KR20240053397A - Appratus for generating x-ray and method thereof - Google Patents

Abstract

This specification proposes an X-ray generating device and method.
Specifically, the X-ray generating device includes a transformer including a primary winding, a secondary winding, and a tertiary winding, a filament power supply unit connected in parallel with the primary winding, and an And, the first end is connected to one end of the tertiary winding, and the second end is connected to the other end of the tertiary winding, one end of the secondary winding, and one end of the cathode.

Description

X-ray generating device and method {APPRATUS FOR GENERATING X-RAY AND METHOD THEREOF}

This specification relates to an X-ray generating device and method, and more specifically, to an X-ray generating device and method capable of capturing low-dose and high-definition images.

X-rays are a type of electromagnetic wave and are used as a non-destructive testing tool in many fields due to their straight propagation, permeability, and differences in absorption characteristics depending on the material properties. As a core device for generating X-rays, X-ray tubes are divided into filament type and carbon nanotube (CNT) type. Existing filament-type X-ray tubes are widely used in medical, industrial, and scientific fields related to X-rays due to their mature technology, stable products, and low prices. The CNT type X-ray tube is a new technology that has not yet been commercialized and its application is limited, while the filament type has a very high market share.

Meanwhile, most X-rays are fired continuously in an analog manner, but as technology develops, X-ray pulsing technology is becoming more important day by day. By pulsing continuous X-ray emission at high speed, moving objects can be photographed more clearly and the amount of radiation exposure received by patients can be significantly reduced. Such high-speed pulsing is possible with CNT-type X-ray tubes. However, the filament type There is a problem.

Public Patent Publication No. 10-2013-0100630

This specification proposes a filament type X-ray generating device and method that allow dose control through high-speed pulsing.

Additionally, this specification proposes an X-ray generating device and method for supplying power to a dose control unit based on a transformer used to heat the filament of an X-ray tube.

In addition, based on the above transformer, this specification proposes an X-ray generation device and method that enable a negative high potential dose control unit to generate high-speed pulsing through insulation.

The technical problems to be achieved in this specification are not limited to the technical problems mentioned above, and other technical problems not mentioned will be clearly understood by those skilled in the art from the description below. You will be able to.

The X-ray generating device of the present specification includes a transformer including a primary winding, a secondary winding, and a tertiary winding, a filament power supply unit connected in parallel with the primary winding, and an X-ray tube whose cathode is connected in parallel with the secondary winding. And, the first end is connected to one end of the tertiary winding, and the second end is connected to the other end of the tertiary winding, one end of the secondary winding, and one end of the cathode.

Additionally, the device of the present specification may further include a bipolar power source, and the bipolar power source may include a positive power source connected to the anode of the X-ray tube and a negative power source connected to the third end of the dose control unit.

Additionally, in the device of the present specification, the cathode of the X-ray tube may be heated based on the filament power source.

Additionally, in the device of this specification, the cathode of the X-ray tube can generate free electrons.

Additionally, in the device of this specification, the X-ray tube can generate X-rays by accelerating free electrons.

Additionally, in the device of the present specification, the dose control unit may receive power from the filament power supply unit.

Additionally, in the device of this specification, the dose control unit may adjust the dose of X-rays generated by the X-ray tube based on the supplied power.

Additionally, in the device of this specification, the dose control unit may include a power supply unit, a signal generation unit, a power amplifier unit, and a switch.

Additionally, in the device of this specification, the power supply unit may rectify the power from the transformer and supply it to at least one of the signal generator, the power amplifier, and/or the switch.

Additionally, in the device of this specification, the signal generator may generate a switching signal.

Additionally, in the device of this specification, the power amplifier may amplify the switching signal.

Additionally, in the device of this specification, the switch may adjust the dose of X-rays based on the power amplifier.

Additionally, in the device of this specification, the primary winding, the secondary winding, and the tertiary winding may be formed of insulated cables.

Additionally, in the device of the present specification, the voltage of the primary winding ( ), the voltage of the secondary pipe line ( ) and the voltage of the tertiary winding ( )silver It has a relationship, where k may be a conversion constant.

In addition, in the X-ray generation method of the present specification, based on a transformer, transferring power from the filament power source to the Generating free electrons, based on the power of the bipolar power supply, generating X-rays by accelerating the free electrons of the X-ray tube, and based on the dose control unit receiving power from the filament power supply, It may include the step of adjusting the dose of X-rays.

According to the present specification, it is possible to implement a filament type X-ray generating device capable of controlling the dose by high-speed pulsing without major structural changes and costs.

In addition, according to the present specification, there is an effect of supplying power to the dose control unit based on the transformer used to heat the filament of the X-ray tube.

In addition, according to the present specification, there is a cost and space saving effect by using the transformer.

In addition, according to the present specification, based on the transformer, there is an effect of enabling the dose control unit of high negative potential to generate high-speed pulsing through insulation.

The effects that can be obtained in this specification are not limited to the effects mentioned above, and other effects not mentioned can be clearly understood by those skilled in the art from the description below. .

The accompanying drawings, which are included as part of the detailed description to aid understanding of the present specification, provide examples of the present specification and explain technical features of the present specification together with the detailed description.
Figure 1 is an example of a circuit diagram for the X-ray generating device proposed in this specification.
FIG. 2A is a diagram for explaining the operation of the X-ray generating device when the switch is in the on state.
FIG. 2B is a diagram for explaining the operation of the X-ray generating device when the switch is in an off state.
Figure 3 is a diagram for explaining the operation of the switch.
Figure 4 is another example of a circuit diagram for the X-ray generating device proposed in this specification.
Figure 5 illustrates the structure of the transformer of Figure 4.
Figure 6 is a diagram for explaining the dose control unit of Figure 4.
Figure 7 shows the output voltage of the transformer and power supply.
Figure 8 is a flowchart for explaining the operating method of the X-ray generating device proposed in this specification.

Hereinafter, preferred embodiments according to the present specification will be described in detail with reference to the attached drawings. The detailed description set forth below in conjunction with the accompanying drawings is intended to illustrate exemplary embodiments of the present disclosure and is not intended to represent the only embodiments in which the disclosure may be practiced. The following detailed description includes specific details to provide a thorough understanding of the disclosure. However, one skilled in the art will understand that the present disclosure may be practiced without these specific details.

In some cases, in order to avoid ambiguity in the concepts of the present specification, well-known structures and devices may be omitted or may be shown in block diagram form focusing on the core functions of each structure and device.

In this specification, '/' means 'and', 'or', or 'and/or' depending on the context.

Figure 1 is an example of a circuit diagram for the X-ray generating device proposed in this specification.

Referring to FIG. 1 , the X-ray generating device 100 may include at least one of a bipolar power supply unit 110, a filament power supply unit 120, an X-ray tube 130, and/or a transformer 140.

The bipolar power source 110 may include at least one of a positive power source 111 and/or a negative power source 112. The cathode of the positive power source 111 and the anode of the negative power source 112 may be connected to ground. And/or, the positive power source 111 or the anode of the positive power source 111 is connected to the anode 131 (or positive electrode) of the X-ray tube 130, and the negative power source 112 or the cathode of the negative power source 112 is connected to the X-ray tube. It may be connected to one end of the cathode 132 (or cathode) of 130 and/or to one end of the secondary winding of transformer 140. The positive power source 111 and the negative power source 112 may supply a high differential voltage or a (bipolar) high voltage to the X-ray tube 130. That is, the positive power source 111 and the negative power source 112 can each generate high voltages of tens of kV relative to ground.

The filament power source 120 may be connected (in parallel) to the primary winding of the transformer 140. The filament power source 120 can generate an alternating current voltage of several volts. The filament power source 120 can generate free electrons by heating the filament 132 on the cathode side of the X-ray tube 130 to 2000°C or more through the transformer 140.

The X-ray tube 130 may include an anode 131 and a cathode 132. For example, the anode 131 of the X-ray tube 130 may be connected (in series) to the positive power source 111. And/or, one end of the cathode 132 of the X-ray tube 130 may be connected to one end of the secondary winding of the transformer 140 and the cathode of the negative power source 112. And/or, the other end of the cathode 132 of the X-ray tube 130 may be connected to the other end of the secondary winding of the transformer 140. The cathode 132 of the X-ray tube 130 is heated based on power supplied from the filament power source 120 and may generate free electrons. Free electrons can be accelerated toward the anode 131 by high-voltage power applied to the anode 131 and the cathode 132. Accordingly, a tube current 170 is formed, and the accelerated moving electrons collide with the anode 131 to generate X-rays. The tube current 170 generated in the can be formed.

However, it is not easy for the For this purpose, a switch may be included in the X-ray generating device 100. That is, to control the dose of X-rays, high-speed switching of tube current can be used.

FIG. 2 is an example of a circuit diagram in which a switch is added to the X-ray generating device of FIG. 1. That is, FIG. 2A is a diagram for explaining the operation of the X-ray generating device 200 when the switch is in the on state, and FIG. 2B is a diagram for explaining the operation of the X-ray generating device 200 when the switch is in the off state.

Referring to FIG. 2A, one end of the switch 250 may be connected to one end of the cathode 232 of the X-ray tube 230 and/or one end of the secondary winding of the transformer 240. And/or, the other end of the switch 250 may be connected to the negative power source 212 of the bipolar power supply unit 210. When the switch 250 is in the on state and the positive power source 211, the negative power source 212, and the filament power source unit 220 operate normally, the tube current 270 may flow and generate X-rays. Here, the positive power source 211 may form a positive high potential part 211-1, and the negative power source 212 may form a negative high potential part 212-1. For example, the positive high potential portion 211-1 may mean a region having a positive high potential. The negative high potential portion 212-1 may refer to a region having a negative high potential.

Referring to Figure 2b, when the switch 250 is in the off state, even if the positive power source 211, the negative power source 212, and the filament power source unit 220 operate normally, the tube current 270 cannot flow and No. Here, the positive power source 211 forms a positive high potential part 211-1 and the negative power source 212 forms a negative high potential part 212-1.

As shown in FIG. 3, the switch 250 can be switched through the supply of power 31 and the input of the switching signal 32, and accordingly, as shown in FIGS. 2A and 2B, on and off operations. By repeating this at high speed, the dose of X-rays can be adjusted. However, as shown in FIGS. 2A and 2B, when the switch 250 is connected to the cathode 232 of the X-ray tube 230, the switch 250 is located in the negative high potential portion 212-1, so the switch 250 ) may occur, and malfunction or insulation breakdown may occur due to the supply of external power 31 and the input of the switching signal 32 based on the ground.

Figure 4 is another example of a circuit diagram for the X-ray generating device proposed in this specification. The X-ray generator 400 of FIG. 4 may be proposed to supply power and a switching signal to a switch located in the negative high potential portion 412-1. That is, the dose control unit 450 receives power through insulation using the transformer 440, and the signal generator 452 that generates a switching signal is installed or included in the dose control unit 450, thereby achieving the above-mentioned The problem can be solved.

Referring to FIG. 4, the X-ray generating device 400 includes at least one of a bipolar power supply unit 410, a filament power supply unit 420, an X-ray tube 430, a transformer 440, and/or a dose control unit 450. can do.

The bipolar power source 410 may include at least one of a positive power source 411 and/or a negative power source 412. The cathode of the positive power source 111 and the anode of the negative power source 112 may be connected to ground. And/or, the positive power source 411 or the anode of the positive power source 411 is connected to the anode 431 of the X-ray tube 430, and the negative electrode of the negative power source 412 or the negative power source 412 is connected to the dose control unit 450 It can be connected to the third stage of . The positive power source 411 and the negative power source 412 can supply a differential voltage (of high voltage) to the X-ray tube 430. For example, the positive power supply 411 may generate a positive (+) high voltage relative to ground. And/or, the negative power source 412 may generate a negative (-) high voltage relative to ground. That is, the positive power source 411 can form a positive high potential part 411-1, and the negative power source 412 can form a negative high potential part 412-1. For example, the positive high potential portion 411-1 may mean a region with high potential. And/or, the negative high potential portion 412-1 may refer to a region having a negative high potential. For example, the bipolar power supply unit 410 may be referred to as a bipolar power supply.

The filament power supply unit 420 may be connected (in parallel) to the primary winding 441 of the transformer 440. That is, one end of the filament power source 420 may be connected to one end of the primary winding 441, and the other end of the filament power source 420 may be connected to the other end of the primary winding 441. The filament power supply unit 420 may generate (alternating current) power/voltage/current to heat the cathode (or filament) 432 of the X-ray tube 430 connected to the secondary winding 442 of the transformer 440. And/or, the filament power supply unit 420 may generate (alternating current) power/voltage/current and supply the power/voltage/current to the dose control unit 450 connected to the tertiary winding 443 of the transformer 440. . For example, the filament power source 420 may be implemented as a filament power source.

The X-ray tube 430 may include an anode 431 and a cathode 432. The cathode 432 may also refer to a filament. And/or, the anode 431 of the X-ray tube 430 may be connected to the anode of the positive power source 411. And/or, the cathode 432 of the X-ray tube 430 may be connected (in parallel) to the secondary winding 442 of the transformer 440. That is, one end of the cathode 432 of the X-ray tube 430 is connected to one end of the secondary winding 442, and the other end of the cathode 432 of the X-ray tube 430 is connected to the other end of the secondary winding 442. You can. And/or, one end of the cathode 432 of the X-ray tube 430 may be connected to the second end of the dose control unit. For example, the cathode 432 of the X-ray tube 430 may be heated based on the filament power source 420. That is, the cathode 432 of the X-ray tube 430 can be heated by receiving power/voltage/current from the filament power source 420 through the transformer 440. And/or, the cathode 432 of the (heated) X-ray tube 430 may generate free electrons. And/or, the X-ray tube 430 may receive power/voltage/current from the bipolar power supply unit 410 to accelerate the free electrons and collide with the anode to generate X-rays. That is, the X-ray tube 430 may be driven by a differential voltage between positive (+) high potential (or high voltage) and negative (-) high potential (or high voltage) to generate X-rays.

Figure 5 illustrates the structure of transformer 440 of Figure 4. 4 and 5, the transformer 440 may include at least one of a primary winding 441, a secondary winding 442, a tertiary winding 443, and/or a core 447. . And/or, each of the primary winding 441, secondary winding 442, and/or tertiary winding 443 may be formed of a high-voltage cable, an insulated cable, and/or a high-voltage insulated cable. That is, each of the primary winding 441, secondary winding 442, and/or tertiary winding 443 can be formed by winding a high-voltage cable, an insulated cable, and/or a high-voltage insulated cable around the core 447. there is. That is, space and cost can be saved by wrapping the first to third windings 441, 442, and 443 around one core 447. For example, the primary winding 441 may be a tens of kV-class insulated cable, and the secondary winding 442 and tertiary winding 443 may be several kV-class (general) insulated cables. As another example, the primary winding 441 may be a several kV-class (general) insulated cable, and the secondary winding 442 and the tertiary winding 443 may be tens of kV-class insulated cables.

And/or, the primary winding 441 may be connected (in parallel) to the filament power supply unit 420. That is, one end of the primary winding 441 may be connected to one end of the filament power supply unit 420, and the other end of the primary winding 441 may be connected to the other end of the filament power supply unit 420. And/or, the secondary winding 442 may be connected (in parallel) to the cathode 432 of the X-ray tube 430. That is, one end of the secondary winding 442 is connected to one end of the cathode 432 of the X-ray tube 430, and the other end of the secondary winding 442 is connected to the other end of the cathode 432 of the X-ray tube 430. You can. And/or, one end of the secondary winding 442 may be connected to the other end of the tertiary winding 442. And/or, one end of the secondary winding 442 may be connected to the second end of the dose control unit 450. And/or, the tertiary winding 443 may be connected (in parallel) to the first and second ends of the dose control unit 450. That is, one end of the tertiary winding 443 may be connected to the first end of the dose control unit 450, and the other end of the tertiary winding 443 may be connected to the second end of the dose control unit 450. And/or, the other end of the tertiary winding 443 may be connected to one end of the secondary winding 442. And/or, the other end of the tertiary winding 443 may be connected to one end of the cathode 432 of the X-ray tube 430.

And/or, the primary winding 441 may be a winding that receives power/power/voltage/current from the filament power supply unit 420. And/or, the primary winding 441 may use a high-voltage cable, an insulated cable, and/or a high-voltage insulated cable that can withstand high voltages of tens of kV. That is, the primary winding 441 may be formed by winding a high-voltage cable, an insulated cable, and/or a high-voltage insulated cable around the core 447. The filament power source 420 may be at a low voltage side potential and the core 447 and the secondary winding 442 and tertiary winding 443 may be at a negative high voltage side potential. And/or, the secondary winding 442 may receive power/power/voltage/current from the primary winding 441 to heat the filament 432 of the X-ray tube 430. That is, tens of W of power/power/voltage/current used to heat the filament 432 can be supplied from the primary winding 441 to the secondary winding 442.

And/or, the secondary winding 442 may receive power/power/voltage/current from the primary winding 441 to heat the filament 432 of the X-ray tube 430 to generate free electrons. And/or, the tertiary winding 443 can receive power from the primary winding 441 to supply the necessary power/power/voltage/current to the dose control unit 450. And/or, because the power consumption of the tertiary winding 443 is much smaller than that of the secondary winding 442, the secondary winding 442 supplies most of the power/power/voltage/current of the filament power supply unit 420. You can receive it. The secondary winding 442 and the tertiary winding 443 are at approximately the same phase, between the primary winding 441 and the secondary winding 442, and/or between the primary winding 441 and the tertiary winding 443. ) A voltage equal to the output voltage of the negative (-) high voltage power supply may be applied.

In the design of transformer 440, the primary voltage or the voltage of the primary winding 441 (or the maximum value of the voltage) is So, the secondary voltage or the voltage of the secondary winding 442 (or the maximum value of the voltage) is As a result, the voltage on the auxiliary winding side or the voltage (or maximum value of voltage) of the tertiary winding 443 is When expressed as , the voltage values of the three windings may have the same relationship as Equation 1.

here, is a conversion constant and can be determined according to the voltage demand of the dose control unit 450 of FIG. 4.

For example, the applied current ( ) can be seen as the range of about 3~4A. And, the resistance value of the filament 432 ( ) may vary depending on the type and capacity of the X-ray tube 430. For example, the resistance value ( ) can range from about 1.3Ω to 1.6Ω. in this case, The minimum value of ( ) and the maximum value ( ) may be 3.9V and 6.4V, respectively, according to Equations 2 to 3.

here, and represents the current and resistance of the filament 432, respectively, and min and max represent the minimum and maximum values, respectively.

, The effective value of is 4~6.5V during normal operation, and the range may vary. The value of can also change. for example, When is set to 0.4, the range of the root mean square (rms) value of the alternating voltage of the auxiliary winding or tertiary winding 443 may be 9.75 to 16 V according to Equations 4 and 5.

Since the voltage of the auxiliary winding or tertiary winding 443 has a fluctuation range of 22% up and down, the power amplifier 453, which will be described later with reference to FIG. 6, is necessary to supply stable power to the dose control unit 440. You can.

For example, the transformer 440 may be referred to as an isolation transformer or a high-voltage isolation transformer.

The first and second ends of the dose control unit 450 may be connected (in parallel) to the tertiary winding 443, and the third end may be connected to the negative power source 412. That is, the first end may be connected to one end of the tertiary winding 443, and the second end may be connected to the other end of the tertiary winding 443. And/or, the second stage may be connected to one end of the secondary winding 442. And/or, the second end may be connected to one end of the cathode 432 of the X-ray tube 430. For example, the first and second stages may be power supply stages, and the third stage may be a negative high voltage connection stage. The dose control unit 450 may receive AC power or (AC) power/voltage/current from the filament power supply unit 420 through the transformer 440. And/or, the dose control unit 450 may adjust the dose of X-rays generated in the X-ray tube 430 based on the supplied (alternating current) power/power/voltage/current. For example, the dose control unit 450 can control the dose of X-rays generated in the there is.

Figure 6 is a diagram for explaining the dose control unit of Figure 4.

Referring to FIG. 6, the dose control unit 450 may include at least one of a power supply unit 451, a signal generation unit 452, a power amplifier 453, and/or a switch 454.

The transformer 440 may supply power/power/voltage/current to at least one of the power supply unit 451, signal generation unit 452, power amplifier 453, and/or switch 454.

The power supply unit 451 rectifies and stabilizes the alternating current (AC) power/AC power/AC voltage/AC current supplied from the transformer 440 to the power amplifier 453, signal generator 452, and switch. It is possible to supply power/power/voltage/current that meets the standards of (454). For example, the power supply unit 451 may be referred to as a power supply unit.

The signal generator 452 can adjust the frequency and duty cycle to generate a signal (or switching signal) that allows the switch 454 to switch at high speed. For example, the signal generator 452 may be composed of a timer circuit, a resonance circuit, and a programmable device. For example, the signal generator 452 may be referred to as a switching signal generation unit.

The power amplifier 453 may be a device that allows the switch 454 to switch from several kHz to hundreds of kHz. And/or, the power amplifier 453 may amplify the switching signal. And/or, the power amplifier 453 may receive power/power/voltage/current from the power supply unit 451 and receive a switching signal from the signal generator 452 to drive the switch 454. For example, the power amplifier 453 may be referred to as a driving power amplifier or a semiconductor switch driver unit.

The switch 454 can be switched at high speed by the power amplifier 453. And/or, as the switch 454 switches at high speed, the tube current in the X-ray tube 430 may flow or be cut off. And/or, the switch 454 may adjust the dose of X-rays based on the power amplifier. For example, the switch 454 may be a metal-oxide-semiconductor field-effect transistor, an insulated gate bipolar transistor (IGBT), or the like. For example, the drain/collector of the switch 454 is connected to the cathode 432 of the X-ray tube 430, and the source/emitter is connected to the negative power 412 or It can be connected to the negative high voltage output terminal.

For example, the dose control unit 450 may be referred to as a perfusion switching module, a dose control module, or a bipolar switching module.

The X-ray generating device described with reference to FIG. 6 can be supplemented by the content described with reference to FIGS. 1 to 5 .

Figure 7 shows the output voltage of the transformer 440 and the power supply unit 451 at a minimum driving current of 3A of the filament 432. In the waveform, yellow (C1) represents the voltage of the primary winding 441, red (C2) represents the voltage of the secondary winding 442, and blue (C3) represents the voltage of the tertiary winding 443. Green (C4) indicates a stable voltage output by the power supply unit 451 of FIG. 6. Referring to FIG. 7, the voltages of the primary winding 441 and the secondary winding 442 are the same, and the power supply unit 451 supplies a stable voltage of 15V by rectifying the output voltage of the tertiary winding 443. You can check that.

Figure 8 is a flowchart for explaining the operating method of the X-ray generating device proposed in this specification.

Referring to FIG. 8, the X-ray generating device may transmit power from the filament power source to the X-ray tube and the dose control unit based on the transformer in step S810.

And/or, the X-ray generating device may generate free electrons by heating the cathode of the X-ray tube based on the power of the filament power supply unit in step S820.

And/or, the X-ray generating device may generate X-rays by accelerating free electrons of the X-ray tube based on the power of the bipolar power supply in step S830.

And/or, the X-ray generating device may adjust the dose of X-rays in step S840, based on the dose control unit that receives power from the filament power supply unit.

Since the operation of the X-ray generating device described with reference to FIG. 8 is the same as the operation of the X-ray generating device described with reference to FIGS. 1 to 7, detailed descriptions thereof will be omitted.

In this specification, power may be applied instead of power, voltage, or current.

According to the above-described device/method of this specification, in a system using a filament-type

In addition, according to the above-described device/method of this specification, the advantages of high-speed X-ray pulsing can be utilized in a wider range of fields at a relatively low price and with little system variation.

The embodiments described above combine the elements and features of the present specification in a predetermined form. Each component or feature should be considered optional unless explicitly stated otherwise. Each component or feature may be implemented in a form that is not combined with other components or features. Additionally, it is possible to configure an embodiment of the present invention by combining some components and/or features. The order of operations described in embodiments of the present invention may be changed. Some features or features of one embodiment may be included in other embodiments or may be replaced with corresponding features or features of other embodiments. It is obvious that claims that do not have an explicit reference relationship in the patent claims can be combined to form an embodiment or included as a new claim through amendment after filing.

Embodiments according to the present specification may be implemented by various means, for example, hardware, firmware, software, or a combination thereof. In the case of implementation by hardware, an embodiment of the present invention includes one or more application specific integrated circuits (ASICs), digital signal processors (DSPs), digital signal processing devices (DSPDs), programmable logic devices (PLDs), and FPGAs ( It can be implemented by field programmable gate arrays, processors, controllers, microcontrollers, microprocessors, etc.

In the case of implementation by firmware or software, an embodiment of the present invention may be implemented in the form of a module, procedure, function, etc. that performs the functions or operations described above. Software code can be stored in memory and run by a processor. The memory is located inside or outside the processor and can exchange data with the processor through various known means.

It is obvious to those skilled in the art that the present specification can be embodied in other specific forms without departing from the essential features of the present specification. Accordingly, the above detailed description should not be construed as restrictive in all respects and should be considered illustrative. The scope of this specification should be determined by reasonable interpretation of the appended claims, and all changes within the equivalent scope of this specification are included in the scope of this specification.

Claims (15)

A transformer comprising a primary, secondary and tertiary winding;
A filament power supply connected in parallel with the primary winding;
an X-ray tube whose cathode is connected in parallel with the secondary winding; and
An X-ray generating device including a dose control unit whose first end is connected to one end of the tertiary winding, and whose second end is connected to the other end of the tertiary winding, one end of the secondary winding, and one end of the cathode. According to paragraph 1,
Further comprising a bipolar power supply,
The bipolar power supply unit includes a positive power source connected to the anode of the X-ray tube and a negative power source connected to a third stage of the dose control unit. According to paragraph 1,
An X-ray generating device in which the cathode of the X-ray tube is heated based on the filament power source. According to paragraph 1,
The cathode of the X-ray tube is an X-ray generating device that generates free electrons. According to paragraph 1,
The X-ray tube is an X-ray generating device that generates X-rays by accelerating free electrons. According to paragraph 1,
The dose control unit is an X-ray generating device that receives power from the filament power supply unit. According to paragraph 1,
The dose control unit is an X-ray generating device that adjusts the dose of X-rays generated in the X-ray tube based on the supplied power. According to paragraph 1,
The dose control unit is an X-ray generating device including a power supply unit, a signal generation unit, a power amplification unit, and a switch. According to clause 8,
The power supply unit rectifies power from the transformer and supplies it to at least one of the signal generator, the power amplifier, and/or the switch. According to clause 8,
The signal generator is an X-ray generator that generates a switching signal. According to clause 8,
The power amplifier is an X-ray generating device that amplifies a switching signal. According to clause 8,
The switch is an X-ray generating device that adjusts the dose of X-rays based on the power amplifier. According to paragraph 1,
The primary winding, the secondary winding, and the tertiary winding are formed of an insulated cable. According to paragraph 1,
The voltage of the primary winding ( ), the voltage of the secondary pipe line ( ) and the voltage of the tertiary winding ( ) has the relationship of Equation 1,
[Equation 1]

Here, k is an X-ray generator where k is a conversion constant. Based on a transformer, transferring power from the filament power source to the X-ray tube and the dose control unit;
Generating free electrons by heating the cathode of the X-ray tube based on the power of the filament power supply unit;
generating X-rays by accelerating the free electrons of the X-ray tube based on the power of the bipolar power supply;
An X-ray generation method comprising adjusting the dose of the X-ray based on the dose control unit receiving power from the filament power supply unit.