CN113543437A - X-ray generating device and medical imaging apparatus - Google Patents
X-ray generating device and medical imaging apparatus Download PDFInfo
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- CN113543437A CN113543437A CN202010322913.0A CN202010322913A CN113543437A CN 113543437 A CN113543437 A CN 113543437A CN 202010322913 A CN202010322913 A CN 202010322913A CN 113543437 A CN113543437 A CN 113543437A
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- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05G—X-RAY TECHNIQUE
- H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
- H05G1/08—Electrical details
- H05G1/10—Power supply arrangements for feeding the X-ray tube
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- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
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Abstract
The invention discloses an X-ray generating device and medical imaging equipment, wherein the device comprises: an X-ray tube for outputting X-rays; a power supply circuit for applying a preset voltage to the X-ray tube; the heating circuit is used for applying preset current to a cathode filament of the X-ray tube so as to heat the cathode filament of the X-ray tube; the driving circuit is used for driving the anode target surface of the X-ray tube to rotate; a feedback circuit for detecting a tube voltage and a tube current of the X-ray tube; and the control circuit controls the driving circuit to drive the anode of the X-ray tube to rotate, controls the output voltage of the power supply circuit according to the tube voltage, and controls the output current of the heating circuit according to the tube current. The device simple structure through the accurate smooth control to X-ray tube anode rotation, can export little focus, powerful X ray for imaging quality is good, and through the closed loop control to pipe voltage, pipe current, can improve the quality of X ray.
Description
Technical Field
The invention relates to the technical field of X-rays, in particular to an X-ray generating device and medical imaging equipment.
Background
At present, in an X-ray generating device in the related art, because the heat dissipation of an anode of an X-ray tube is poor, the focus of generated X-rays is large, and the X-ray generating device cannot continuously operate under the condition of high power; the driving device of the rotary anode mostly adopts an analog device control mode, is easy to be interfered, has poor control precision and has a complex control system.
Disclosure of Invention
The present invention is directed to solving, at least to some extent, one of the technical problems in the related art.
Therefore, an object of the present invention is to provide an X-ray generating apparatus for outputting a small-focus, high-power X-ray, making the imaging quality good, and improving the quality of the X-ray.
A second object of the invention is to propose a medical imaging apparatus.
In order to achieve the above object, a first embodiment of the present invention provides an X-ray generating apparatus, which includes: the X-ray tube is connected with the power circuit, the heating circuit and the feedback circuit respectively, and the control circuit is connected with the power circuit, the heating circuit, the driving circuit and the feedback circuit respectively; wherein the control circuit controls the drive circuit to drive the anode of the X-ray tube to rotate; the power supply circuit applies a preset voltage to the X-ray tube to form a tube voltage, and the heating circuit applies a preset current to a cathode filament of the X-ray tube to heat the cathode filament of the X-ray tube to generate electrons, wherein the electrons move to an anode of the X-ray tube under the action of the tube voltage to generate a tube current, and X-rays are output through the X-ray tube; the feedback circuit detects tube voltage and tube current of the X-ray tube and feeds the tube voltage and the tube current back to the control circuit; the control circuit controls the output voltage of the power circuit and the output current of the heating circuit according to the tube voltage and the tube current.
According to the X-ray generating device provided by the embodiment of the invention, the control circuit controls the driving circuit to drive the anode of the X-ray tube to rotate, the control power supply circuit applies a preset voltage to the X-ray tube to form a tube voltage, the control heating circuit heats a cathode filament of the X-ray tube to generate electrons, the electrons move under the action of the tube voltage to generate a tube current, the feedback circuit is used for detecting the tube voltage and the tube current of the X-ray tube, the output voltage of the power supply circuit and the output current of the heating circuit are respectively controlled according to the tube voltage and the tube current, and the driving circuit drives the anode of the X-ray tube to rotate again to form closed-loop control. Therefore, the device can output X-rays with small focus and high power, so that the imaging quality is good, and the quality of the X-rays can be improved.
In addition, the X-ray generating device according to the above-described embodiment of the present invention may further have the following additional technical features:
in one embodiment of the invention, the control circuit comprises: the first pulse width modulation chip is respectively connected with the heating circuit and the feedback circuit and is used for acquiring the tube current; the second pulse width modulation chip is respectively connected with the power circuit and the feedback circuit and is used for acquiring the tube voltage; the main control chip is respectively connected with the feedback circuit, the driving circuit, the first pulse width modulation chip and the second pulse width modulation chip, and is used for: when a preheating starting command is received, transmitting a preheating starting signal to the second pulse width modulation chip so that the second pulse width modulation chip controls the heating circuit to heat a cathode filament of the X-ray tube; transmitting an anode rotation driving signal to the driving circuit to cause the driving circuit to drive the anode of the X-ray tube to rotate; generating a tube voltage set value and a tube current set value; when an X-ray starting command is received, transmitting the tube voltage set value to the first pulse width modulation chip so that the first pulse width modulation chip performs closed-loop control on the power supply circuit according to the tube voltage set value and the tube voltage; transmitting the tube current set value to the second pulse width modulation chip so that the second pulse width modulation chip performs closed-loop control on the heating circuit according to the tube current set value and the tube current; and when receiving an X-ray closing command, stopping transmitting an anode rotation driving signal to the driving circuit, and transmitting a stopping signal to the driving circuit to enable the driving circuit to stop driving the anode of the X-ray tube to rotate.
In one embodiment of the present invention, the power supply circuit includes: the input end of the first rectifier sub-circuit is connected with an alternating current power supply, and the first rectifier sub-circuit is used for receiving a first alternating current output by the alternating current power supply and rectifying the first alternating current to output a first direct current; the input end of the inverter sub-circuit is connected with the output end of the first rectifier sub-circuit, the control end of the inverter sub-circuit is connected with the first pulse width modulation chip, and the inverter sub-circuit is used for inverting the first direct current according to an inversion driving signal output by the first pulse width modulation chip to output a second alternating current; the input end of the boosting sub-circuit is connected with the output end of the inverting sub-circuit, and the boosting sub-circuit is used for boosting the second alternating current to output a third alternating current; and the input end of the second rectifying sub-circuit is connected with the output end of the boosting sub-circuit, the output end of the second rectifying sub-circuit is connected with the X-ray tube, and the second rectifying sub-circuit is used for rectifying the third alternating current to output the preset voltage.
In one embodiment of the invention, the heating circuit comprises: the input end of the push-pull sub-circuit is connected with the second pulse width modulation chip and is used for receiving the heating signal output by the second pulse width modulation chip, converting the heating signal into alternating current required by heating and outputting the alternating current from the first output end or the second output end of the push-pull sub-circuit; the transformer comprises a first primary coil, a second primary coil and a secondary coil, the first primary coil is connected with a first output end of the push-pull sub-circuit, the second primary coil is connected with a second output end of the push-pull sub-circuit, the secondary coil is connected with a cathode filament of the X-ray tube, and the transformer is used for carrying out voltage transformation on the alternating current required for heating and transmitting the alternating current subjected to voltage transformation to the cathode filament of the X-ray tube so as to heat the cathode filament of the X-ray tube.
In one embodiment of the invention, the feedback circuit comprises: the voltage detection sub-circuit is respectively connected with the X-ray tube and the first pulse width modulation chip and is used for detecting the tube voltage of the X-ray tube and feeding the tube voltage back to the first pulse width modulation chip; and the current detection sub-circuit is respectively connected with the X-ray tube and the second pulse width modulation chip and is used for detecting the tube current of the X-ray tube and feeding the tube current back to the second pulse width modulation chip.
In one embodiment of the present invention, the driving circuit includes: the motor is used for driving the anode of the X-ray tube to rotate; the shutdown sub-circuit is respectively connected with the main control chip and a stator winding of the motor, and is used for inputting preset low-voltage direct current to the stator winding according to the shutdown signal so as to reduce the time required by the anode of the X-ray tube to stop rotating; and the driving sub-circuit is respectively connected with the main control chip and the stator winding of the motor, and is used for controlling the motor to drive the anode of the X-ray tube to rotate according to the anode rotation driving signal.
In one embodiment of the present invention, the feedback circuit further includes: the zero-crossing detection sub-circuit is respectively connected with the alternating current power supply and the main control chip and is used for performing zero-crossing detection on first alternating current output by the alternating current power supply to output a zero-crossing detection signal and feeding the zero-crossing detection signal back to the main control chip; the main control chip is further configured to output the anode rotation driving signal with a preset pulse width after receiving the zero-crossing detection signal for a preset time each time.
In one embodiment of the invention, the driving sub-circuit comprises: a first input end of the optical coupler is connected with a preset power supply through a first resistor, a second input end of the optical coupler is connected with the main control chip to receive the anode rotation driving signal, and a first output end of the optical coupler is grounded through a second resistor; the control end of the switching tube is respectively connected with the first output end of the optical coupler and one end of the second resistor, the first end of the switching tube is connected with the second output end of the optical coupler to form a first node, and the second end of the switching tube is grounded; the gate pole of the bidirectional thyristor is connected with the first node through a third resistor, a first main electrode of the bidirectional thyristor is connected with a zero line of the alternating current power supply, a second main electrode of the bidirectional thyristor is connected with one end of the stator winding, and the other end of the stator winding is connected with a live wire of the alternating current power supply; the input end of the voltage reduction rectifying unit is connected with the alternating current power supply, and the voltage reduction rectifying power supply is used for carrying out voltage reduction rectifying processing on the first alternating current output by the alternating current power supply so as to output preset direct current.
In an embodiment of the present invention, the step-down rectifying unit includes a first capacitor, a second capacitor, a fourth resistor, a fifth resistor, a sixth resistor, a zener diode, and a rectifying diode, wherein one end of the first capacitor is connected to the live line of the ac power supply, the other end of the first capacitor is connected to the anode of the rectifying diode, the fourth resistor is connected to the fifth resistor in parallel and is connected to the first capacitor in parallel, the sixth resistor is connected to the second capacitor in parallel, the anode of the second capacitor is connected to the neutral line of the ac power supply and the cathode of the rectifying diode, the cathode of the second capacitor is grounded, the anode of the zener diode is grounded, and the cathode of the zener diode is connected to the anode of the rectifying diode.
In an embodiment of the present invention, the feedback circuit further includes a stator detection sub-circuit, the stator detection sub-circuit is connected to the stator winding and the main control chip, respectively, and the stator detection sub-circuit is configured to detect a current of the stator winding and feed the current of the stator winding back to the main control chip; and the main control chip is also used for judging whether the anode of the X-ray tube rotates or not according to the current of the stator winding.
In order to achieve the above object, a second aspect of the present invention provides a medical imaging apparatus, which includes the X-ray generating device of the above embodiment.
According to the medical imaging equipment provided by the embodiment of the invention, the X-ray generating device provided by the embodiment can output X-rays with small focal points, high power and good quality, so that the imaging quality is good.
Additional aspects and advantages of the invention will be set forth in part in the description which follows and, in part, will be obvious from the description, or may be learned by practice of the invention.
Drawings
The foregoing and/or additional aspects and advantages of the present invention will become apparent and readily appreciated from the following description of the embodiments, taken in conjunction with the accompanying drawings of which:
FIG. 1 is a block diagram of an X-ray generator according to an embodiment of the present invention;
FIG. 2 is a block diagram of a control circuit according to an embodiment of the present invention;
FIG. 3 is a block diagram of the power supply circuit of one embodiment of the present invention;
FIG. 4 is a block diagram of a heating circuit according to an embodiment of the present invention;
FIG. 5 is a block diagram of the feedback circuit of one embodiment of the present invention;
FIG. 6 is a signal waveform diagram of an embodiment of the present invention;
FIG. 7 is a block diagram of a driving circuit according to an embodiment of the present invention;
FIG. 8 is a block diagram of the driving sub-circuit of one embodiment of the present invention;
FIG. 9 is a signal waveform diagram of another embodiment of the present invention;
fig. 10 is a block diagram of a medical imaging apparatus according to an embodiment of the present invention.
Detailed Description
Reference will now be made in detail to embodiments of the present invention, examples of which are illustrated in the accompanying drawings, wherein like or similar reference numerals refer to the same or similar elements or elements having the same or similar function throughout. The embodiments described below with reference to the drawings are illustrative and intended to be illustrative of the invention and are not to be construed as limiting the invention.
An X-ray generating apparatus and a medical imaging device according to an embodiment of the present invention are described below with reference to the drawings.
Fig. 1 is a block diagram of an X-ray generator according to an embodiment of the present invention.
In this embodiment, as shown in fig. 1, the X-ray generating apparatus includes an X-ray tube 6, a power supply circuit 2, a heating circuit 3, a drive circuit 4, a feedback circuit 5, and a control circuit 1.
Wherein, the X-ray tube 6 is used for outputting X-rays; the power supply circuit 2 is connected with the X-ray tube 6, and the power supply circuit 2 is used for applying preset voltage to the X-ray tube 6; the heating circuit 3 is connected with the X-ray tube 6, and the heating circuit 3 is used for applying preset current to a cathode filament of the X-ray tube 6 so as to heat the cathode filament of the X-ray tube 6; the drive circuit 4 is used for driving the anode of the X-ray tube 6 to rotate; the feedback circuit 5 is connected with the X-ray tube 6, and the feedback circuit 5 is used for detecting tube voltage and tube current of the X-ray tube 6; the control circuit 1 is connected with the power circuit 2, the heating circuit 3, the driving circuit 4 and the feedback circuit 5 respectively, the control circuit 1 is used for driving an anode of the X-ray tube 6 to rotate through the driving circuit 4, then preset voltage is applied to the X-ray tube 6 to form tube voltage, the heating circuit 3 is controlled to heat a cathode filament of the X-ray tube 6 to enable the cathode filament to generate electrons, the electrons move under the action of the tube voltage to generate tube current, then the feedback circuit 5 is used for detecting the tube voltage and the tube current of the X-ray tube 6, then the output voltage of the power circuit 2 and the output current of the heating circuit 3 are controlled according to the tube voltage and the tube current respectively, and the anode of the X-ray tube 6 is driven to rotate through the driving circuit 4 again to form closed-loop control. First, in the present embodiment, the rotation of the anode of the X-ray tube 6 is performed by driving the rotation of the anode thereof.
Specifically, the control circuit 1 drives the anode of the X-ray tube 6 to rotate through the driving circuit 4, and then performs closed-loop control on the output voltage of the power supply circuit 2 according to the tube voltage of the X-ray tube 6 fed back by the feedback circuit 5, so that the power supply circuit 2 outputs a stable preset voltage, and the preset voltage is applied to the anode and the cathode of the X-ray tube 6, thereby forming a tube voltage on the X-ray tube 6. Meanwhile, the control circuit 1 performs closed-loop control on the output current of the heating circuit 3 according to the tube current of the X-ray tube 6 fed back by the feedback circuit 5, the heating circuit 3 outputs a stable current to the cathode filament of the X-ray tube 6 to heat the cathode filament of the X-ray tube 6 to generate electrons, the electrons bombard the anode target surface of the X-ray tube under the action of tube voltage to generate X-rays, and the electrons move to form a current which is the tube current of the X-ray tube 6. The feedback circuit 5 detects the tube voltage and the tube current of the X-ray tube 6, and feeds back the detected signals to the control circuit 1 again, thereby realizing the formation of closed-loop control. Meanwhile, the control circuit 1 can also drive the anode target surface of the X-ray tube 6 to rotate according to the driving circuit 4 so as to avoid the electron impact received by a fixed point of the focus, reduce the damage to the anode of the X-ray tube 6 and be beneficial to prolonging the service life of the X-ray tube. The X-ray generating device can output X-rays with small focal points, high power and good quality, so that the imaging quality is good, and the device has a simple structure.
In one example of the present invention, as shown in fig. 2, the control circuit 1 includes: a first pulse width modulation chip 101, a second pulse width modulation chip 102 and a main control chip 103.
The first pulse width modulation chip 101 is connected with the heating circuit 3 and the feedback circuit 5 respectively, and the first pulse width modulation chip 101 is used for obtaining tube current; the second pulse width modulation chip 102 is connected with the power circuit 2 and the feedback circuit 5 respectively, and the second pulse width modulation chip 102 is used for obtaining the tube voltage; the main control chip 103 is connected to the feedback circuit 5, the driving circuit 4, the first pwm chip 101 and the second pwm chip 102, respectively.
Specifically, as shown in fig. 1-2, the main control chip 103 (e.g., a single chip microcomputer may be used) is specifically configured to, when receiving the preheating turn-on command, transmit a preheating turn-on signal to the second pulse width modulation chip 102 by the main control chip 103, so that the second pulse width modulation chip 102 controls the heating circuit 3 to heat the cathode filament of the X-ray tube 6. In this embodiment, referring to fig. 2, a preheating signal switch S3 may be disposed between the main control chip 103 and the second pwm chip 102, and when the main control chip 103 receives the preheating turn-on command, the preheating signal switch S3 is controlled to be closed to transmit the preheating turn-on signal to the second pwm chip 102. Alternatively, the preheating signal switch S3 may be a component having a switching function, such as a photoelectric coupler. After the second pulse width modulation chip 102 receives the preheating turn-on signal, the second pulse width modulation chip 102 sends a filament heating signal to the heating circuit 3, so that the heating circuit 3 heats the cathode filament of the X-ray tube 6, thereby forming a tube current in the X-ray tube 6 and releasing X-rays. Meanwhile, the main control chip 103 also transmits an anode rotation driving signal to the driving circuit 4, so that the driving circuit 4 can drive the anode target surface of the X-ray tube 6 to rotate; the main control chip 103 may also generate a tube voltage set value and a tube current set value, wherein the tube voltage set value and the tube current set value are preset values.
When receiving an X-ray turn-on command, the main control chip 103 transmits a set tube voltage value to the first pulse width modulation chip 101, the first pulse width modulation chip 101 generates an inversion driving signal according to the set tube voltage value and the tube voltage, and the power circuit 2 outputs a voltage to the X-ray tube 6 according to the inversion driving signal to provide the tube voltage for the X-ray tube 6. The feedback circuit 5 transmits the detected tube voltage to the first pwm chip 101 to form a closed loop control of the power circuit 2. Meanwhile, the main control chip 103 also transmits the tube current set value to the second pulse width modulation chip 102, the second pulse width modulation chip 102 generates a filament heating signal according to the tube current set value and the tube current, and transmits the filament heating signal to the heating circuit 3, and the heating circuit 3 heats the cathode of the X-ray tube 6, so that the X-ray tube 6 can generate the tube current. The feedback circuit 5 feeds back the sensed tube current to the second pulse width modulation chip 102, forming a closed loop control of the heating circuit 3. Alternatively, a switch S1 is disposed between the main control chip 103 and the first pwm chip 101, and when the main control chip 103 receives an X-ray turn-on command, the switch S1 may be controlled to be closed to transmit the tube voltage set value to the first pwm chip 101.
Alternatively, referring to fig. 2, a switch S1 may be disposed between the main control chip 103 and the first pwm chip 101, and when the main control chip 103 receives an X-ray turn-on command, the switch S1 may be controlled to be closed to transmit the tube voltage set value to the first pwm chip 101; a switch S2 may be disposed between the main control chip 103 and the second pwm chip 102, and when the main control chip 103 receives an X-ray turn-on command, the switch S2 may be controlled to be closed to transmit a set value of the tube current to the second pwm chip 102, wherein the switches S1 and S2 may both be photocouplers and other devices having a switching function.
As an example, the feedback circuit 5 may further detect a temperature signal and an anode operating signal of the X-ray tube 6, and when the main control chip 103 receives an X-ray turn-on command, the temperature signal and the anode operating signal fed back by the feedback circuit 5 may be first obtained, and then after it is determined that the temperature signal and the anode operating signal are both normal, the tube voltage setting value and the tube current setting value are correspondingly transmitted to the first pwm chip 101 and the second pwm chip 102, respectively.
When receiving the X-ray shutdown command, the main control chip 103 stops transmitting the anode rotation driving signal to the driving circuit 4, and transmits the shutdown signal to the driving circuit 4, so that the driving circuit 4 stops driving the anode target surface of the X-ray tube 6 to rotate, and the X-ray tube 6 is shut down.
Optionally, when at least one of the temperature signal and the anode operation signal fed back by the feedback circuit 5 is abnormal, the main control chip 103 may transmit a shutdown signal to the driving circuit 4, and may also send a fault notification message.
Referring to fig. 2, the feedback circuit 5 may also feed back the tube voltage and the tube current to the main control chip 103, and the main control chip 103 may perform analog-to-digital conversion on the received tube voltage and the received tube current, and display the converted values through a display for viewing.
In one embodiment of the present invention, as shown in fig. 3, the power supply circuit 2 may include: a first rectifier sub-circuit 201, an inverter sub-circuit 202, a boost sub-circuit 203, and a second rectifier sub-circuit 204.
The input end of the first rectifier sub-circuit 201 is connected to an ac power supply (for example, 220V ac power), and the first rectifier sub-circuit 201 is configured to receive a first ac power output by the ac power supply and rectify the first ac power to output a first dc power; the input end of the inverter sub-circuit 202 is connected with the output end of the first rectifier sub-circuit 201, the control end of the inverter sub-circuit 202 is connected with the first pulse width modulation chip 101, and the inverter sub-circuit 202 is used for inverting the first direct current according to an inversion driving signal output by the first pulse width modulation chip 101 to output a second alternating current; the input end of the boost sub-circuit 203 is connected with the output end of the inverter sub-circuit 202, and the boost sub-circuit 203 is used for boosting the second alternating current to output a third alternating current; the input end of the second rectifying sub-circuit 204 is connected to the output end of the boost sub-circuit 203, the output end of the second rectifying sub-circuit 204 is connected to the X-ray tube 6, and the second rectifying sub-circuit 204 is configured to rectify the third alternating current to output a preset voltage.
As an example, the power circuit 2 may further include a filter sub-circuit connected to the output terminal of the first rectifier sub-circuit 201 to filter the first direct current output by the first rectifier sub-circuit 201. The power circuit 2 may further include a voltage stabilizing sub-circuit, and the voltage stabilizing sub-circuit is connected to the filter sub-circuit and configured to stabilize the first dc power after the filtering. Thereby, the second rectifier sub-circuit 204 is facilitated to output a stable voltage.
In one embodiment of the invention, as shown in fig. 4, the heating circuit 3 comprises a push-pull sub-circuit 301 and a transformer 302.
The input end of the push-pull sub-circuit 301 is connected to the second pulse width modulation chip 102, and is configured to receive a heating signal output by the second pulse width modulation chip 102, convert the heating signal into an alternating current required for heating, and output the alternating current from the first output end or the second output end of the push-pull sub-circuit; the transformer 302 includes a first primary coil, a second primary coil and a secondary coil, the first primary coil is connected with the first output end of the push-pull sub-circuit 301, the second primary coil is connected with the second output end of the push-pull sub-circuit 301, the secondary coil is connected with the cathode filament of the X-ray tube 6, and the transformer 302 is used for transforming the alternating current required for heating and transmitting the alternating current after transformation to the cathode filament of the X-ray tube 6 so as to heat the cathode filament of the X-ray tube 6. Thus, the second pulse width modulation chip 102 can control the magnitude of the heating current of the cathode filament of the X-ray tube 6 by the filament heating signal, and can control the magnitude of the tube current of the X-ray tube 6 to obtain a stable state.
In one example of the present invention, as shown in fig. 5, the feedback circuit 5 includes a voltage detection sub-circuit 501 and a current detection sub-circuit 502.
The voltage detection sub-circuit 501 is connected to the X-ray tube 6 and the first pwm chip 101, respectively, and the voltage detection sub-circuit 501 is configured to detect a tube voltage of the X-ray tube 6 and feed the tube voltage back to the first pwm chip 101; the current detection sub-circuit 502 is connected to the X-ray tube 6 and the second pwm chip 102, respectively, and the current detection sub-circuit 502 is configured to detect a tube current of the X-ray tube 6 and feed the tube current back to the second pwm chip 102.
In some examples, as shown in fig. 5, the feedback circuit 5 may also include a zero crossing detection subcircuit 503.
The zero-crossing detection sub-circuit 503 is connected to the ac power supply and the main control chip 103, respectively, and the zero-crossing detection sub-circuit 503 is configured to perform zero-crossing detection on the first ac power output by the ac power supply to output a zero-crossing detection signal, and feed back the zero-crossing detection signal to the main control chip 103. The main control chip 103 is further configured to output an anode rotation driving signal with a preset pulse width after receiving the zero-crossing detection signal for a preset time each time.
Specifically, as shown in fig. 5 and 6, the zero-crossing detection sub-circuit 503 is configured to detect a zero-crossing point of the first ac power output by the ac power supply, the generated zero-crossing detection signal may be a square wave, and transmit the square wave to the main control chip 103 as an external interrupt, the main control chip 103 turns on a timer after receiving the interrupt signal, and outputs an anode rotation driving signal with a preset pulse width after the timer delays for a preset time, so as to drive the anode of the X-ray tube 6 to rotate.
In one example of the present invention, as shown in fig. 5, the feedback circuit 5 further includes a stator detection sub-circuit 506.
The electronic detection sub-circuit 506 is connected to the stator winding and the main control chip 103, respectively, and it is understood that the current of the stator winding determines the rotation of the X-ray tube 6. The stator detection sub-circuit 506 detects the current of the stator winding and feeds the detected current of the stator winding back to the main control chip 103, so that the main control chip 103 can judge the rotation condition of the anode of the X-ray tube 6 according to the current, and further accurately control the X-ray tube 6.
Optionally, referring to fig. 5, the feedback circuit 5 may further include an anode operation detection sub-circuit 504 and a temperature detection sub-circuit 505.
Wherein, the anode operation detection sub-circuit 504 is respectively connected with the X-ray tube 6 and the main control chip 103; the temperature detection sub-circuit 505 is connected to the X-ray tube 6 and the main control chip 103, respectively. The anode operation detection sub-circuit 504 and the temperature detection sub-circuit 505 respectively transmit the anode operation signal and the temperature signal to the main control chip 103, and the main control chip 103 can better acquire the operation condition of the X-ray tube 6 according to the signals, so that the X-ray tube 6 can be better and more safely controlled to work.
In one embodiment of the present invention, as shown in fig. 7, the driving circuit 4 includes a motor M, which may be a single-phase asynchronous motor, a shutdown sub-circuit 401, and a driving sub-circuit 402.
The motor M is used for driving the anode target surface of the X-ray tube to rotate; the shutdown sub-circuit 401 is connected with the main control chip 103 and the stator winding of the motor M respectively, and the shutdown sub-circuit 401 is used for inputting preset low-voltage direct current to the stator winding according to a shutdown signal so as to enable the motor to stop driving the anode target surface of the X-ray tube to rotate; the driving sub-circuit 402 is connected to the main control chip 103 and the stator winding of the motor M, and the driving sub-circuit 402 is configured to control the motor M to drive the anode target surface of the X-ray tube 6 to rotate according to the anode rotation driving signal.
Alternatively, as shown in fig. 7, a switch S4 may be disposed between the ac power source and the stopping sub-circuit 401 and the driving sub-circuit 402, the stationary terminal of the switch S4 may be connected to the ac power source, the first movable terminal of the switch S4 is connected to the stopping sub-circuit 401, and the second movable terminal of the switch S4 is connected to the driving sub-circuit 402. When the main control chip 103 sends a shutdown signal to the shutdown sub-circuit 401, a preset low-voltage direct current can be input to the stator winding through the shutdown sub-circuit 401, so that the rotation of the anode target surface of the X-ray tube 6 can be rapidly stopped; when the anode target surface of the X-ray tube 6 needs to be controlled to rotate, the main control chip 103 controls the stationary terminal of the switch S4 to be connected with the second movable terminal, and transmits an anode rotation driving signal to the driving sub-circuit 402.
In some examples, as shown in fig. 8, the driving sub-circuit 402 includes an optocoupler K1, a switching tube Q1, a triac TH1, and a buck rectifier unit 4021.
A first input end of the optical coupler K1 is connected to a preset power supply (e.g., +5V dc power supply) through a first resistor R1, R1 is a current-limiting resistor, a second input end of the optical coupler K1 is connected to the main control chip 103 to receive an anode rotation driving signal, and a first output end of the optical coupler K1 is grounded through a second resistor R2; a control end B of the switching tube Q1 is respectively connected with a first output end of the optical coupler K1 and one end of the second resistor R2, a first end C of the switching tube Q1 is connected with a second output end of the optical coupler K1 and forms a first node, and a second end E of the switching tube Q1 is grounded; a gate of the bidirectional thyristor TH1 is connected with a first node through a third resistor R3, a first main electrode of the bidirectional thyristor TH1 is connected with a zero line of an alternating current power supply, a second main electrode of the bidirectional thyristor TH1 is connected with one end of a stator winding, and the other end of the stator winding is connected with a live wire of the alternating current power supply; the input end of the step-down rectification unit 4021 is connected to an ac power supply, and the step-down rectification power supply is used for performing step-down rectification processing on the first ac power output by the ac power supply to output a preset dc power.
Specifically, when the anode rotation driving signal is at a low level, the optical coupler K1 is turned on, the switching tube Q1 is turned on, a preset direct current (for example, a 12V direct current) flows out from both ends of the step-down rectifying unit 4021, flows in from the first main electrode of the triac TH1, flows out from the gate, the triac TH1 is turned on, the stator winding is connected to a 220V alternating current, so that the anode rotation of the X-ray tube 6 is controlled, when the zero point of the first alternating current output by the alternating current power supply arrives, the switching tube Q1 is automatically turned off, and when the next anode rotation driving signal arrives, the switching light Q1 is turned on again, and is cycled repeatedly, so that the anode of the X-ray tube 6 is stably rotated. In this embodiment, the isolation of the amplified anode rotation drive signal from the stator current flowing through the stator windings is shown in FIG. 9.
Optionally, referring to fig. 8, the driving sub-circuit 402 further includes a sinking unit 4022, the sinking unit 4022 includes a third capacitor C3 and a seventh resistor R7 connected in series, and two ends of the third capacitor C3 and the seventh resistor R7 connected in series are respectively connected to the first main electrode and the second main electrode of the triac TH 1. The absorption unit 4022 composed of the third capacitor C3 and the seventh resistor R7 is used for recovering excess energy generated when the alternating current is at zero.
As an example, referring to fig. 8, a buck rectifying unit 4021 includes a first capacitor C1, a second capacitor C2, a fourth resistor R4, a fifth resistor R5, a sixth resistor R6, a zener diode D2, and a rectifying diode D1.
Specifically, referring to fig. 8, one end of a first capacitor C1 is connected to the live line L of the ac power supply, the other end of the first capacitor C1 is connected to the anode of a rectifier diode D1, a fourth resistor R4 is connected to a fifth resistor R5 in parallel and is connected to a first capacitor C1 in parallel, a sixth resistor R6 is connected to a second capacitor C2 in parallel, the anode of the second capacitor C2 is connected to the neutral line N of the ac power supply and the cathode of a rectifier diode D1, the cathode of the second capacitor C2 is grounded, the anode of a zener diode D2 is grounded, and the cathode of the zener diode D2 is connected to the anode of a rectifier diode D1. In this specific example, the buck rectifying unit 4021 is configured to buck and rectify the first ac power output by the ac power supply to 12V dc power, specifically, a stable 12V dc voltage is output at two ends of the second capacitor C2 to be used by an amplifying circuit at an output end of the optical coupler K1, when the anode rotation driving signal is low level, the optical coupler K1 is turned on, the triode Q1 is turned on, the 12V dc power at two ends of the second capacitor C2 starts from an anode of the second capacitor C2, enters from a first main electrode of the triac TH1, exits from a gate, and returns to a cathode of the second capacitor C2, the first main electrode and a second main electrode of the triac TH1 are turned on, the stator winding is supplied with 220V ac power, and the anode of the X-ray tube 6 rotates.
In summary, the X-ray generating device of the embodiment of the invention can output small-focus and high-power X-rays by accurately and stably controlling the rotation of the anode target surface of the X-ray tube, so that the imaging quality is good, and the quality of the X-rays can be improved by closed-loop control of the tube voltage and the tube current. In addition, the control module for controlling the heating circuit, the power supply circuit and the driving circuit is integrated, so that the device is simple in structure, and meanwhile, the driving circuit is controlled by the control chip, and the anti-interference capability is high.
Fig. 10 is a block diagram of a medical imaging apparatus according to an embodiment of the present invention.
As shown in fig. 10, the medical imaging apparatus 100 includes the X-ray generation device 10 of the above-described embodiment.
According to the medical imaging equipment provided by the embodiment of the invention, the X-ray generating device provided by the embodiment can output X-rays with small focal points, high power and good quality, so that the imaging quality is good.
In the description herein, references to the description of the term "one embodiment," "some embodiments," "an example," "a specific example," or "some examples," etc., mean that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the invention. In this specification, the schematic representations of the terms used above do not necessarily refer to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples.
In the description of the present invention, it is to be understood that the terms "central," "longitudinal," "lateral," "length," "width," "thickness," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," "clockwise," "counterclockwise," "axial," "radial," "circumferential," and the like are used in the orientations and positional relationships indicated in the drawings for convenience in describing the invention and to simplify the description, and are not intended to indicate or imply that the referenced devices or elements must have a particular orientation, be constructed and operated in a particular orientation, and are therefore not to be considered limiting of the invention.
Furthermore, the terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one such feature. In the description of the present invention, "a plurality" means at least two, e.g., two, three, etc., unless specifically limited otherwise.
In the present invention, unless otherwise expressly stated or limited, the terms "mounted," "connected," "secured," and the like are to be construed broadly and can, for example, be fixedly connected, detachably connected, or integrally formed; can be mechanically or electrically connected; they may be directly connected or indirectly connected through intervening media, or they may be connected internally or in any other suitable relationship, unless expressly stated otherwise. The specific meanings of the above terms in the present invention can be understood by those skilled in the art according to specific situations.
In the present invention, unless otherwise expressly stated or limited, the first feature "on" or "under" the second feature may be directly contacting the first and second features or indirectly contacting the first and second features through an intermediate. Also, a first feature "on," "over," and "above" a second feature may be directly or diagonally above the second feature, or may simply indicate that the first feature is at a higher level than the second feature. A first feature being "under," "below," and "beneath" a second feature may be directly under or obliquely under the first feature, or may simply mean that the first feature is at a lesser elevation than the second feature.
Although embodiments of the present invention have been shown and described above, it is understood that the above embodiments are exemplary and should not be construed as limiting the present invention, and that variations, modifications, substitutions and alterations can be made to the above embodiments by those of ordinary skill in the art within the scope of the present invention.
Claims (11)
1. An X-ray generation device, comprising:
the X-ray tube is connected with the power circuit, the heating circuit and the feedback circuit respectively, and the control circuit is connected with the power circuit, the heating circuit, the driving circuit and the feedback circuit respectively;
wherein the control circuit controls the drive circuit to drive the anode of the X-ray tube to rotate;
the power supply circuit applies a preset voltage to the X-ray tube to form a tube voltage, and the heating circuit applies a preset current to a cathode filament of the X-ray tube to heat the cathode filament of the X-ray tube to generate electrons, wherein the electrons move to an anode of the X-ray tube under the action of the tube voltage to generate a tube current, and X-rays are output through the X-ray tube;
the feedback circuit detects tube voltage and tube current of the X-ray tube and feeds the tube voltage and the tube current back to the control circuit;
the control circuit controls the output voltage of the power circuit and the output current of the heating circuit according to the tube voltage and the tube current.
2. The X-ray generation apparatus of claim 1, wherein the control circuit comprises:
the first pulse width modulation chip is respectively connected with the heating circuit and the feedback circuit and is used for acquiring the tube current;
the second pulse width modulation chip is respectively connected with the power circuit and the feedback circuit and is used for acquiring the tube voltage;
the main control chip is respectively connected with the feedback circuit, the driving circuit, the first pulse width modulation chip and the second pulse width modulation chip, and is used for:
when a preheating starting command is received, transmitting a preheating starting signal to the second pulse width modulation chip so that the second pulse width modulation chip controls the heating circuit to heat a cathode filament of the X-ray tube; transmitting an anode rotation driving signal to the driving circuit to cause the driving circuit to drive the anode of the X-ray tube to rotate; generating a tube voltage set value and a tube current set value;
when an X-ray starting command is received, transmitting the tube voltage set value to the first pulse width modulation chip so that the first pulse width modulation chip performs closed-loop control on the power supply circuit according to the tube voltage set value and the tube voltage; transmitting the tube current set value to the second pulse width modulation chip so that the second pulse width modulation chip performs closed-loop control on the heating circuit according to the tube current set value and the tube current;
and when receiving an X-ray closing command, stopping transmitting an anode rotation driving signal to the driving circuit, and transmitting a stopping signal to the driving circuit to enable the driving circuit to stop driving the anode of the X-ray tube to rotate.
3. The X-ray generating apparatus of claim 2, wherein the power circuit comprises:
the input end of the first rectifier sub-circuit is connected with an alternating current power supply, and the first rectifier sub-circuit is used for receiving a first alternating current output by the alternating current power supply and rectifying the first alternating current to output a first direct current;
the input end of the inverter sub-circuit is connected with the output end of the first rectifier sub-circuit, the control end of the inverter sub-circuit is connected with the first pulse width modulation chip, and the inverter sub-circuit is used for inverting the first direct current according to an inversion driving signal output by the first pulse width modulation chip to output a second alternating current;
the input end of the boosting sub-circuit is connected with the output end of the inverting sub-circuit, and the boosting sub-circuit is used for boosting the second alternating current to output a third alternating current;
and the input end of the second rectifying sub-circuit is connected with the output end of the boosting sub-circuit, the output end of the second rectifying sub-circuit is connected with the X-ray tube, and the second rectifying sub-circuit is used for rectifying the third alternating current to output the preset voltage.
4. The X-ray generating apparatus of claim 2, wherein the heating circuit comprises:
the input end of the push-pull sub-circuit is connected with the second pulse width modulation chip and is used for receiving the heating signal output by the second pulse width modulation chip, converting the heating signal into alternating current required by heating and outputting the alternating current from the first output end or the second output end of the push-pull sub-circuit;
the transformer comprises a first primary coil, a second primary coil and a secondary coil, the first primary coil is connected with a first output end of the push-pull sub-circuit, the second primary coil is connected with a second output end of the push-pull sub-circuit, the secondary coil is connected with a cathode filament of the X-ray tube, and the transformer is used for carrying out voltage transformation on the alternating current required for heating and transmitting the alternating current subjected to voltage transformation to the cathode filament of the X-ray tube so as to heat the cathode filament of the X-ray tube.
5. The X-ray generating apparatus of claim 2, wherein the feedback circuit comprises:
the voltage detection sub-circuit is respectively connected with the X-ray tube and the first pulse width modulation chip and is used for detecting the tube voltage of the X-ray tube and feeding the tube voltage back to the first pulse width modulation chip;
and the current detection sub-circuit is respectively connected with the X-ray tube and the second pulse width modulation chip and is used for detecting the tube current of the X-ray tube and feeding the tube current back to the second pulse width modulation chip.
6. The X-ray generating apparatus of claim 2, wherein the drive circuit comprises:
the motor is used for driving the anode of the X-ray tube to rotate;
the shutdown sub-circuit is respectively connected with the main control chip and a stator winding of the motor, and is used for inputting preset low-voltage direct current to the stator winding according to the shutdown signal so as to enable the motor to stop driving the anode of the X-ray tube to rotate;
and the driving sub-circuit is respectively connected with the main control chip and the stator winding of the motor, and is used for controlling the motor to drive the anode of the X-ray tube to rotate according to the anode rotation driving signal.
7. The X-ray generating apparatus of claim 2, wherein the feedback circuit further comprises:
the zero-crossing detection sub-circuit is respectively connected with the alternating current power supply and the main control chip and is used for performing zero-crossing detection on first alternating current output by the alternating current power supply to output a zero-crossing detection signal and feeding the zero-crossing detection signal back to the main control chip;
the main control chip is further configured to output the anode rotation driving signal with a preset pulse width after receiving the zero-crossing detection signal for a preset time each time.
8. The X-ray generating apparatus of claim 6, wherein the driving sub-circuit comprises:
a first input end of the optical coupler is connected with a preset power supply through a first resistor, a second input end of the optical coupler is connected with the main control chip to receive the anode rotation driving signal, and a first output end of the optical coupler is grounded through a second resistor;
the control end of the switching tube is respectively connected with the first output end of the optical coupler and one end of the second resistor, the first end of the switching tube is connected with the second output end of the optical coupler to form a first node, and the second end of the switching tube is grounded;
the gate pole of the bidirectional thyristor is connected with the first node through a third resistor, a first main electrode of the bidirectional thyristor is connected with a zero line of the alternating current power supply, a second main electrode of the bidirectional thyristor is connected with one end of the stator winding, and the other end of the stator winding is connected with a live wire of the alternating current power supply;
the input end of the voltage reduction rectifying unit is connected with the alternating current power supply, and the voltage reduction rectifying power supply is used for carrying out voltage reduction rectifying processing on the first alternating current output by the alternating current power supply so as to output preset direct current.
9. The X-ray generating apparatus of claim 8, wherein the buck rectifier unit comprises a first capacitor, a second capacitor, a fourth resistor, a fifth resistor, a sixth resistor, a zener diode, and a rectifier diode, wherein,
one end of the first capacitor is connected with a live wire of the alternating current power supply, the other end of the first capacitor is connected with an anode of the rectifier diode, the fourth resistor is connected with the fifth resistor in parallel and connected with the first capacitor in parallel, the sixth resistor is connected with the second capacitor in parallel, an anode of the second capacitor is connected with a zero line of the alternating current power supply and a cathode of the rectifier diode respectively, a cathode of the second capacitor is grounded, an anode of the voltage stabilizing diode is grounded, and a cathode of the voltage stabilizing diode is connected with an anode of the rectifier diode.
10. The X-ray generating apparatus of claim 6, wherein the feedback circuit further comprises:
the stator detection sub-circuit is respectively connected with the stator winding and the main control chip and is used for detecting the current of the stator winding and feeding the current of the stator winding back to the main control chip;
and the main control chip is also used for judging whether the anode of the X-ray tube rotates or not according to the current of the stator winding.
11. Medical imaging device, characterized in that it comprises an X-ray generating apparatus according to any one of claims 1-10.
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| CN202010322913.0A CN113543437A (en) | 2020-04-22 | 2020-04-22 | X-ray generating device and medical imaging apparatus |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN116313703A (en) * | 2023-05-18 | 2023-06-23 | 斯派曼电子技术(苏州工业园区)有限公司 | Rotary anode driver, rotary anode driving method, radiation generating device and control method |
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