conductive by the next signal p, the capacitor C is caused to discharge so that a voltage is induced across the reactor L whereby the controlled rectifiers SCR, and SCR are cut off. Subsequently, the controlled rectifier SCR, is also cut off. As a result of repetition of the operation as described above, axially symmetrical rectangular pulses as shown at r which are the combination of FIG. 5i and Sq are applied to the primary winding of the high voltage transformer, so that the voltage applied to the X-ray tube assumes a pulse waveform in synchronism with the shutter opening signals as shown in FIG. 5s.

The advantages of this invention are as follows:

I. Since pulselike X-rays persisting for a short period of time are produced only during the time when the shutter of the camera is opened, the dosage to which a patient is exposed in the production of cine-radiography can be minimized, and a high-quality photograph can be obtained which is less blurred due to motion of an object to be photographed. 2. Since there is no need to achieve synchronization with respect to the phase of the power source, no limitation is imposed upon the number of frames per second, and the power supply source embodying the present invention can be applied not only to a camera which is so designed as to be driven by means of a synchronous motor but also to any type of camera if there is only provided a signal contact.

3. Since the waveform of the tube voltage is rectangular and the pulse width can be optionally selected, high-speed photographying such as that with more than frames per second can also be effected which is required for cine-angiocardiography.

4. Since no three-electrode X-ray tube and high voltage condenser are needed, the total manufacturing cost of the device can be lowered, and cine-photographying can be realized merely by incorporating an inverter and control signal circuit therefor as an adapter into an ordinary full-wave rectification type X-ray device using a two-electrode X-ray tube. Thus, the circuit arrangement of this invention can be simply applied to any existing device of this type.

5. Since an input pulse applied to the high-voltage transformer is of axially symmetrical waveform, there is no possibility that the high-voltage transformer is linearly magnetized as in the cases where use is made of nonsymmetrical pulses. Consequently, the waveform is not distorted.

We claim:

1. A power supply circuit for use with an X-ray generating device for cine-radiography, comprising rectifier-smoother circuit means for converting an AC sinusoidal input from a commercial AC power source into a DC voltage, DC chopper circuit means composed of controlled rectifiers and connected with the output of said rectifier-smoother circuit means, means for supplying a control signal to said DC chopper circuit means in accordance with shutter opening signals provided by a cine-camera being independent of the voltage produced by the AC power source so as to produce rectangular pulses in synchronism with said shutter opening signals at the output side of said DC chopper circuit means, and means for boosting the output pulses of said DC chopper circuit means to high voltage pulses and applying the latter to the anode of an X-ray tube, wherein pulselike X-rays of optional time-width are generated with the application of said high voltage pulses every time the shutter is opened.

2. The power supply circuit of claim 1, wherein said means for supplying a control-signal includes first means for receiving said shutter open signal from said cine-camera and for generating first and second signals each time said cine-camera delivers shutter opening signals.

3. The power supply circuit of claim 2 further including second and third means for receiving said first and second signals respectively forgenerating pulses alternately reversed in polarity in synchronism with the delivery of shutter opening signals by said cine-camera.

4. The power supply circuit of claim 3, wherein said second and third means each comprise a differentiating rectifier and monostable rnultivibrator connected in series.

5. The power supply circuit of claim 4, wherein said first means comprises a differentiating rectifier and flip-flop connected in series.

6. The power supply circuit of claim 2, wherein said first means comprises a differentiating rectifier and flip-flop connected in series.

7. A power supply circuit for use with an X-ray generating circuit for cine-radiography comprising a pair of rectifiersmoother circuits for converting an AC sinusoidal input from a commercial AC power source into a DC voltage, a pair of DC chopper circuits composed of controlled rectifiers and connected with the outputs of said rectifier-smoother circuits, means for supplying a control signal to each of said chopper circuits in accordance with shutter opening signals provided by a cine-camera independently of the voltage produced by the AC power source so as to produce rectangular pulses in synchronism with said shutter opening signals alternately at the output sides of said DC chopper circuits, means for com bining the output pulses of said chopper circuits into axially symmetrical rectangular pulses which are alternately reverse in polarity, and means for boosting and rectifying said axially symmetrically rectangular pulses to high voltage pulses and applying the latter to the anode of an X-ray tube, wherein pulselike X-rays of optional time-width are generated with the application of high voltage pulses every time the shutter is opened.

8. A power supply circuit for use with an X-ray generating device for cine-radiography, comprising rectifier-smoother circuit means for converting an AC sinusoidal input from a commercial AC power source into a DC voltage, DC chopper circuit means including at least bridge-connected four controlled rectifiers connected with the output of said rectifiersmoother circuit means, means for supplying a control signal to said DC chopper circuit means in accordance with shutter opening signals provided by a cine-camera independently of the voltage produced by the AC power source so as to UNITED STATES PATENT OFFICE CERTIFICATE OF CORRECTION Patent No. 243 Dated February 16, 1971 I r( Yoshito Takao, Haruyuki KUSAGAYA, Shigenobu YANAKJ and Kou1cn1 KUIKE It is certified that error appears in the above-identified patent and that said Letters Patent are hereby corrected as shown below:

Column 1, Line 11, insert Priority Japan March 13, 1967, 42/15, 320

Signed and sealed this 9th day of November 1971.

(SEAL) Attest:

EIMARD M.FLETCHER,JR. ROBERT GOT'ISCHALK Attesting Officer Acting Commissioner of Pat

Claims

2. The power supply circuit of claim 1, wherein said means for supplying a control signal includes first means for receiving said shutter open signal from said cine-camera and for generating first and second signals each time said cine-camera delivers shutter opening signals.

3. The power supply circuit of claim 2 further including second and third means for receiving said first and second signals respectively for generating pulses alternately reversed in polarity in synchronism with the delivery of shutter opening signals by said cine-camera.

4. The power supply circuit of claim 3, wherein said second and third means each comprise a differentiating rectifier and monostable multivibrator connected in series.

7. A power supply circuit for use with an X-ray generating circuit for cine-radiography comprising a pair of rectifier-smoother circuits for converting an AC sinusoidal input from a commercial AC power source into a DC voltage, a pair of DC chopper circuits composed of controlled rectifiers and connected with the outputs of said rectifier-smoother circuits, means for supplying a control signal to each of said chopper circuits in accordance with shutter opening signals provided by a cine-camera independently of the voltage produced by the AC power source so as to produce rectangular pulses in synchronism with said shutter opening signals alternately at the output sides of said DC chopper circuits, means for combining the output pulses of said chopper circuits into axially symmetrical rectangular pulses which are alternately reverse in polarity, and means for boosting and rectifying said axially symmetrically rectangular pulses to high voltage pulses and applying the latter to the anode of an X-ray tube, wherein pulselike X-rays of optional time-width are generated with the application of high voltage pulses every time the shutter is opened.

8. A power supply circuit for use with an X-ray generating device for cine-radiography, comprising rectifier-smoother circuit means for converting an AC sinusoidal input from a commercial AC power source into a DC voltage, DC chopper circuit means including at least bridge-connected four controlled rectifiers connected with the output of said rectifier-Smoother circuit means, means for supplying a control signal to said DC chopper circuit means in accordance with shutter opening signals provided by a cine-camera independently of the voltage produced by the AC power source so as to produce axially symmetrical rectangular pulses which are alternately reversed in polarity in synchronism with said shutter opening signals at the output side of said DC chopper circuit means, and means for boosting and rectifying the output pulses of said DC chopper circuit means to high voltage pulses and applying the latter to the anode of an X-ray tube, wherein pulselike X-rays of optional time-width are generated with the application of said high voltages every time the shutter is opened.