JPS60198099A - Rotating anode type x-ray tube driving device - Google Patents

Abstract

PURPOSE:To stop X-ray irradiation when a stator circuit is opened by connecting in series resistances by which driving current is detected to a stator coil, and detecting voltage producing at both ends for interlocking. CONSTITUTION:When potential difference is produced at both ends of each resistance 1R and 2R by rotation of X-ray tube, capacitors 1C and 2C are charged. Each LED in photo couplers 1PH and 2PH is emitted by charged voltage of capacitors 1C and 2C, and an input circuit is closed. When resistances 1R and 2R are disconnected, since voltage is not generated at both ends of each of resistances 1R and 2R, LEDs are not emitted. Thereby, photo transistor in an input circuit is not turned on and an input circuit in an X-ray irradiation signal generator circuit XRS is kept open. Therefore, X-ray irradiation is not performed.

Description

[Detailed Description of the Invention] [Technical Field] The present invention relates to a drive device for a single-rotation anode type X-ray tube (hereinafter referred to as an "X-ray tube"), and particularly relates to a driving device for a single-rotation anode type X-ray tube (hereinafter referred to as an "X-ray tube"). t: relates to a technique that is effective when applied to a technique that prevents X-ray radiation from occurring.

[Background technology]

Figures 1 and 2 show problems with conventional X-ray tube drive devices□
It is a circuit diagram for explaining the points.

In FIGS. 1 and 2, XS is an X-ray radiation switch, and XSC is an X-ray tube stator coil circuit.

SM is the main coil of the stator coil, SA is the auxiliary coil of the stator coil, IR to 3R are resistors, ID, 2D are diodes, IVR is a variable resistor (volume), IZ
D is Zener diode, l5CR is thyristor, IC
~3C is a capacitor, IRY is a relay, IRY・1
t a, IRYI t b and IRY・2a are contacts of relay IRY, 2RY is a delay relay, 2RY-1b and 2RY2a are contacts of relay 2RY, XR8 is an X-ray radiation signal generation circuit, and its output is connected to the X-ray tube. X on the grid of
Input as a line radiation signal. The symbol a of the contact is red to indicate a normally closed contact, and the symbol b indicates a normally closed contact.

Next: The operation of this circuit will be explained.

In Figure 1, when the X-ray radiation switch XS is pressed,
As the rotating anode of the wire tube starts rotating, the resistances R1 and R
A potential difference occurs between both ends of 2. Capacitor IC is charged with a time constant determined by variable resistor IVR and capacitor IC. When the charging voltage of this capacitor IC reaches the Zener voltage of Zener diode IZ'D, thyristor I5CR is triggered and relay IRY operates. The variable resistor IVR is adjusted so that the relay IRY does not operate until the rotating anode of the X-ray tube reaches a specified rotational speed. When the relay IRY operates, contact IRY-1tb
opens, contacts IRY and 1ta close, and the power supply is AC100V.
At the same time, as shown in FIG. 2, the contact IRY.2a provided in the input circuit of the X-ray radiation signal generation circuit XRS is closed. On the other hand, at the same time that the X-ray radiation switch close. As a result, an X-ray radiation signal is generated from the X-ray radiation signal generation circuit XR8, and is sent to the grid control circuit GB of the X-ray tube, where X-rays are emitted.

However, in such a conventional method, the relay IR
After Y is activated, if the circuit of the main coil SM of the stator coil is opened due to a failure such as disconnection of the resistor 2R, the relay IRY remains activated, so the contact IRY・2a shown in FIG. had the disadvantage that it would remain closed and X-rays would be emitted.

[Purpose of the invention]

The object of the present invention is to provide a technical means that can be interlocked so that X-rays are not emitted when the power supply circuit of the main coil or auxiliary coil of the stator coil of a rotary anode type XIIIA tube is opened. There is a particular thing.

The above and other objects and novel features of the present invention will become apparent from the description of this specification and the accompanying drawings.

[Summary of the invention]

A brief overview of typical inventions disclosed in this application is as follows.

In other words, a resistor is connected in series to the main coil and auxiliary coil of the cheetah coil of a single-rotation anode X-ray tube to detect the drive current supplied to each, and the voltage generated across each resistor is detected. However, by providing an interlock mechanism to prevent X-ray emission if there is an abnormality in the detected voltage.

When the power supply circuit of the main coil or auxiliary coil of the stator coil is opened, an interlock is provided to prevent X-rays from being emitted.

[Structure of the invention]

The following five configurations of the present invention will be explained together with examples.

FIG. 3 is a circuit diagram showing the configuration of a driving device for a rotating anode type X-ray tube according to an embodiment of the present invention.

In FIG. 3, parts having the same functions as those in FIGS. 1 and 2 are given the same reference numerals, and repeated explanations thereof will be omitted.

In FIG. 3, 4R and 5R are resistors, I P tl and 2PH are photocoupler, which are composed of a light emitting diode and a phototransistor.

As shown in FIG. 3, the rotating anode type X-ray tube drive device of this embodiment has a drive current supplied to the main coil SM and the auxiliary coil SA of the stator coil, respectively. Resistors IR and 2R are connected in series for detecting IR and 2R, and photocouplers IPH and 2PH are connected in parallel to both ends of each of the resistors IR and 2R. Each phototransistor of these photocouplers IPH and 2PH is connected to an X-ray radiation signal generation circuit XR8 shown in FIG.
It is a contact point for controlling the opening and closing of the input circuit.

Next, the operation of this embodiment will be explained.

In FIGS. 3 and 4, when the X-ray emission switch XS is pressed, the X-ray tube starts rotating and a potential difference is generated across the resistors IR and 2R. Capacitors IC and 2C are charged via diodes ID and 2D. This capacitor I
The light emitting diodes of the photocouplers IPH and 2PI-1 emit light by the charging voltages of C and 2C. This emitted light is transmitted to the X-ray radiation signal generation circuit X and the photo coupler 1' P H provided in the input circuit of the RS.
and the photo 1-transistor of 2PH, thereby closing the input circuit. As a result, when the X-ray imaging switch is turned on, the XIA@radiation signal generation circuit XR3 generates an X-ray radiation signal and the grid bias control circuit G of the X-ray tube generates an X-ray radiation signal.
Enter B and emit X-rays.

Next, when the resistor IR or 2R is disconnected, no voltage is generated across the resistor IR or 2R, so the photo 1
- The light emitting diode of Kabra IPH or 2PH does not emit light. As a result, the phototransistor provided in the input circuit of the X-ray radiation signal generation circuit XR8 is not turned on.

Therefore, the input circuit of the X-ray radiation signal generation circuit XR8 remains open, and no Xi radiation signal is generated.

In this way, the photo couplers IPH and 2PH are provided at both ends of each of the resistors IR and 2R in parallel with them, and the phototransistors of the photo couplers IPH and 2PH are connected to the input circuit of the X-ray radiation signal generation circuit XR8. By providing the resistor IR or 2R, when the resistor IR or 2R is disconnected,
It is possible to prevent the generation of X-ray radiation signals.

[Effects] As explained above, according to the novel technical means disclosed in the present application, the following effects can be obtained.

(1) Resistors are connected in series to the main coil and auxiliary coil of the stator coil of the rotating anode X-ray tube to detect the drive current supplied to each, and if there is an abnormality in each resistance, By providing an interlock mechanism to prevent X-ray radiation, it is possible to prevent X-ray radiation from being emitted when the power supply circuit of the main coil or auxiliary coil of the stator coil is opened.

The present invention has been specifically explained above using examples, but
It goes without saying that the present invention is not limited to the embodiments described above, and can be modified in various ways without departing from the gist thereof.

[Brief explanation of drawings]

1 and 2 are circuit diagrams for explaining the problems of a conventional X-ray tube drive device, and FIG. 3 is a circuit diagram of a rotating anode type X-ray tube drive device according to an embodiment of the present invention. FIG. 2 is a circuit diagram showing the configuration. In the figure, XS...X-ray radiation switch, Xsc...stator coil circuit, SM and SA...coil, IR. 2R, 4R and 5R...resistance, IC, 2C and 3c...
...Capacitor, 2RY...Relay, IPH and 2P
H...Photocoupler, ID and 2D...Diode, 2RY-1a, 2RY1b, and 2RY.2a-contact.

Claims (1)

[Claims] (1) From when the X-ray irradiation start switch is turned on until the rotation speed of the rotating anode of the rotating anode type X-ray tube reaches the specified value
In a rotating anode X-ray tube drive device that prevents radiation from being irradiated, a resistor is installed in the main coil and auxiliary coil of the stator coil of the rotary anode X-ray tube to detect the drive current supplied to each. Rotating anode type Wire tube drive device.