Method for regulating and controlling focus beam spot of X-ray tube, X-ray tube and medical equipment

Abstract

The invention provides an X-ray tube focus beam spot regulation and control method, an X-ray tube and medical equipment, and belongs to the technical field of X-ray tubes. The method comprises the following steps: acquiring the working parameter information of the X-ray tube at the current moment and the working parameter information of the X-ray tube at the previous moment; magnetic control current information of the previous moment is determined according to the working parameter information of the previous moment, and magnetic control current information of the current moment is determined according to the working parameter information of the current moment; determining a magnetic control current difference according to the magnetic control current information at the previous moment and the magnetic control current information at the current moment; and selecting a preset current unit according to the magnetic control current difference, and regulating and controlling the magnetic field of the next magnetic control stage according to the preset current unit so as to regulate and control the size of a focus beam spot generated by the X-ray tube. Through the method, the magnetic control current information of the next magnetic control stage can be dynamically adjusted in real time, so that the real magnetic focusing magnetic field response is matched with the change of the tube voltage or / and the tube current, and the problem of low dimensional stability of the focus beam spot is solved.

Description

Technical Field

[0001] This application belongs to the field of X-ray tube technology, and particularly relates to a method for controlling the focal spot of an X-ray tube, an X-ray tube, and medical equipment. Background Technology

[0002] X-rays are widely used in industrial flaw detection, security inspection, medical diagnosis, and medical treatment. In an X-ray tube, an electron emission device, after being energized and heated, emits a stream of electrons that, under the control of a magnetocontrol system, bombard a target disk at high speed, thus generating X-rays. By adjusting the tube voltage and / or tube current and other operating parameters of the X-ray tube, the intensity, wavelength, and other characteristics of the X-rays can be controlled to meet different application requirements.

[0003] However, in traditional control methods, when the tube voltage and / or tube current change, the rapid change in the magnetron current leads to the introduction of eddy currents, causing the actual magnetic field waveform to lag significantly behind the current change waveform of the magnetron system. Consequently, when the tube voltage and / or tube current change, the magnetic field has not yet responded, causing the focal spot size to continuously change due to the lag in magnetic field response. This results in a constantly fluctuating and unstable focal spot size generated by the X-ray tube. Summary of the Invention

[0004] The purpose of this application is to provide a method for controlling the focal spot of an X-ray tube, an X-ray tube, and a medical device, aiming to solve the technical problem of low focal spot size stability caused by the hysteresis of the magnetic field response when the tube voltage and / or tube current changes in traditional control methods.

[0005] This application provides a method for controlling the focal spot of an X-ray tube, including:

[0006] Obtain the current and previous operating parameter information of the X-ray tube;

[0007] The magnetic control current information at the previous moment is determined based on the operating parameter information at the previous moment, and the magnetic control current information at the current moment is determined based on the operating parameter information at the current moment.

[0008] The magnetic control current difference is determined based on the magnetic control current information at the previous moment and the magnetic control current information at the current moment.

[0009] A preset current unit is selected based on the magnetic control current difference, and the magnetic field of the next magnetic control stage is adjusted based on the preset current unit to control the focal spot size generated by the X-ray tube.

[0010] In one embodiment, before the step of determining the magnetic control current information at the previous moment based on the operating parameter information at the previous moment, and determining the magnetic control current information at the current moment based on the operating parameter information at the current moment, the method further includes:

[0011] The difference in operating parameters is determined based on the operating parameter information at the current moment and the operating parameter information at the previous moment;

[0012] If the difference in operating parameters is greater than a critical value, then the steps of determining the magnetic control current information at the previous moment based on the operating parameter information at the previous moment, and determining the magnetic control current information at the current moment based on the operating parameter information at the current moment are executed.

[0013] In one embodiment, the step of selecting a preset current unit based on the magnetic control current difference and adjusting the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube includes:

[0014] If the magnetic control current difference is less than or equal to the current interval difference of the first preset current unit, and the magnetic control current difference is less than or equal to the current interval difference of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the magnetic control current information of the current magnetic control stage, so as to adjust the focal spot size generated by the X-ray tube.

[0015] In one embodiment, the step of selecting a preset current unit based on the magnetic control current difference and adjusting the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube further includes:

[0016] If the magnetic control current difference is greater than the current range difference of the first preset current unit and less than the current range difference of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the first preset current unit to adjust the focal spot size generated by the X-ray tube.

[0017] In one embodiment, the step of selecting a preset current unit based on the magnetic control current difference and adjusting the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube further includes:

[0018] If the difference in the magnetic control current is greater than the current range difference of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the second preset current unit to control the focal spot size generated by the X-ray tube.

[0019] In one embodiment, after the steps of selecting a preset current unit based on the magnetic control current difference and adjusting the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube, the method further includes:

[0020] The difference in operating parameters is determined based on the operating parameter information at the current moment and the operating parameter information at the previous moment;

[0021] If the difference in the operating parameters is less than or equal to the critical value, the magnetic control current information of the current magnetic control stage is maintained.

[0022] In one embodiment, before the step of obtaining the current operating parameter information and the previous operating parameter information of the X-ray tube, the method further includes:

[0023] The feedback time interval for the selected working parameter information is formed by the current time and the previous time.

[0024] In one embodiment, the step of selecting a preset current unit based on the magnetic control current difference and adjusting the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube includes:

[0025] The type of the preset current unit is selected based on the feedback time interval and the difference between the magnetically controlled current; the type of the preset current unit is determined based on the time period and the difference between the current interval of the preset current unit; the time period of the preset current unit is the same as the feedback time interval.

[0026] The magnetic field of the next magnetocontrol stage is controlled by the preset current unit to regulate the focal spot size generated by the X-ray tube.

[0027] In one embodiment, the step of determining the type of the preset current unit based on the difference between the time period and the current interval of the preset current unit includes:

[0028] During the time period of the preset current unit, the magnetically controlled current of the preset current unit linearly increases from zero to a first current amplitude, and then linearly decreases from the first current amplitude to a first current target value; the current range difference of the preset current unit is determined based on the first current amplitude and the zero value.

[0029] In one embodiment, the step of determining the type of the preset current unit based on the difference between the time period and the current interval of the preset current unit includes:

[0030] During the time period of the preset current unit, the magnetically controlled current of the preset current unit increases linearly from the initial current value to the second current amplitude, and then decreases linearly from the second current amplitude to the second current target value; the current range difference of the preset current unit is determined based on the second current amplitude and the initial current value.

[0031] This application provides an X-ray tube, comprising:

[0032] The electron emission module is used to emit an electron beam based on operating parameter information;

[0033] A magnetically controlled power supply, connected to the electron emission module, is used to acquire the current and previous operating parameter information of the electron emission module; determine the magnetically controlled current information of the previous moment based on the previous operating parameter information; determine the magnetically controlled current information of the current moment based on the current operating parameter information; determine the magnetically controlled current difference based on the previous and current magnetically controlled current information; select a preset current unit based on the magnetically controlled current difference; and regulate the magnetic field of the next magnetic control stage based on the preset current unit to regulate the focal spot size of the electron beam.

[0034] In one embodiment, the X-ray tube further includes:

[0035] A magnetic focusing module, connected to the magnetically controlled power supply, is used to focus and control the magnetic field through which the electron beam passes according to the preset current unit provided by the magnetically controlled power supply, so as to control the focal spot size generated by the X-ray tube.

[0036] In one embodiment, the X-ray tube further includes:

[0037] A magnetic deflection module, connected to the magnetically controlled power supply, is used to deflect and control the magnetic field through which the electron beam passes, based on the magnetic deflection current provided by the magnetically controlled power supply.

[0038] In one embodiment, the electron emission module includes:

[0039] The cathode module is used to emit the electron beam based on the tube voltage signal sent by the tube voltage source;

[0040] A gate, disposed around the cathode module, is used to adjust the tube current according to the gate voltage signal sent by the gate voltage source, thereby controlling the electron beam.

[0041] In one embodiment, the X-ray tube further includes:

[0042] The shell surrounds and forms a vacuum chamber;

[0043] The target disk is disposed within the vacuum chamber;

[0044] The cathode module and the gate are disposed within the vacuum chamber;

[0045] Inside the vacuum chamber, the electron beam emitted by the cathode module is bombarded onto the target disk after being controlled by the grid and magnetic field.

[0046] In one embodiment, the target disk is provided with an inclined surface for determining the focal spot size of the controlled electron beam after it has struck the target disk by line projection.

[0047] This application provides a medical device including an X-ray tube as described in any of the above embodiments.

[0048] The beneficial effects of the embodiments of the present invention compared with the prior art are as follows:

[0049] In this application, the preset current unit is set based on the eddy current effect, which can solve the problem of magnetic field response lag. During use, the core material of the magnetic focusing module is carefully selected to ensure that the magnetic field required for X-ray tube focus control is in the unsaturated region. In the unsaturated region of the magnetic field, different magnetic induction intensities correspond to different relative permeabilities; the stronger the magnetic field, the greater the relative permeability, and therefore the greater the eddy current. Using the preset current unit provided in this application, when the magnetic control current information required by the magnetic focusing module needs adjustment, the corresponding preset current unit can be selected based on the difference between the magnetic control current information obtained from the previous moment and the current moment, and adjustment can be performed using the preset current unit. The waveform of the preset current unit is sawtooth-shaped; the magnetic control current will first overcharge and then return to the preset target value, which can effectively counteract the influence of eddy currents and make the magnetic field response faster.

[0050] When the operating parameters of the X-ray tube change, the magnetron power supply determines the magnetron current difference based on the feedback of the operating parameters from the previous and current moments. A preset current unit is selected based on this difference, and the magnetron current is adjusted synchronously with the waveform of the magnetron current information. This allows the magnetic focusing magnetic field to change approximately linearly, resulting in a more stable focal spot size after magnetron focusing magnetic field control. Therefore, the X-ray tube focal spot control method provided in this application, using real-time feedback of the tube voltage and / or tube current at the current moment and a preset current unit incorporating eddy current hysteresis as the adjustment step size, can dynamically and in real-time adjust the magnetron current information of the magnetron focusing module in the next magnetron control stage. This ensures that the actual magnetron focusing magnetic field response matches the changes in tube voltage and / or tube current. Matching the actual magnetron focusing magnetic field response with the changes in tube voltage and / or tube current guarantees a constant density distribution of the focal spot in the X-ray tube, improving the stability of the focal spot size. This ensures the stability of the focal spot size in scenarios with rapid tube voltage switching, rapid tube current switching, and real-time dose control. Attached Figure Description

[0051] Figure 1 A schematic flowchart illustrating the steps of the X-ray tube focal spot control method provided in this application;

[0052] Figure 2 A schematic diagram illustrating the control of tube voltage and / or tube current, preset current unit, and magnetic induction intensity in the X-ray tube focal spot control method provided in this application.

[0053] Figure 3 A waveform diagram of the preset current unit and magnetic induction intensity provided in this application;

[0054] Figure 4 A schematic diagram illustrating the changes in magnetic field strength and permeability provided in this application;

[0055] Figure 5 A schematic diagram of the tube voltage and tube current waveforms for the real-time dose control scenario provided in this application;

[0056] Figure 6 A waveform diagram illustrating the rapid switching scenario of the tube voltage provided in this application;

[0057] Figure 7 A waveform diagram illustrating the rapid switching scenario of tube current provided in this application;

[0058] Figure 8 This is a schematic diagram illustrating the change in focal spot size controlled by traditional methods.

[0059] Figure 9 A schematic diagram illustrating the stability of the focal spot size in the X-ray tube focal spot control method provided in this application;

[0060] Figure 10 A schematic diagram of the waveform changes of the preset current unit and the magnetic induction intensity in one embodiment provided in this application;

[0061] Figure 11 A schematic diagram of the waveform changes of the preset current unit and the magnetic induction intensity in one embodiment provided in this application;

[0062] Figure 12 A schematic diagram of the waveform changes of the preset current unit and the magnetic induction intensity in one embodiment provided in this application;

[0063] Figure 13 A schematic diagram of the waveform changes of the preset current unit and the magnetic induction intensity in one embodiment provided in this application;

[0064] Figure 14 This is a schematic diagram of the structure of the X-ray tube provided in this application;

[0065] Figure 15 A schematic diagram of the structure of the medical device provided in this application;

[0066] Figure 16 A cross-sectional schematic diagram of the medical device provided in this application. Detailed Implementation

[0067] To make the technical problems, technical solutions, and beneficial effects to be solved by this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and are not intended to limit the scope of this application.

[0068] It should be noted that when a component is referred to as being "fixed to" or "set on" another component, it can be directly on or indirectly on that other component. When a component is referred to as being "connected to" another component, it can be directly connected to or indirectly connected to that other component.

[0069] It should be understood that the terms "length", "width", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this application.

[0070] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this application, "multiple" means two or more, unless otherwise explicitly specified.

[0071] Please see Figure 1 This application provides a method for controlling the focal spot of an X-ray tube, comprising:

[0072] Step S10: Obtain the current operating parameter information and the previous operating parameter information of the X-ray tube;

[0073] Step S20: Determine the magnetic control current information of the previous moment based on the operating parameter information of the previous moment, and determine the magnetic control current information of the current moment based on the operating parameter information of the current moment.

[0074] Step S30: Determine the magnetic control current difference based on the magnetic control current information of the previous moment and the magnetic control current information of the current moment;

[0075] Step S40: Select a preset current unit based on the magnetic control current difference, and adjust the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube.

[0076] In this embodiment, the current operating parameter information of the X-ray tube includes the current tube voltage and / or tube current. Please refer to [link to relevant documentation]. Figure 2 As shown, the current and previous times of the X-ray tube are referenced to the operating time of the X-ray tube, such as... Figure 2 The waveforms t1, t2, t3, t4, t5, and t6 in the waveform diagram 710 show the operating parameter information. The magnetic power supply 110 receives the tube voltage and / or tube current from the previous and current moments fed back by components such as the tube voltage source 212 or the gate voltage source 214. The tube voltage can be directly obtained from the tube voltage source 212. The tube current can be the measured value of the X-ray tube, or it can be obtained by converting the tube current based on the gate voltage provided by the gate voltage source 214, or by inferring the tube current based on the change pattern of the tube current during the change of the tube voltage. Furthermore, based on the operating parameter information fed back from the previous moment, the magnetic power supply 110 can obtain the magnetic control current information corresponding to the previous moment in the magnetic focusing function table in the pre-stored board. The magnetic focusing function table includes various parameters, settings, or instructions corresponding to different combinations of tube voltage and tube current. Based on the operating parameter information fed back from the current moment, the magnetic control current information corresponding to the current moment in the magnetic focusing function table in the pre-stored board can be obtained.

[0077] The magnetic control power supply 110 compares the magnetic control current information obtained at the current moment with the magnetic control current information retrieved from the previous moment to determine the difference in magnetic control current between the two moments. Based on this difference, it compares it with one or more preset current units to select and determine the magnetic control current information for the next magnetic control stage of the magnetic focusing module 120 in the X-ray tube. The next magnetic control stage represents the next stage of magnetic field change controlled by the magnetic focusing module 120, such as... Figure 2 The waveforms of the magnetically controlled current information in Figure 720 are shown as T1, T2, T3, T4, and T5.

[0078] The preset current unit can be understood as the current waveform required for the magnetic focusing module 120 to be controlled, or as the basic unit for the change of magnetically controlled current, such as... Figure 3The diagram shows a first preset current unit 740 and a second preset current unit 760. The first preset current unit 740 corresponds to a first magnetic flux density waveform 750 controlled by the magnetic focusing module 120. The second preset current unit 760 corresponds to a second magnetic flux density waveform 770 controlled by the magnetic focusing module 120. Based on the magnetic control current difference, selection is made from the first preset current unit 740 and the second preset current unit 760 to determine the magnetic control current information of the magnetic focusing module 120 in the next magnetic control stage, thereby controlling the focal spot size generated by the X-ray tube.

[0079] In this application, the preset current unit has overcharge characteristics and is set according to the eddy current effect. It can generate reverse eddy currents to cancel the eddy currents generated earlier, resulting in a faster magnetic field response. Therefore, when the tube voltage and / or tube current changes, the magnetic field can respond quickly and promptly, solving the problem of continuously changing focal spot size caused by magnetic field response lag, thus ensuring that the focal spot size remains stable. When using the magnetic focusing module 120, the core material is carefully selected to ensure that the magnetic field required for X-ray tube focus control is in the unsaturated region, i.e. Figure 4 Medium magnetic field strength H and relative permeability μ r The waveform diagram in Figure 780 shows the region where the magnetic field is less than H1. In this region, different magnetic field strengths correspond to different relative permeability μr; the stronger the magnetic field, the higher the relative permeability μr. r The larger the magnetic flux density, the larger the eddy current will be. For magnetically controlled currents at maximum magnetic flux density (… Figure 4 Medium magnetic field strength H and relative permeability μ r When the change waveform (the peak value in waveform 780) is adjusted, the relative permeability μr is at its maximum, the eddy current is at its strongest, and thus the magnetic field lines change directly from B1 to the maximum magnetic induction intensity (as shown in the second magnetic induction intensity waveform 770). Figure 3 As shown. For magnetically controlled currents with small amplitudes, the relative permeability μ r Smaller magnetic field strength results in smaller eddy currents, making the first magnetic flux density waveform 750 closer to the first preset current unit 740, such as... Figure 3 As shown.

[0080] With the preset current unit provided in this application, when the magnetic control current information required by the magnetic focusing module 120 needs to be adjusted, the corresponding preset current unit can be selected based on the difference between the magnetic control current information obtained from the feedback at the previous moment and the magnetic control current information at the current moment, and the adjustment can be performed using the preset current unit. The waveform of the preset current unit is sawtooth-shaped, and the magnetic control current will first be overcharged and then restored to the preset target value, which can effectively counteract the influence of eddy currents and make the magnetic field response faster.

[0081] When the operating parameters of the X-ray tube change as shown in waveform 710, the magnetic control power supply 110 adjusts the magnetic control current synchronously with waveform 720 based on the feedback obtained operating parameter information, thereby obtaining waveform 730 of the magnetic focusing magnetic induction intensity generated by the magnetic focusing module 120. This shows that the magnetic focusing magnetic field changes approximately linearly after being controlled by the preset current unit, resulting in a more stable focal spot size after magnetic focusing magnetic field control. Therefore, the X-ray tube focal spot control method provided in this application, based on real-time feedback of the X-ray tube voltage and / or tube current and using a preset current unit incorporating eddy current hysteresis as the adjustment step size, can dynamically and in real-time adjust the magnetic control current information of the magnetic focusing module 120 in the next magnetic control stage, ensuring that the actual magnetic focusing magnetic field response matches the changes in tube voltage and / or tube current. The real magnetic focusing magnetic field response matches the changes in tube voltage and / or tube current, which can ensure that the density distribution of the focal spot in the X-ray tube remains unchanged, improve the stability of the focal spot size, and ensure the stability of the focal spot size in scenarios with rapid tube voltage switching, rapid tube current switching, and real-time dose control.

[0082] Please see Figure 5 The clinical scenario requirement for X-ray tubes is the first change diagram of tube voltage V1 and gate voltage V2 in a digital orthophoto map (DOM) scenario, shown in Figure 810, and tube current I. tube The corresponding second variation is illustrated in diagram 820. In the DOM scenario, the tube voltage V1 remains constant, and the patient is scanned at different angles by rotating the gantry. The slice thickness varies at different angles, requiring different doses. Therefore, the lead-out tube current I is changed by adjusting the gate voltage V2. tube The period of change in gate voltage V2 is the same as the rack rotation speed. The tube current I... tube As things are constantly changing, the magnetic focusing module 120 must also change accordingly to ensure that the focal spot size remains stable.

[0083] Please see Figure 6 The clinical application of X-ray tubes requires rapid tube voltage switching. In this scenario, the tube voltage V1 changes between two values, corresponding to the third change diagram 830, and the tube current I... tube The basic structure remains unchanged, corresponding to the fourth change diagram 840. As the tube voltage V1 changes from time t1 to t2, the magnetic focusing module 120 also needs to synchronously adjust to maintain the stability of the focal spot size. In the scenario of rapid tube voltage switching, the output tube current I is not adjusted through the gate voltage V2. tube However, during the switching of the tube voltage V1, the tube current I... tubeDue to factors such as control or space charge force, there will be approximately a 10% variation between the two tube voltages. Therefore, the adjustment of the magnetic focusing module 120 needs to be based not only on the tube voltage V1, but also on the tube current I monitored by the X-ray tube. tube Or the pre-stored tube current I corresponding to the change in tube voltage V1. tube Obtain the corresponding tube current I from the relationship of change tube Then adjust the magnetic focusing module 120.

[0084] Please see Figure 7 Clinical applications of X-ray tubes require rapid tube current switching. When the tube voltage V1 changes, the gate voltage V2 also adjusts synchronously to change the tube current I. tube The magnitude of the voltage is adjusted to ensure that the X-ray tube output power is the same under tube voltage V1 and gate voltage V2, as shown in the fifth variation diagram 850. From time t1 to time t2, tube voltage V1 decreases, and gate voltage V2 increases to draw more tube current I. tube To maintain stable power output, as shown in the sixth variation diagram 860. From time t2 to time t3, the tube voltage V1 has completed switching, the gate voltage V2 remains unchanged, and the tube current I... tube Continue laying the line at the preset value.

[0085] Please see Figure 8 ,exist Figure 5 , Figure 6 as well as Figure 7 In the various application scenarios shown, the tube voltage V1 or tube current I tube When the seventh variation diagram 870 changes, if the first magnetic focusing field strength waveform diagram 871 remains unchanged, the final obtained focal spot size will continuously change during the time period from time t1 to time t4, as shown in the diagram. Figure 8 The dimensional variations shown in Figure 872 are unacceptable in a real X-ray tube.

[0086] Please see Figure 9 The target condition of the focal spot size or the condition required by the X-ray tube, such as Figure 9 The medium-sized stability diagram is shown in Figure 882. The tube voltage V1 or tube current I... tube As the eighth change diagram 880 changes, the second magnetic focusing field strength waveform diagram 881 also changes synchronously, ensuring that the focal spot size remains stable throughout the entire dynamic process, presenting as shown in the diagram. Figure 9 The medium-sized stability diagram is shown in Figure 882.

[0087] In one embodiment, before step S20, which involves determining the magnetic control current information based on the operating parameter information of the previous moment and determining the magnetic control current information based on the operating parameter information of the current moment, the method further includes:

[0088] Step S110: Determine the difference in working parameters based on the working parameter information at the current moment and the working parameter information at the previous moment;

[0089] Step S120: If the difference in operating parameters is greater than the critical value, then proceed to step S20: determine the magnetic control current information of the previous moment based on the operating parameter information of the previous moment, and determine the magnetic control current information of the current moment based on the operating parameter information of the current moment.

[0090] In this embodiment, the operating parameters of the X-ray tube include tube voltage and / or tube current. The operating parameter difference is the difference between the tube voltage at the current moment and the tube voltage at the previous moment, and / or the difference between the tube current at the current moment and the tube current at the previous moment. In one embodiment, please refer to... Figure 2 As shown, the transistor voltage fed back by the magnetically controlled power supply 110 at time t1 (which can also be understood as the current time) is 100.5kV, and the transistor current is 20.5mA. The transistor voltage fed back by the magnetically controlled power supply 110 at time t0 (which can also be understood as the previous time) is 100kV, and the transistor current is 20mA. The operating parameter difference is the difference between the transistor voltage and the transistor current. The transistor voltage difference is 0.5kV, and the transistor current difference is 0.5mA. The transistor voltage threshold is set to 1kV. The transistor current threshold is set to 1mA.

[0091] If the operating parameter difference is less than or equal to the critical value, it indicates that the current numerical change is relatively small, and the system is in a relatively stable or acceptable range of change; the magnetic power supply 110 does not respond. After a feedback interval of 751, at time t2, the magnetic power supply 110 receives the tube voltage and / or tube current values ​​again and calculates the operating parameter difference. If the operating parameter difference is greater than the critical value, the magnetic control current information corresponding to the tube voltage and / or tube current is obtained from the magnetic focusing function table. Further, the magnetic control current difference is determined based on the magnetic control current information at the previous time and the magnetic control current information at the current time, and subsequent steps S20, S30, and S40 are executed sequentially. For a detailed description of steps S20, S30, and S40, please refer to the relevant descriptions in the full text.

[0092] Please see Figure 10 and Figure 11 In one embodiment, step S40, selecting a preset current unit based on the magnetocontrol current difference and adjusting the magnetic field of the next magnetocontrol stage based on the preset current unit to control the focal spot size generated by the X-ray tube, includes:

[0093] Step S411: If the magnetic control current difference is less than or equal to the current interval difference of the first preset current unit, and the magnetic control current difference is less than or equal to the current interval difference of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the magnetic control current information of the current magnetic control stage, so as to adjust the focal spot size generated by the X-ray tube.

[0094] In this embodiment, the size of the focal spot generated by the X-ray tube is controlled by changing the magnetic field. The magnetic induction intensity cannot be directly set and needs to be indirectly adjusted based on the current input to the magnetic focusing module 120. In step S30, the magnetic control current difference is determined based on the magnetic control current information at the previous moment and the magnetic control current information at the current moment. The magnetic control current difference indicates the change in the magnetic control current. The first preset current unit and the second preset current unit are two different selectable magnetic control current units. The magnetic control current difference can also be understood as the amplitude difference between the magnetic control current information at the previous moment and the magnetic control current information at the current moment, for example, |I2-I1|.

[0095] In one embodiment, the second preset current unit can be Figure 10 The first preset current waveform 911 corresponds to the formation of the first magnetic induction intensity waveform 921. The first preset current unit can be... Figure 10 The second preset current waveform 912 corresponds to the second magnetic induction intensity waveform 922. The current interval difference ΔI2 of the second preset current unit is greater than the current interval difference ΔI1 of the first preset current unit. The current interval difference can be understood as the difference in current within the time period of the preset current unit, or it can be understood as... Figure 10 The difference between the maximum and minimum values ​​of the medium current waveform. Figure 10 The current range difference of the first preset current waveform 911 is greater than the current range difference of the second preset current waveform 912.

[0096] In one embodiment, the second preset current unit can be Figure 11 The third preset current waveform 931 corresponds to the third magnetic induction intensity waveform 941. The first preset current unit can be... Figure 11 The fourth preset current waveform 932 corresponds to the fourth magnetic induction intensity waveform 942. Figure 11 The current range difference of the third preset current waveform 931 is greater than the current range difference of the fourth preset current waveform 932.

[0097] By comparing the magnetic control current difference with the first preset current unit and the second preset current unit, a suitable preset current unit can be selected to regulate the magnetic field, thereby controlling the focal spot size and ensuring its stability. If the magnetic control current difference |I2-I1| is less than or equal to the current interval difference ΔI1 of the first preset current unit, and the magnetic control current difference is less than or equal to the current interval difference ΔI2 of the second preset current unit, then the magnetic control power supply 110 does not respond and maintains the current magnetic control current information. This can also be understood as regulating the magnetic field of the next magnetic control stage based on the magnetic control current information of the current magnetic control stage, thereby regulating the focal spot size generated by the X-ray tube and ensuring its stability.

[0098] In one embodiment, step S40, which involves selecting a preset current unit based on the magnetocontrol current difference and adjusting the magnetic field of the next magnetocontrol stage based on the preset current unit to control the focal spot size generated by the X-ray tube, further includes:

[0099] Step S412: If the magnetic control current difference is greater than the current range difference of the first preset current unit and less than the current range difference of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the first preset current unit to adjust the focal spot size generated by the X-ray tube.

[0100] In this embodiment, the current range difference ΔI1 of the first preset current unit is less than the current range difference ΔI2 of the second preset current unit. If the magnetic control current difference |I2-I1| is greater than the current range difference ΔI1 of the first preset current unit, and |I2-I1| is less than the current range difference ΔI2 of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the first preset current unit. This can also be understood as the magnetic control current being adjusted according to the first preset current unit. When the magnetic control current changes, the magnetic field of the next magnetic control stage will also change accordingly, thereby adjusting the focal spot size generated by the X-ray tube and maintaining the stability of the focal spot size.

[0101] Both the first and second preset current units are set based on the eddy current effect, fully considering the problem of magnetic field response lag caused by the eddy current effect. The waveforms of the first and second preset current units are sawtooth-shaped, and the magnetic control current will first overcharge and then return to the preset target value, which can effectively counteract the influence of eddy current and make the magnetic field response faster.

[0102] The magnetic control current difference indicates the switching amplitude between the magnetic control current information at the previous moment and the magnetic control current information at the current moment. Based on the magnetic control current difference, a matching preset current unit is selected, such that a smaller preset current unit matches a smaller magnetic control current amplitude switching, and a larger preset current unit matches a larger magnetic control current amplitude switching. The current range difference ΔI2 of the second preset current unit is greater than the current range difference ΔI1 of the first preset current unit. The first preset current unit is matched for scenarios with fine magnetic control current changes. The second preset current unit is matched for scenarios with larger magnetic control current changes. Depending on the different switching scenarios, a more suitable current unit can be selected from the first and second preset current units, enabling the magnetic focusing module 120 to respond synchronously and promptly, changing the output magnetic induction intensity. This allows for more accurate handling of fluctuations in the focal spot size caused by switching of tube voltage and / or tube current, timely adjustment of the focal spot size, and maintenance of focal spot size stability.

[0103] In one embodiment, step S40, which involves selecting a preset current unit based on the magnetocontrol current difference and adjusting the magnetic field of the next magnetocontrol stage based on the preset current unit to control the focal spot size generated by the X-ray tube, further includes:

[0104] Step S413: If the difference in magnetic control current is greater than the current range difference of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the second preset current unit to adjust the focal spot size generated by the X-ray tube.

[0105] In this embodiment, if the magnetic control current difference |I2-I1| is greater than the current interval difference ΔI2 of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the second preset current unit. This can also be understood as the magnetic control current being adjusted according to the second preset current unit. When the magnetic control current changes, the magnetic field of the next magnetic control stage will also change accordingly, thereby adjusting the focal spot size generated by the X-ray tube and maintaining the stability of the focal spot size.

[0106] In one embodiment, multiple preset current units can be configured. By setting multiple preset current units corresponding to different current range differences based on the current range difference, it is possible to match multiple different magnetocontrol current differences, and to regulate the magnetic field with a more suitable preset current unit, thereby controlling the focal spot size generated by the X-ray tube and maintaining the stability of the focal spot size.

[0107] In one embodiment, the time period of the second preset current unit is the same as that of the first preset current unit, and the amplitude difference of the second preset current unit is greater than the amplitude difference of the first preset current unit, such as... Figure 10 and Figure 11As shown. Depending on the switching scenario, a more suitable current unit can be selected from the first preset current unit and the second preset current unit, so that the magnetic focusing module 120 can respond synchronously in a timely manner, change the output magnetic induction intensity, and more accurately cope with the fluctuation of the focal spot size caused by the switching of tube voltage and / or tube current, and adjust the focal spot size in a timely manner to maintain the stability of the focal spot size.

[0108] In one embodiment, after step S40, which involves selecting a preset current unit based on the magnetocontrol current difference and adjusting the magnetic field of the next magnetocontrol stage based on the preset current unit to control the focal spot size generated by the X-ray tube, the method further includes:

[0109] Step S50: Determine the difference in working parameters based on the working parameter information at the current moment and the working parameter information at the previous moment;

[0110] In step S60, if the difference in operating parameters is less than or equal to the critical value, the magnetic control current information of the current magnetic control stage is maintained.

[0111] In this embodiment, after steps S10 to S40 are executed, the magnetic focusing module 120 can respond synchronously and promptly, changing the output magnetic induction intensity and adjusting the focal spot size in a timely manner, thus maintaining the stability of the focal spot size. Figure 2 As shown, the feedback interval 751 from time t1 to time t2 is the time interval between the current time and the previous time. The time interval from time t2 to time t3 is the feedback time interval. The time interval from time t3 to time t4 is the feedback time interval. After the X-ray tube focal spot control method provided in the above embodiments is applied, the tube voltage and / or tube current reach stability at time t5. However, compared to time t4, the tube voltage and / or tube current still change. The magnetic field of the next magnetic control stage is then controlled according to the preset current unit. Until time t6, the tube voltage and / or tube current reach stability, and compared to time t5, the tube voltage and / or tube current no longer change. The magnetic control current information of the current magnetic control stage is maintained, and the magnetic control current I... focusing Stability is reached. Throughout the regulation process, the magnetic control response lags behind the feedback time of the tube voltage and / or tube current by two feedback intervals 751. However, the feedback intervals 751 are very small and do not affect the focus characteristics over the entire regulation process.

[0112] When the transistor voltage and / or current no longer change under different application scenarios and a steady state is reached, such as Figure 2In the waveform diagram 710 showing the operating parameter information, when the tube voltage and / or tube current no longer change at time t6, the difference in operating parameters is less than or equal to the critical value. This indicates that the current numerical change is relatively small, and the tube is in a relatively stable or acceptable range of change. The magnetic control power supply 110 does not respond, maintaining the current magnetic control current information to regulate the focal spot size generated by the X-ray tube, ensuring that the focal spot size remains stable, and ultimately completing the process. Figure 2 The magnetic field adjustment is shown throughout the entire magnetocontrol phase.

[0113] In one embodiment, before step S10, which involves obtaining the current and previous operating parameter information of the X-ray tube, the method further includes:

[0114] Step S01: Select the feedback time interval for working parameter information; the current time and the previous time form a feedback time interval.

[0115] In this embodiment, the feedback time interval for operating parameter information is selected according to different clinical scenario requirements. Selecting the feedback time interval for operating parameter information can be understood as selecting the feedback time interval for tube voltage and / or tube current. Different clinical scenario requirements include... Figure 5 The DOM scene shown Figure 6 The fast tube voltage switching scenario shown and Figure 7 The diagram illustrates a rapid tube current switching scenario. For example, the feedback time interval in a rapid tube voltage switching scenario is longer than that in a rapid tube current switching scenario. Similarly, the feedback time interval in a DOM (Domain-Oriented Domain) scenario is longer than that in a rapid tube current switching scenario. Different clinical scenarios require different feedback time intervals, which can be selected based on the actual application. By selecting different feedback time intervals and choosing preset current units of corresponding lengths, the magnetic field in the next magnetocontrol stage can be controlled more accurately under different clinical scenario requirements, ensuring that the focal spot size remains stable.

[0116] Please see Figure 12 and Figure 13 In one embodiment, step S40, selecting a preset current unit based on the magnetocontrol current difference and adjusting the magnetic field of the next magnetocontrol stage based on the preset current unit to control the focal spot size generated by the X-ray tube, includes:

[0117] Step S421: Select the type of preset current unit based on the feedback time interval and the difference in magnetic control current; the type of preset current unit is determined based on the time period of the preset current unit and the difference in current interval; the time period of the preset current unit is the same as the feedback time interval.

[0118] Step S422: Adjust the magnetic field of the next magnetocontrol stage according to the preset current unit to control the focal spot size generated by the X-ray tube.

[0119] In this embodiment, different combinations of the time period and current interval difference of the preset current unit form different types of preset current units. For example... Figure 12 The fifth preset current waveform 951 and the sixth preset current waveform 952 are shown in the diagram. The time period of the fifth preset current waveform 951 is longer than that of the sixth preset current waveform 952. The difference in the current range of the fifth preset current waveform 951 is greater than the difference in the current range of the sixth preset current waveform 952. Figure 13 The seventh preset current waveform 971 and the eighth preset current waveform 972 are shown. The time period of the seventh preset current waveform 971 is longer than that of the eighth preset current waveform 972. The current interval difference of the seventh preset current waveform 971 is greater than that of the eighth preset current waveform 972. The fifth preset current waveform 951, the sixth preset current waveform 952, the seventh preset current waveform 971, and the eighth preset current waveform 972 are small magnetically controlled current units with different time periods (or different unit times) and different current interval differences (or different amplitudes), which can cope with more different clinical scenarios. The current interval difference (or amplitude) of the preset current unit and the feedback time interval are determined by comprehensively considering the amplitude differences of current switching in various scenarios in the X-ray tube. Compared to Figure 10 and Figure 11 The current range differences (or amplitudes) of the first preset current waveform 911, the second preset current waveform 912, the third preset current waveform 931, the fourth preset current waveform 932, the fifth preset current waveform 951, the sixth preset current waveform 952, the seventh preset current waveform 971, and the eighth preset current waveform 972 are smaller, and their time periods (or unit times) are also shorter. The time period of the preset current unit is the same as the feedback time interval, which makes the feedback time interval more matched with the control of the small change unit of the magnetic control current, and can more accurately control the magnetic field to ensure that the focal spot size remains stable.

[0120] In one embodiment, the fifth preset current waveform 951 corresponds to the fifth magnetic flux density waveform 961. The sixth preset current waveform 952 corresponds to the sixth magnetic flux density waveform 962. The seventh preset current waveform 971 corresponds to the seventh magnetic flux density waveform 981. The eighth preset current waveform 972 corresponds to the eighth magnetic flux density waveform 982. Smaller preset current units are equivalent to further subdividing larger preset current units into multiple parts, allowing for finer control of the magnetic field, which can meet the needs of more precise clinical scenarios.

[0121] Please see Figure 10 and Figure 12As shown, in one embodiment, step S421, the step of determining the type of the preset current unit based on the time period and current interval difference of the preset current unit, includes:

[0122] Step S4211, within the time period of the preset current unit, the magnetic control current I of the preset current unit... focusing The current amplitude increases linearly from zero to the first current amplitude, and then decreases linearly from the first current amplitude to the first target current value; the current range difference is determined based on the first current amplitude and the zero value.

[0123] In this embodiment, the magnetically controlled current I focusing The current increases linearly from zero to the first current amplitude, and then decreases linearly from the first current amplitude to the first target current value, forming a current as follows: Figure 10 The first preset current waveform 911 and the second preset current waveform 912 shown are as follows: Figure 12 The fifth preset current waveform 951 and the sixth preset current waveform 952 are shown. The first current amplitude and the first current target value in the preset current unit can be set according to the actual application scenario. In one embodiment, by simulating the magnetic induction intensity waveforms corresponding to different preset current units, multiple different types of preset current units can be obtained, thereby adapting to the magnetic field response required by different application scenarios to ensure that the focal spot size remains stable. By using small preset current units (which can also be understood as small magnetically controlled current change units), more precise adjustment accuracy can be achieved to control more different clinical scenarios, thereby ensuring that the speed of magnetic field response matches the switching of tube voltage and / or tube current.

[0124] The magnetic control current I of the preset current unit focusing The current amplitude linearly increases from zero to a first current value and then linearly decreases from the first current value to a first target current value, forming a sawtooth-shaped magnetically controlled current waveform with overcharge characteristics. During the phase where the first current amplitude linearly decreases to the first target current value, a reverse eddy current is generated to counteract the eddy current generated during the phase where the current amplitude linearly increases from zero to the first current value. This results in a faster magnetic field response, allowing the magnetic field to respond quickly and promptly to changes in tube voltage and / or tube current. This avoids the problem of continuously changing focal spot size due to magnetic field response lag, thus ensuring that the focal spot size remains stable.

[0125] Please see Figure 11 and Figure 13 In one embodiment, step S421, the step of determining the type of the preset current unit based on the time period and current interval difference of the preset current unit, includes:

[0126] Step S4212, within the time period of the preset current unit, the magnetic control current I of the preset current unit... focusingThe current is linearly increased from the initial value to the second current amplitude, and then linearly decreased from the second current amplitude to the second target current value; the second current amplitude is greater than the first current amplitude; the current interval difference is determined based on the second current amplitude and the initial current value.

[0127] In this embodiment, the magnetically controlled current I focusing The current increases linearly from its initial value to a second current amplitude, and then decreases linearly from its second current amplitude to a second target current value, forming a current pattern as follows: Figure 11 The third preset current waveform 931 and the fourth preset current waveform 932 shown are as follows: Figure 13 The seventh preset current waveform 971 and the eighth preset current waveform 972 are shown. The initial current value, second current amplitude, and second current target value in the preset current unit can be set according to the actual application scenario. In one embodiment, by simulating the initial current value, second current amplitude, and second current target value of different preset current units, different magnetic induction intensity waveforms can be obtained, thereby obtaining multiple different types of preset current units that can adapt to the magnetic field response required by different application scenarios, ensuring that the focal spot size remains stable. The initial current value of the preset current unit is greater than zero, compared to... Figure 10 The first preset current waveform 911 and the second preset current waveform 912 shown are as follows: Figure 12 The fifth preset current waveform 951 and the sixth preset current waveform 952 shown are... Figure 11 The third preset current waveform 931 and the fourth preset current waveform 932 shown are as follows: Figure 13 The difference in current range between the seventh preset current waveform 971 and the eighth preset current waveform 972 shown is smaller, which allows for more precise control.

[0128] The magnetic control current I of the preset current unit focusing The current increases linearly from an initial value to a second current amplitude, and then decreases linearly from the second current amplitude to a second target current value, forming a sawtooth-shaped magnetically controlled current waveform with overcharge characteristics. During the phase where the second current amplitude decreases linearly to the second target current value, a reverse eddy current is generated to counteract the eddy current generated during the phase where the current increases linearly from the initial value to the second current amplitude. This further accelerates the magnetic field response, allowing for a timely and rapid response when the tube voltage and / or tube current changes. This avoids the problem of continuously changing focal spot size due to magnetic field response lag, thus ensuring the stability of the focal spot size.

[0129] Please see Figure 14This application provides an X-ray tube 100. The X-ray tube 100 includes an electron emission module 210 and a magnetron power supply 110. The electron emission module 210 is used to emit an electron beam according to operating parameter information. The magnetron power supply 110 is connected to the electron emission module 210. The magnetron power supply 110 is used to acquire the current operating parameter information and the previous operating parameter information of the electron emission module 210; determine the magnetron current information of the previous operating parameter information based on the previous operating parameter information, and determine the magnetron current information of the current operating parameter information based on the current operating parameter information; determine the magnetron current difference based on the magnetron current information of the previous operating parameter information and the magnetron current information of the current operating parameter information; select a preset current unit based on the magnetron current difference, and regulate the magnetic field of the next magnetron stage according to the preset current unit to regulate the focal spot size of the electron beam.

[0130] In this embodiment, the magnetically controlled power supply 110 is connected to the electron emission module 210 and is used to acquire the current and previous operating parameter information of the electron emission module 210. The magnetically controlled power supply 110 receives the tube voltage and / or tube current from the previous and current times fed back by components such as the tube voltage source 212 or the gate voltage source 214 in the electron emission module 210. The tube voltage can be directly obtained from the tube voltage source 212. The tube current can be the measured value of the X-ray tube. Alternatively, the tube current can be calculated based on the gate voltage provided by the gate voltage source 214 in the electron emission module 210. Or, it can be obtained by inference based on the change law of the tube current during the change of the tube voltage.

[0131] The magnetically controlled power supply 110 is used to determine the magnetically controlled current information at the previous moment based on the operating parameter information at the previous moment, and to determine the magnetically controlled current information at the current moment based on the operating parameter information at the current moment; to determine the magnetically controlled current difference based on the magnetically controlled current information at the previous moment and the magnetically controlled current information at the current moment; to select a preset current unit based on the magnetically controlled current difference, and to regulate the magnetic field of the next magnetic control stage based on the preset current unit, so as to regulate the focal spot size of the electron beam, the relevant steps can be referred to the relevant descriptions of steps S10 to S40 in the above embodiments.

[0132] In one embodiment, the X-ray tube 100 further includes a magnetic focusing module 120. The magnetic focusing module 120 is connected to the magnetically controlled power supply 110. The magnetic focusing module 120 is used to focus and control the magnetic field through which the electron beam passes according to a preset current unit provided by the magnetically controlled power supply 110, so as to control the focal spot size generated by the X-ray tube.

[0133] In this embodiment, the electron beam, after being extracted from the electron emission module 210, is modulated by the magnetic focusing module 120. The magnetic focusing module 120 is a magnetic focusing system, which can be a beam optical element such as a quadrupole magnet or a solenoid magnet. For the focusing system, the magnetic induction intensity of the region corresponding to the size of the electron beam (which can also be understood as the size of the beam envelope) is linearly related to the position. Therefore, when the focal spot size is adjusted by the magnetic focusing module 120, the impact on the electron density distribution is relatively small. When the tube voltage or tube current changes, the magnetic focusing module 120 will respond synchronously, changing the output magnetic induction intensity to ensure that the focal spot size on the target disk 410 remains unchanged. For a description of the preset current unit, please refer to the descriptions in the above embodiments.

[0134] In one embodiment, the X-ray tube 100 further includes a magnetic deflection module 130. The magnetic deflection module 130 is connected to the magnetically controlled power supply 110 and is used to deflect and control the magnetic field through which the electron beam passes based on the magnetic deflection current information provided by the magnetically controlled power supply 110.

[0135] In this embodiment, the magnetic deflection module 130 is a deflecting magnet used to adjust the position of the electron beam striking the target disk 410. The magnetic deflection module 130 includes a magnetic core structure and a coil. The coil is arranged around the surface of the magnetic core structure. The coil is connected to the magnetically controlled power supply 110. The magnetic core structure is a sheet-like or stacked structure. The coil is used to generate a deflecting magnetic field by passing magnetic deflection current information sent by the magnetically controlled power supply 110, thereby adjusting the position of the electron beam striking the target disk 410.

[0136] In one embodiment, the electron emission module 210 includes a cathode module 211 and a gate 213. The cathode module 211 is used to emit an electron beam according to the tube voltage signal sent by the tube voltage source 212. The gate 213 is disposed around the cathode module 211 and is used to adjust the tube current according to the gate voltage signal sent by the gate voltage source 214 to control the electron beam.

[0137] In this embodiment, the cathode module 211 includes a cathode 2111 and a cathode focusing edge 2112. The cathode 2111 is connected to the tube voltage source 212. The potential of the cathode 2111 (which can also be understood as the tube voltage) ranges from -160kV to -30kV. For scenarios involving rapid tube voltage switching, where the potential of the cathode 2111 changes rapidly, the potential of the cathode 2111 is adjusted by the tube voltage signal sent by the tube voltage source 212.

[0138] The grid 213 is at a floating potential relative to the cathode 2111. The voltage of the grid 213 is adjusted within the range of -15kV to 15kV relative to the cathode 2111 potential. This can also be understood as the voltage of the grid 213 being 15kV lower or higher than the cathode 2111 potential, or being adjusted within the range of -15kV to 15kV. The tube current in the X-ray tube 100 is adjusted in real time by changing the voltage of the grid 213. The voltage of the grid 213 is adjusted by a grid voltage signal sent by the grid voltage source 214, thereby adjusting the tube current. After the electron beam is extracted from the grid 213, it is modulated by the magnetic focusing module 120 and the magnetic deflection module 130.

[0139] In one embodiment, the X-ray tube 100 further includes a housing 310 and a target disk 410. The housing 310 surrounds and forms a vacuum chamber 311. The target disk 410 is disposed within the vacuum chamber 311. A cathode module 211 and a grid 213 are disposed within the vacuum chamber 311. Within the vacuum chamber 311, the electron beam emitted by the cathode module 211 is modulated by the grid 213 and a magnetic field before bombarding the target disk 410.

[0140] In this embodiment, the housing 310 surrounds and forms a vacuum chamber 311, ensuring that the entire system is within a vacuum range. The housing 310 can be made of glass or metal to maintain a vacuum environment inside. A magnetic focusing module 120 and a magnetic deflection module 130 are disposed outside the vacuum chamber 311. The magnetic focusing module 120 and the magnetic deflection module 130 apply magnetic fields to control the electron beam within the vacuum chamber 311. Electron beam emission, magnetic focusing, and magnetic deflection occur within the vacuum chamber 311. The vacuum environment provided by the housing 310 eliminates external interference during operation, improving the stability of the X-ray tube 100.

[0141] In one embodiment, the target disk 410 is provided with an inclined surface 411 for determining the focal spot size after the modulated electron beam bombards the target disk 410 by line projection.

[0142] In this embodiment, the target disk 410 is provided with an inclined surface 411. The inclined surface 411 forms an angle with the body of the target disk 410 for line projection. After the electron beam bombards the target disk 410, it generates X-rays 510. The X-rays 510 are used to image a portion of the patient's body.

[0143] This application provides a medical device, including the X-ray tube 100 in any of the above embodiments.

[0144] In this embodiment, the medical device includes an X-ray tube 100, which can be a CT scanner, X-ray machine, etc. Please refer to [link / reference]. Figure 15The CT scanner 200 is shown. The CT scanner 200 includes an X-ray tube 100. The X-ray tube 100 generates X-rays 510, which pass through a patient lying on a bed 610 and are collected by a detector 620 for imaging. The bed 610 moves along a direction 630. Therefore, the X-rays 510 generated by the X-ray tube 100 can scan more areas of the patient. Both the X-ray tube 100 and the detector 620 are fixedly mounted on a gantry 640. The gantry 640 is rigidly connected to both the X-ray tube 100 and the detector 620, and their relative positions remain unchanged.

[0145] Please see Figure 16 As shown, the gantry 640 rotates rapidly at a speed of 650 rpm in the XY plane to image the patient's target area in a 360° direction with X-rays. The XY plane is perpendicular to the direction of movement 630 of the bed 610. During the 360° scan, the patient's dose needs to be adjusted synchronously in real time because the slice thickness varies at different angles; this is known as DOM imaging.

[0146] Those skilled in the art will clearly understand that, for the sake of convenience and brevity, the above-described division of functional units and modules is merely an example. In practical applications, the above functions can be assigned to different functional units and modules as needed, that is, the internal structure of the device can be divided into different functional units or modules to complete all or part of the functions described above. The functional units and modules in the embodiments can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit. Furthermore, the specific names of the functional units and modules are only for easy differentiation and are not intended to limit the scope of protection of this application. The specific working process of the units and modules in the above system can be referred to the corresponding process in the foregoing method embodiments, and will not be repeated here.

[0147] In the above embodiments, the descriptions of each embodiment have different focuses. For parts that are not described in detail or recorded in a certain embodiment, please refer to the relevant descriptions of other embodiments.

[0148] Those skilled in the art will recognize that the units and algorithm steps of the various examples described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are implemented in hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this application.

[0149] In the embodiments provided in this application, it should be understood that the disclosed devices / terminal equipment and methods can be implemented in other ways. For example, the device / terminal equipment embodiments described above are merely illustrative. For instance, the division of modules or units is only a logical functional division, and in actual implementation, there may be other division methods. For example, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. Furthermore, the displayed or discussed mutual coupling or direct coupling or communication connection may be through some interfaces; the indirect coupling or communication connection between devices or units may be electrical, mechanical, or other forms.

[0150] The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the units can be selected to achieve the purpose of this embodiment according to actual needs.

[0151] Furthermore, the functional units in the various embodiments of this application can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit.

[0152] If the integrated module / unit is implemented as a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, all or part of the processes in the methods of the above embodiments can also be implemented by a computer program instructing related hardware. The computer program can be stored in a computer-readable storage medium, and when executed by a processor, it can implement the steps of the various method embodiments described above. The computer program includes computer program code, which can be in the form of source code, object code, executable files, or certain intermediate forms. The computer-readable medium can include: any entity or device capable of carrying the computer program code, recording media, USB flash drives, portable hard drives, magnetic disks, optical disks, computer memory, read-only memory (ROM), random access memory (RAM), electrical carrier signals, telecommunication signals, and software distribution media, etc. It should be noted that the content included in the computer-readable medium can be appropriately added or removed according to the requirements of legislation and patent practice in the jurisdiction. For example, in some jurisdictions, according to legislation and patent practice, computer-readable media do not include electrical carrier signals and telecommunication signals.

[0153] The above-described embodiments are only used to illustrate the technical solutions of this application, and are not intended to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application, and should all be included within the protection scope of this application.

Claims

1. A method for controlling the focal spot of an X-ray tube, characterized in that, include: Obtain the current and previous operating parameter information of the X-ray tube; The magnetic control current information at the previous moment is determined based on the operating parameter information at the previous moment, and the magnetic control current information at the current moment is determined based on the operating parameter information at the current moment. The magnetic control current difference is determined based on the magnetic control current information at the previous moment and the magnetic control current information at the current moment. A preset current unit is selected based on the magnetic control current difference, and the magnetic field of the next magnetic control stage is adjusted based on the preset current unit to control the focal spot size generated by the X-ray tube.

2. The method for controlling the focal spot of an X-ray tube as described in claim 1, characterized in that, Before the steps of determining the magnetic control current information at the previous moment based on the operating parameter information at the previous moment, and determining the magnetic control current information at the current moment based on the operating parameter information at the current moment, the method further includes: The difference in operating parameters is determined based on the operating parameter information at the current moment and the operating parameter information at the previous moment; If the difference in operating parameters is greater than a critical value, then the steps of determining the magnetic control current information at the previous moment based on the operating parameter information at the previous moment, and determining the magnetic control current information at the current moment based on the operating parameter information at the current moment are executed.

3. The method for controlling the focal spot of an X-ray tube as described in claim 1, characterized in that, The step of selecting a preset current unit based on the magnetic control current difference, and adjusting the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube includes: If the magnetic control current difference is less than or equal to the current interval difference of the first preset current unit, and the magnetic control current difference is less than or equal to the current interval difference of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the magnetic control current information of the current magnetic control stage, so as to adjust the focal spot size generated by the X-ray tube.

4. The method for controlling the focal spot of an X-ray tube as described in claim 3, characterized in that, The step of selecting a preset current unit based on the magnetic control current difference and adjusting the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube further includes: If the magnetic control current difference is greater than the current range difference of the first preset current unit and less than the current range difference of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the first preset current unit to adjust the focal spot size generated by the X-ray tube.

5. The method for controlling the focal spot of an X-ray tube as described in claim 4, characterized in that, The step of selecting a preset current unit based on the magnetic control current difference and adjusting the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube further includes: If the difference in the magnetic control current is greater than the current range difference of the second preset current unit, then the magnetic field of the next magnetic control stage is adjusted according to the second preset current unit to control the focal spot size generated by the X-ray tube.

6. The method for controlling the focal spot of an X-ray tube as described in claim 1, characterized in that, After the steps of selecting a preset current unit based on the magnetic control current difference and adjusting the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube, the method further includes: The difference in operating parameters is determined based on the operating parameter information at the current moment and the operating parameter information at the previous moment; If the difference in the operating parameters is less than or equal to the critical value, the magnetic control current information of the current magnetic control stage is maintained.

7. The method for controlling the focal spot of an X-ray tube as described in claim 1, characterized in that, Before the step of obtaining the current and previous operating parameter information of the X-ray tube, the method further includes: The feedback time interval for the selected working parameter information is formed by the current time and the previous time.

8. The method for controlling the focal spot of an X-ray tube as described in claim 7, characterized in that, The step of selecting a preset current unit based on the magnetic control current difference, and adjusting the magnetic field of the next magnetic control stage based on the preset current unit to control the focal spot size generated by the X-ray tube includes: The type of the preset current unit is selected based on the feedback time interval and the difference between the magnetically controlled current; the type of the preset current unit is determined based on the time period and the difference between the current interval of the preset current unit; the time period of the preset current unit is the same as the feedback time interval. The magnetic field of the next magnetocontrol stage is controlled by the preset current unit to regulate the focal spot size generated by the X-ray tube.

9. The method for controlling the focal spot of an X-ray tube as described in claim 8, characterized in that, The step of determining the type of the preset current unit based on the difference between the time period and the current interval of the preset current unit includes: During the time period of the preset current unit, the magnetically controlled current of the preset current unit linearly increases from zero to a first current amplitude, and then linearly decreases from the first current amplitude to a first current target value; the current range difference of the preset current unit is determined based on the first current amplitude and the zero value.

10. The method for controlling the focal spot of an X-ray tube as described in claim 8, characterized in that, The step of determining the type of the preset current unit based on the difference between the time period and the current interval of the preset current unit includes: During the time period of the preset current unit, the magnetically controlled current of the preset current unit increases linearly from the initial current value to the second current amplitude, and then decreases linearly from the second current amplitude to the second current target value; the current range difference of the preset current unit is determined based on the second current amplitude and the initial current value.

11. An X-ray tube, characterized in that, include: An electron emission module (210) is used to emit an electron beam according to operating parameter information; A magnetically controlled power supply (110) is connected to the electron emission module (210). The magnetically controlled power supply (110) is used to obtain the current working parameter information and the previous working parameter information of the electron emission module (210). The magnetic control current information at the previous moment is determined based on the operating parameter information at the previous moment, and the magnetic control current information at the current moment is determined based on the operating parameter information at the current moment. The magnetic control current difference is determined based on the magnetic control current information at the previous moment and the magnetic control current information at the current moment. A preset current unit is selected based on the magnetic control current difference, and the magnetic field of the next magnetic control stage is adjusted based on the preset current unit to control the focal spot size of the electron beam.

12. The X-ray tube as claimed in claim 11, characterized in that, The X-ray tube also includes: The magnetic focusing module (120) is connected to the magnetic power supply (110) and is used to focus and control the magnetic field through which the electron beam passes according to the preset current unit provided by the magnetic power supply (110) so as to control the size of the focal spot generated by the X-ray tube.

13. The X-ray tube as claimed in claim 11, characterized in that, The X-ray tube also includes: The magnetic deflection module (130) is connected to the magnetic control power supply (110) and is used to deflect and control the magnetic field through which the electron beam passes according to the magnetic deflection current provided by the magnetic control power supply (110).

14. The X-ray tube as claimed in claim 11, characterized in that, The electron emission module (210) includes: The cathode module (211) is used to emit the electron beam according to the tube voltage signal sent by the tube voltage source (212); A gate (213) is disposed on the periphery of the cathode module (211) and is used to adjust the tube current according to the gate voltage signal sent by the gate voltage source (214) to control the electron beam.

15. The X-ray tube as claimed in claim 14, characterized in that, The X-ray tube further includes: a housing (310) that surrounds and forms a vacuum chamber (311); A target disk (410) is disposed within the vacuum chamber (311); The cathode module (211) and the gate (213) are disposed inside the vacuum chamber (311); Inside the vacuum chamber (311), the electron beam emitted by the cathode module (211) is bombarded by the target disk (410) after being controlled by the grid (213) and the magnetic field.

16. The X-ray tube as claimed in claim 15, characterized in that, The target disk (410) is provided with an inclined surface (411) for determining the focal spot size after the controlled electron beam bombards the target disk (410) by line projection.

17. A medical device, characterized in that, Including the X-ray tube as described in any one of claims 11 to 16.

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