JP5201017B2 - X-ray generator and X-ray imaging apparatus having the same - Google Patents

Description

  The present invention relates to an X-ray generator having an X-ray tube built therein, and an X-ray imaging apparatus having the X-ray generator.

  The X-ray imaging apparatus is generally used for nondestructive inspection and the like. Such an X-ray imaging apparatus has an X-ray generation apparatus incorporating an X-ray tube that generates X-rays.

  FIG. 7 is a diagram for explaining the configuration of a conventional X-ray generator. The X-ray tube 51 includes a container 52 whose inside is a vacuum, a cathode electrode 53 that emits electrons E, and a target electrode 54 that the electrons E collide with. When the electron E collides with the target electrode 54, X-rays are generated therefrom, and the X-rays are radiated outward from a window 52a provided in the container 52.

  The cathode electrode 53 is connected to the first power supply 61, and the target electrode 54 is connected to the second power supply 62. The target electrode 54 has a higher potential than the cathode electrode 53. A grid electrode 55 is provided at a position where the cathode electrode 53 and the target electrode 54 are interposed. The grid electrode 55 is connected to the ground G and has a potential of 0V. Note that the return lines of the first power supply 61 and the second power supply 62 are connected to the ground. As an X-ray generator having such a configuration, for example, there is one described in Patent Document 1. As a circuit configuration of the first power supply 61 for applying a potential to the cathode electrode 53, a circuit using a Cockcroft-Walton circuit as shown in FIG.

  An electric circuit according to a conventional configuration will be briefly described with reference to FIG. In FIG. 8, for ease of explanation, necessary elements are extracted from FIG. 16 of Patent Document 2 and reconfigured, and are described as a first power supply 61 and resistors R3 and R6. The first power supply 61 supplies a DC voltage corresponding to the control command value V, and the output P 1 on the high potential side is connected to the cathode electrode 53. The low-potential side output P2 is connected to the cathode electrode 53 via the bypass resistor R6 and to the ground G via the current detection resistor R3.

  When the control command value V is set, the first power supply 61 provides a control voltage corresponding to the control command value V between the outputs P1 and P2. Since the output P1 is connected to the cathode electrode 53, the voltage of the cathode electrode 53 becomes the control voltage. An amount of electrons E corresponding to the control voltage flows from the cathode electrode 53 toward the target electrode 54. That is, a tube current A in the direction opposite to the direction of the electrons E flows.

  The tube current A flows from the second power source 62 to the cathode electrode 53 through the target electrode 54, but cannot flow into the first power source 61. Therefore, a bypass resistor R6 is provided. The tube current A flows through the current detection resistor R3 through the bypass resistor R6 and flows to the return line of the second power source 62 through the ground G.

  Since the bypass resistor R6 is located between P1 and P2 that are the outputs of the first power supply 61, the current B also flows from the first power supply 61.

International Publication No. 2008/062519 Pamphlet Japanese Patent No. 2,634,369

However, the conventional X-ray generator has the following problems.
In the conventional circuit, when the set voltage of the control command value V is lower than a balanced voltage described later, the output P1, that is, the voltage of the cathode electrode 53 cannot be followed.

  In the X-ray tube, a larger tube current A flows as the potential of the cathode electrode 53 is lower than the grid electrode 55. Therefore, if it is attempted to reduce the set voltage of the control command value V in order to flow a large amount of tube current A, the tube current A flowing into the bypass resistor R6 increases, and the voltage drop in the bypass resistor R6 increases. Then, the potential of the cathode electrode 53 viewed from the ground G is pushed up.

  As described above, when the potential of the cathode electrode 53 is increased, the tube current A is decreased. As described above, when the tube current A is increased to a certain extent (as the voltage of the cathode electrode 53 is decreased), the potential of the cathode electrode 53 is increased and the tube current A is further decreased. Therefore, the voltage of the cathode electrode 53 reaches a certain equilibrium state. Thus, the voltage of the cathode electrode 53 cannot be lower than a voltage that balances with the voltage drop of the bypass resistor R6 caused by the tube current A that can be caused to flow by the voltage.

  By the way, by reducing the value of the bypass resistor R6, the balanced voltage of the cathode electrode 53 can be lowered. However, if so, the current B flowing from the first power supply 61 becomes large, and the capacity of the first power supply 61 must be increased. Further, since the power consumption of the bypass resistor R6 increases and the heat generation amount of the bypass resistor R6 and the first power supply 61 also increases, the value that the bypass resistor R6 can take has a practical limit. Although a current detection resistor R3 exists in series with the bypass resistor R6 on the circuit, the value of the current detection resistor R3 can take a sufficiently small value, which is caused by a voltage drop at the current detection resistor R3. The impact is negligible.

  As described above, the fact that the voltage of the cathode electrode 53 does not fall below the above-mentioned balanced voltage means that there is a range in which the current cannot flow regardless of the ability of the X-ray tube to flow the tube current. This means that the amount of X-rays that can be reduced is less than the original capability, and as a result, the X-ray output that should originally be obtained from the X-ray tube cannot be extracted to the maximum.

  The present invention has been made in view of such circumstances, and an object thereof is to suppress energy and heat generation that are wasted in the first power supply 61 and the bypass resistor R6 that apply a control voltage to the cathode electrode 53. An object of the present invention is to provide an X-ray imaging apparatus equipped with an improved performance of an X-ray generator by expanding the control range to obtain the maximum X-ray output originally obtained from the X-ray tube.

In order to solve the above-described problems, the present invention has the following configuration.
That is, the invention according to claim 1 is connected to a cathode electrode that emits electrons, a target electrode that collides with electrons to generate X-rays, and a ground for controlling the amount of electrons passing between them. An X-ray tube having a grid electrode, a target voltage generator for applying a tube voltage to the target electrode and supplying a tube current, a cathode voltage generator having a high potential terminal and a low potential terminal, and a high potential terminal A diode having a cathode connected to the cathode electrode of the X-ray tube, a resistor connected to a position between the anode and the low potential terminal, a base connected to the anode, and a cathode electrode of the X-ray tube And a transistor having a collector connected to the low potential terminal, and the low potential terminal is connected to the ground directly or through current detection means. The one in which the features.

  [Operation / Effect] According to the configuration of the present invention, the diode, the transistor, and the resistor are connected in the above-described relationship, so that the voltage of the cathode electrode of the X-ray tube is maintained at a predetermined voltage. The tube current that flows from the target electrode that emits electrons toward the cathode electrode that emits electrons can be bypassed to the ground through the transistor.

  This circuit operates as follows. That is, the voltage to be output to the cathode electrode of the X-ray tube output to the high potential terminal of the cathode voltage generator is applied to the cathode electrode through the diode. On the other hand, when a tube current flows from the cathode electrode, it is blocked by the diode, so that the voltage of the cathode electrode increases. Then, a current flows from the emitter of the transistor toward the base, and a current-amplified current flows from the emitter to the collector. As a result, the tube current flowing into the cathode electrode is bypassed to the ground through the transistor, and reaches an equilibrium state in the vicinity where the potential difference between the emitter and base of the transistor is eliminated. That is, the voltage of the cathode electrode of the X-ray tube is maintained in the vicinity of the voltage to be output to the cathode electrode regardless of the amount of tube current flowing in.

  Further, according to the configuration of the present invention, since the flowing tube current is bypassed by the transistor, it can be connected to the ground with a low impedance. Therefore, even if the tube current increases, it is possible to follow the voltage of the cathode electrode of the X-ray tube to a low voltage. In other words, it is possible to control the cathode electrode voltage to be set lower, which is not possible with the conventional apparatus.

  Further, the invention according to claim 2 is the X-ray generator according to claim 1, further comprising current detection means connected to a position between the low potential terminal and the ground, and a feedback control unit, wherein the current detection means Is fed back to the cathode voltage generator through the feedback controller.

  [Operation / Effect] According to the above-described configuration, the signal from the current detection means is fed back to the cathode voltage generator through the feedback controller. As a result, the voltage output from the cathode voltage generator is recursively changed, and the tube current can be made to follow the tube current command value from the outside.

  The above configuration shows a specific mode of recursive voltage adjustment of the cathode voltage control unit including the cathode voltage generation unit. That is, the above-described X-ray generator includes a current detection unit. Thereby, the magnitude of the tube current of the X-ray tube can be known. By feeding back the magnitude of this tube current to the cathode voltage generation section through the feedback control section, the tube current can be made to follow the tube current command value from the outside.

  According to a third aspect of the present invention, in the X-ray generator according to the first aspect, the low potential terminal is directly connected to the ground, and the current detection means detects the tube current supplied from the target voltage generation unit. Further, a feedback control unit is further provided, and a signal from the current detection means is fed back to the cathode voltage generation unit through the feedback control unit.

  [Operation / Effect] The above-described configuration shows a specific mode of recursive voltage adjustment of the cathode voltage control unit including the cathode voltage generation unit. That is, the above-described current detection means has a function of detecting the current supplied from the target voltage generator to the X-ray tube. By feeding back the signal output from the current detection means to the cathode voltage generator through the feedback controller, the tube current can be made to follow the tube current command value from the outside.

  According to a fourth aspect of the present invention, in the X-ray generator according to the first aspect, the low-potential terminal is directly connected to the ground and detects the amount of X-rays output from the target electrode. And a feedback control unit, and a signal from the X-ray dose detection means is fed back to the cathode voltage generation unit through the feedback control unit.

  [Operation / Effect] According to the above-described configuration, the X-ray generator includes the X-ray dose detection means. Thereby, the magnitude of the X-ray dose generated from the X-ray tube can be known. Since the generated X-ray dose is proportional to the tube current, the tube current is controlled by feeding back the magnitude of this X-ray dose to the cathode voltage generator through the feedback control unit, and the X-ray dose command value from the outside It is possible to follow the generated X-ray dose.

  An invention according to claim 5 is an X-ray imaging apparatus including the X-ray generation apparatus according to any one of claims 1 to 4, wherein X-ray detection means for detecting X-rays, An image generation unit that generates an X-ray fluoroscopic image based on a signal output from the line detection unit and a display unit that displays the X-ray fluoroscopic image are provided.

  [Operation / Effect] The configuration described above shows a specific mode of the X-ray generator. That is, the above-described configuration includes the X-ray generator according to the present invention as an X-ray generation source. Thereby, it is possible to provide an X-ray imaging apparatus capable of various controls.

  According to the configuration of the present invention, the tube current flowing from the target electrode that emits X-rays toward the cathode electrode that emits electrons is maintained through the transistor with low impedance while the voltage of the cathode electrode of the X-ray tube is maintained at a predetermined voltage. Can be bypassed to ground.

  Therefore, it is possible to follow the voltage of the cathode electrode to a low voltage even if the tube current increases. In other words, it is possible to control the cathode electrode voltage to be set lower, which is not possible with the conventional apparatus. As a result, the performance of the X-ray generator can be improved by taking out the X-ray output that should be originally obtained from the X-ray tube to the maximum, and an X-ray imaging apparatus including the same can be provided.

  In addition, it is possible to suppress wasteful energy and heat generation by the first power supply and the bypass resistor that apply the control voltage to the cathode electrode of the conventional device.

1 is a schematic cross-sectional view illustrating a configuration of an X-ray tube according to Embodiment 1. FIG. 3 is a functional block diagram of a tube current control unit of the X-ray generator according to Embodiment 1. FIG. FIG. 3 is a circuit diagram illustrating an operation of a cathode electrode control unit of the X-ray tube according to Embodiment 1. 6 is a functional block diagram illustrating an X-ray imaging apparatus according to Embodiment 2. FIG. It is a functional block diagram of the X-ray generator which concerns on 1 modification of this invention. It is a functional block diagram of the X-ray generator which concerns on 1 modification of this invention. It is a schematic sectional drawing which concerns on a conventional structure. It is a functional block diagram concerning a conventional configuration.

  The configuration of the X-ray generator according to Embodiment 1 will be described below with reference to the drawings.

  FIG. 1 is a schematic cross-sectional view illustrating the configuration of the X-ray tube according to the first embodiment. In Example 1, an electron gun and a target electrode are disposed so as to emit X-rays in a direction orthogonal to the optical axis of the electron beam, and X-rays are generated by colliding the electron beam B against the target electrode. A reflection type X-ray tube will be described as an example. In the first embodiment, a sealed X-ray tube configured by vacuum-sealing the container will be described as an example.

  As shown in FIG. 1, an electron gun 3 and a target electrode 4 are accommodated in a vacuum vessel 2, and an electron beam B irradiated from the electron gun 3 is caused to collide with the target electrode 4, thereby causing a collision site (X-ray generation point). The X-ray tube 1 is configured to take out the X-rays generated from the X-ray from an X-ray window 2 b provided in the vacuum vessel 2.

  The electron gun 3 includes a cathode electrode 3a that emits an electron beam B and an intermediate electrode. Among these intermediate electrodes, a first electrode 3b, a second electrode 3c, and a third electrode 3d are sequentially formed from the cathode electrode 3a side. The cathode electrode 3a is heated by a heater (not shown). When the cathode electrode 3a becomes high temperature, electrons are easily emitted from the cathode electrode 3a.

  Next, the configuration of the electrical system in the X-ray generator will be described with reference to FIGS. 1 and 2. The cathode electrode 3 a in the X-ray tube 1 is connected to the cathode voltage controller 82, and the target electrode 4 is connected to the target voltage generator 17. The potential of the cathode electrode 3a is several hundred volts, whereas the target electrode 4 is about 100 kV. Since the potential of the target electrode 4 is much higher than the potential of the cathode electrode 3a, electrons flow from the cathode electrode 3a toward the target electrode 4. That is, a current flows from the target electrode 4 toward the cathode electrode 3a. This current is called tube current A.

  The connection between the cathode voltage control unit 82 and the cathode electrode 3a, which is the most characteristic configuration in the first embodiment, will be described. As shown in FIG. 2, the cathode voltage generator S1 includes an inverter 13, a transformer T, a Cockcroft-Walton circuit 11, and a filter circuit 12. The node N1 is an output terminal on the high potential side of the cathode voltage generator S1, and the node N2 is an output terminal on the low potential side.

  The control command value generation unit 25 sends a tube current command value CC to the tube current control unit 16 related to the cathode electrode 3a, and sends a tube voltage command value CV to the target voltage generation unit 17 related to the target electrode 4. ing. The tube current control unit 16 adjusts the tube current of the X-ray tube according to the tube current command value CC, and the target voltage generation unit 17 adjusts the voltage of the target electrode 4 according to the tube voltage command value CV. The tube current control unit 16 corresponds to the feedback control unit of the present invention.

  The operation of the cathode voltage generator S1 will be briefly described. The inverter 13 generates an AC voltage having an amplitude corresponding to the control command value V from the tube current control unit 16 and applies the AC voltage to the primary side of the transformer T. From the secondary side of the transformer T, an AC voltage boosted in accordance with the winding ratio of the transformer is output, and further doubled by a Cockcroft-Walton circuit 11 comprising capacitors C1, C2, and diodes D1, D2. Rectified to voltage. The rectified DC voltage is output to the node N1 after the ripple is reduced by the filter circuit 12 including the resistor R1 and the capacitor C3.

  The bypass circuit 14 connected to the end is provided for supplying a control voltage to the cathode electrode 3a and bypassing the flowing tube current A to the ground G. The bypass circuit 14 includes a diode, a resistor, and a PNP bipolar transistor.

  The diode D3 is connected to a position via the node N1 (high potential terminal) and the cathode electrode 3a, and the side connected to the node N1 is the anode a and the side connected to the cathode electrode 3a is the cathode k. . The resistor R2 is provided at a position between the anode a of the diode D3 and the node N2 (low potential terminal). The base B of the transistor Q is connected to the anode a of the diode D3, and the emitter E is connected to the cathode k of the diode D3. The collector C is connected to the node N2 and is also connected to the ground G via the current detection resistor R3. The current detection resistor R3 corresponds to the current detection means 15 of the present invention. Other current detection methods such as a current detector using a Hall element may be used instead of the current detection resistor R3.

  The operation of the bypass circuit 14 will be described with reference to FIG. The voltage at the node N1 determined by the cathode voltage generator S1 is a control voltage to be applied to the cathode electrode 3a of the X-ray tube, and is applied to the cathode electrode 3a through the diode D3.

  On the other hand, even if a tube current A of an amount corresponding to the voltage of the cathode electrode 3a flows from the cathode electrode 3a, the diode does not flow from the cathode to the anode, so the tube current A flows in the direction of the node N1. There is nothing.

Then, since the potential of the emitter E of the transistor Q becomes higher than the potential of the base B, a base current iEB flows from the emitter E toward the base B. Thereafter, the base current iEB flows to the ground G side through the resistor R2. The base current iEB is amplified by the transistor Q, and the collector current iEC flows from the emitter E to the collector C. The amount can be expressed by the following equation 1 where the current amplification factor of the transistor Q is HFE.
iEC = iEB x HFE (1)

This is because the voltage of the cathode electrode 3a of the X-ray tube is the same VK, and the values of the resistor R6 and the resistor R2 are the same as compared to the bypass current flowing through the bypass resistor R6 of the conventional configuration shown in FIG. When HFE is 100, the bypass current IBP1 that can flow in the conventional configuration is IBP1 = VK / R6, whereas the bypass current IBP2 that can flow in the configuration of the first embodiment is It can be expressed as
IBP2 = iEB + iEC = (1 + HFE) × iEB = 101 × VK / R2 = 101 × IBP1 (2)

  That is, it has the ability to bypass a current that is 101 times that of the conventional configuration. This indicates that the impedance from the cathode electrode 3a to the ground G is very low.

  Actually, since the current of 101 times is not passed, the value of the resistor R2 can be set to a value sufficiently larger than the bypass resistor R6, and the current flowing from the cathode voltage generator S1 to the resistor R2 can be reduced. It becomes possible. As a result, the capacity of the cathode voltage generator S1 and the resistor R2 can be reduced, and heat generation can also be reduced.

  As described above, according to the configuration of the first embodiment, since the tube current A flowing into the cathode electrode 3a is bypassed with a low impedance with respect to the ground G, the potential of the cathode electrode 3a quickly decreases, and the transistor The equilibrium state is reached in the vicinity where the potential difference between the emitter E and the base B of Q is eliminated. That is, the potential of the cathode electrode 3a of the X-ray tube is maintained in the vicinity of the control voltage of the node N1 to be output to the cathode electrode regardless of the amount of the tube current A flowing in.

  Therefore, by adopting the configuration of the first embodiment, the voltage drop that occurs in the conventional bypass resistor R6 does not occur, and the X-ray tube reaches about 0 V where the potential difference between the emitter E and the base B of the transistor Q cannot be obtained. The cathode electrode 3a can be made to follow the control voltage of the node N1.

  In the first embodiment, the tube current A that has passed through the bypass circuit 14 is returned to the ground G through the current detection resistor R3. Here, the current detection resistor R3 has a sufficiently small resistance value so as not to greatly affect the potential of the cathode electrode 3a. When the tube current A flows through the current detection resistor R3, a voltage proportional to the amount of the current is generated at both ends of the current detection resistor R3. That is, the voltage at the node N2 is a voltage proportional to the tube current A. The node N2 is connected to the feedback input of the tube current control unit 16 and performs feedback control by the tube current control unit 16.

  That is, it is possible to control so that the tube current command value from an X-ray imaging apparatus or the like (not shown) and the tube current A of the X-ray tube are always equal.

  Next, the configuration of the X-ray imaging apparatus 21 according to the second embodiment will be described. As shown in FIG. 4, the X-ray imaging apparatus 21 according to the second embodiment includes a housing 22, an X-ray tube 23 provided on the lower side of the housing 22, and a flat panel detector (FPD) provided on the upper side. 24. In addition, the X-ray imaging apparatus 21 includes an X-ray tube control unit 26 that controls the X-ray tube 23 and an image generation unit 31 that receives the output of the FPD 24. The FPD corresponds to the X-ray detection unit of the present invention, and the image generation unit corresponds to the image generation unit of the present invention.

  The display unit 28 provided in the housing 22 displays the X-ray fluoroscopic image generated by the image generation unit 31, displays the operator's input, and displays various parameters related to X-ray irradiation. It is. The display unit corresponds to display means of the present invention.

  The input unit 27 inputs an operator's instruction, and the main control unit 35 controls the units 26 and 31 in an integrated manner. The tube current control unit 16 and the target voltage generation unit 17 in the first embodiment are included in the X-ray tube control unit 26 in the second embodiment, and the tube current command value and the tube voltage command in the first embodiment. The value is given from the main control unit 35 in the second embodiment.

  A sliding door 22a is attached to the housing 22, and the sliding door 22a can be opened and closed by moving a handle 22b attached thereto. When the sliding door 22a is opened, a mounting table for mounting the inspection object appears inside the housing 22. The operator places the inspection object on the mounting table and closes the sliding door 22a before photographing. In order to prevent the operator from being accidentally exposed to X-rays, whether the sliding door 22a is securely closed as an interlock mechanism is detected by a door switch (not shown) and sent to the main control unit 35. Controls whether or not irradiation is possible.

  When the operator gives an instruction to start imaging through the input unit 27, X-rays are emitted from the X-ray tube 23, pass through the inspection target, and enter the FPD 24. The FPD 24 sends detection data indicating a planar distribution of the intensity of incident X-rays to the image generation unit 31. Based on this, the image generation unit 31 generates an X-ray fluoroscopic image in which a fluoroscopic image to be inspected is reflected. The X-ray fluoroscopic image is displayed on the display unit 28, and the acquisition of the X-ray fluoroscopic image in the X-ray imaging apparatus 21 ends.

  As described above, the configuration of the second embodiment shows a specific aspect of the X-ray imaging apparatus using the X-ray generator. That is, the above-described configuration includes the X-ray generator according to the first embodiment as an X-ray generation source. Thereby, the X-ray imaging apparatus 21 which can perform more various controls can be provided.

  The present invention is not limited to the configuration of each of the embodiments described above, and can be modified as follows.

  (1) The configuration of the transistor Q in each of the above embodiments is not limited to the bipolar type, and a unipolar type may be used.

  (2) Each embodiment described above is an industrial apparatus, but the present invention can also be applied to a medical apparatus or a nuclear apparatus.

  (3) Each embodiment described above uses a sealed X-ray tube, but can also be applied to an open X-ray tube.

  (4) As a modification of the first embodiment, as shown in FIG. 5, the current detection 15 including the current detection resistor R3 is provided at the low potential terminal P4 of the target voltage generation unit 17, and the voltage proportional to the tube current A is controlled by the tube current. It is also possible to obtain the same effect as in the first embodiment by connecting to the feedback input of the unit 16.

  (5) As a modification of the first embodiment, as shown in FIG. 6, an X-ray dose detection means 90 such as a scintillation detector is provided at a position where a part of the X-rays emitted from the X-ray tube can be detected without using the current detection resistor R3. And a voltage proportional to the X-ray dose is connected to the feedback input of the tube current control unit 16. Since the X-ray dose generated in the X-ray tube is proportional to the tube current A, by controlling the cathode electrode 3a of the X-ray tube by feedback control by the tube current control unit 16, an X-ray imaging apparatus (not shown) or the like is used. It is possible to control so that the X-ray dose command value and the X-ray dose generated by the X-ray tube are always equal.

D3 Diode G Ground Q Transistor R2 Resistor S1 Cathode voltage generator 3a Cathode electrode 4 Target electrode 15 Current detector 16 Tube current controller (feedback controller)
24 FPD (X-ray detection means)
28 Display section (display means)
31 Image generation unit (image generation means)

Claims (5)

A cathode electrode that emits electrons;
An X-ray tube comprising a target electrode that generates X-rays upon collision of electrons, and a grid electrode connected to the ground for controlling the amount of electrons passing between them;
A target voltage generator for applying a tube voltage to the target electrode and supplying a tube current;
A cathode voltage generator having a high potential terminal and a low potential terminal;
A diode having an anode connected to the high potential terminal and a cathode connected to the cathode electrode of the X-ray tube;
A resistor connected to a position between the anode and the low potential terminal;
A transistor having a base connected to the anode, an emitter connected to the cathode electrode of the X-ray tube, and a collector connected to the low potential terminal;
The X-ray generator according to claim 1, wherein the low potential terminal is connected to the ground directly or through current detection means. The X-ray generator according to claim 1,
The current detection means connected to a position between the low potential terminal and the ground, and a feedback control section are further provided, and a signal from the current detection means is fed back to the cathode voltage generation section through the feedback control section. An X-ray generator characterized by that. The X-ray generator according to claim 1,
The low potential terminal is directly connected to the ground;
Current detection means for detecting the tube current supplied from the target voltage generator;
A feedback control unit;
The X-ray generator according to claim 1, wherein a signal from the current detector is fed back to the cathode voltage generator through the feedback controller. The X-ray generator according to claim 1,
The low potential terminal is directly connected to the ground;
X-ray dose detection means for detecting the amount of X-rays output from the target electrode;
A feedback control unit;
An X-ray generation apparatus characterized in that a signal from the X-ray dose detection means is fed back to the cathode voltage generation unit through the feedback control unit. An X-ray imaging apparatus comprising the X-ray generation apparatus according to any one of claims 1 to 4,
X-ray detection means for detecting X-rays;
Image generating means for generating an X-ray fluoroscopic image based on a signal output from the X-ray detecting means;
An X-ray imaging apparatus comprising: display means for displaying the X-ray fluoroscopic image.

Images