A method and system for effectively reducing x-ray radiation dose in electrocardiogram scanning scenarios

Abstract

This invention discloses a method and system for effectively reducing X-ray radiation dose during electrocardiogram (ECG) scanning, relating to the field of artificial intelligence technology. The method includes: acquiring real-time ECG signals of the subject, identifying the R-wave and its occurrence time, and calculating the RR interval between adjacent R-waves; dividing the subject's cardiac cycle based on the RR interval and the R-wave occurrence time, and determining the intense cardiac motion phase and diastolic phase of each cardiac cycle; during the intense cardiac motion phase, controlling the X-ray tube mA value to decrease to a dose reduction mA value below the source mA value; when the current time enters the diastolic phase, controlling the X-ray tube mA value to recover from the dose reduction mA value back to the source mA value; after determining that the X-ray tube mA value has recovered and stabilized at the source mA value, a trigger signal is activated, and the acquisition of projection data is initiated based on the trigger signal. This method helps solve the problem that existing technologies cannot effectively reduce X-ray radiation dose during ECG scanning.

Description

Technical Field

[0001] This invention relates to the field of artificial intelligence technology, and in particular to a method and system for effectively reducing X-ray radiation dose in electrocardiogram (ECG) scanning scenarios. Background Technology

[0002] In the field of medical imaging diagnosis, electrocardiogram (ECG) scanning (such as ECG-gated CT scans) is an important means of diagnosing heart diseases. It obtains cardiac projection data through X-ray scanning, providing accurate information for clinical diagnosis. However, X-ray radiation can cause potential damage to the human tissues of the examined subjects. Especially for patients who require multiple scans, the cumulative risk of radiation increases significantly. Therefore, reducing X-ray radiation dose has become a key requirement for the development of ECG scanning technology.

[0003] Current methods for controlling radiation dose in electrocardiogram (ECG) scans mostly employ fixed-dose scanning or simple time-segmented dose reduction modes, which cannot dynamically adjust the radiation dose based on the real-time cardiac motion. Cardiac motion is periodic, with a phase of intense motion (such as myocardial systole) and a relatively stable phase of diastole. During the intense motion phase, the imaging clarity is poor, and high-dose radiation is not required. During diastole, the heart's motion is gentle, which is the optimal time for imaging, requiring a stable high dose to ensure image quality.

[0004] Existing technologies cannot accurately identify different stages of cardiac motion and dynamically match radiation doses. They either use high-dose scanning throughout to ensure image clarity, resulting in excessive radiation doses, or blindly reduce the dose, causing blurred images during the diastolic phase of the heart, affecting diagnostic accuracy.

[0005] Therefore, there is an urgent need for an effective method to reduce X-ray radiation dose during electrocardiogram (ECG) scans. Summary of the Invention

[0006] In view of this, the present invention proposes a method and system for effectively reducing X-ray radiation dose in electrocardiogram (ECG) scanning scenarios, which can effectively reduce X-ray radiation dose in ECG scanning scenarios.

[0007] To achieve the above objectives, the present invention provides the following technical solution: A method for effectively reducing X-ray radiation dose during electrocardiogram (ECG) scanning includes: Real-time electrocardiogram (ECG) signals of the subjects are collected, the R waves and their occurrence times are identified, and the RR interval between adjacent R waves is calculated. Based on the RR interval and the time of R wave occurrence, the cardiac cycle of the subject is divided, and the intense cardiac movement phase and the diastolic phase of each cardiac cycle are determined. During the intense cardiac activity phase, the dose reduction mA value in the control tube is reduced to below the source mA value; When the current time enters the diastolic phase of the heart, the control tube mA value is restored from the downdose mA value to the source mA value; After determining that the mA value of the X-ray tube has recovered and stabilized at the source mA value, the trigger signal takes effect, and the acquisition of projection data is started based on the trigger signal.

[0008] Based on the above technical solution, the present invention can be further improved as follows: Optionally, the step of acquiring the real-time electrocardiogram (ECG) signal of the subject and identifying the R wave and the time of R wave occurrence in the real-time ECG signal includes: The electrocardiogram signal is subjected to signal processing, which includes filtering, baseline drift correction, and QRS wave detection. The peak of the R wave and the time of R wave occurrence in the real-time electrocardiogram signal are identified by a combination of threshold discrimination and time constraints.

[0009] Optionally, the step of dividing the cardiac cycle of the subject based on the RR interval and the time of R wave occurrence, and determining the intense cardiac motion phase and the diastolic phase of each cardiac cycle, includes: Using the R wave as a reference, the time range of the intense cardiac exercise phase is determined by the interval of the preset relative time window before and after the R wave. The onset and end points of the P wave, QRS complex, and P wave are detected based on the electrocardiogram waveform. The time interval from the onset of the P wave to the end of the QRS complex is taken as the stage of intense cardiac exercise.

[0010] Optionally, the dose reduction mA value is 10% to 50% of the source mA value, and the dose reduction mA value can be adaptively adjusted according to the subject's weight, body type, heart rate, and scanning protocol parameters.

[0011] Optionally, the recovery process of the source mA value is step-type or ramp-type. After the recovery is completed, a first stabilization time threshold is set, and the trigger signal is allowed to take effect after the first stabilization time threshold is exceeded.

[0012] Optionally, after the projection data acquisition is completed, the electrocardiogram signal of the subsequent cardiac cycle is continuously monitored, and the steps of RR interval detection, dose reduction control during the intense cardiac exercise phase, source mA value recovery during the diastolic phase, and triggering projection data acquisition are executed cyclically.

[0013] Optionally, the method for effectively reducing X-ray radiation dose in electrocardiogram scanning scenarios further includes: Before scanning, the system automatically recommends a combination of source mA and dose-reduction mA values ​​based on the pre-scanned images, the subject's body type information, and the subject's clinical needs.

[0014] A system for effectively reducing X-ray radiation dose during electrocardiogram (ECG) scans includes: The ECG acquisition module is used to acquire the real-time ECG signal of the subject, identify the R wave and the time of R wave occurrence of the real-time ECG signal, and calculate the RR interval between adjacent R waves; The cycle division module is used to divide the cardiac cycle of the subject based on the RR interval and the time of R wave occurrence, and to determine the intense cardiac motion phase and the diastolic phase of each cardiac cycle. The dose control module is used to control the X-ray tube mA value to decrease to a dose reduction mA value below the source mA value during the intense cardiac exercise phase, and to control the X-ray tube mA value to recover to the source mA value from the dose reduction mA value when the current time enters the diastolic phase of the heart. The acquisition trigger module is used to trigger a signal after determining that the mA value of the X-ray tube has recovered and stabilized at the source mA value, and to start the acquisition of projection data based on the trigger signal.

[0015] An electronic device includes a memory, a processor, and a computer program stored in the memory and running on the processor, wherein the processor executes the computer program to implement the steps of the method described herein.

[0016] A non-transitory computer-readable storage medium having a computer program stored thereon, the computer program implementing the steps of the method when executed by a processor.

[0017] The present invention has the following advantages: The present invention provides a method for effectively reducing X-ray radiation dose in electrocardiogram (ECG) scanning scenarios. It precisely matches the cardiac cycle of the subject and dynamically adjusts the mA value of the X-ray tube to reduce the radiation dose during the stage of intense cardiac activity and low imaging demand, while ensuring the radiation dose during the diastolic phase of the heart. This effectively reduces unnecessary X-ray radiation and balances radiation protection with imaging clarity. Attached Figure Description

[0018] For illustrative and not limiting purposes, the present invention will now be described in conjunction with embodiments and accompanying drawings, wherein: Figure 1 This is a flowchart illustrating a method for effectively reducing X-ray radiation dose in electrocardiogram (ECG) scanning scenarios according to an embodiment of the present invention. Figure 2 This is a schematic diagram of the electrocardiogram signal waveform and the control curve of the X-ray tube mA value changing with time in an embodiment of the present invention; Figure 3 This is a schematic diagram of the main components of a system for effectively reducing X-ray radiation dose in electrocardiogram scanning scenarios according to an embodiment of the present invention; Figure 4 This is a schematic diagram of the physical structure of the electronic device provided by the present invention. Detailed Implementation

[0019] To enable those skilled in the art to better understand the present invention, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of the present invention, and not all of them. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort should fall within the scope of protection of the present invention.

[0020] It should be noted that the terms "first," "second," etc., in the specification and accompanying drawings of this invention are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such data can be used interchangeably where appropriate for the embodiments of the invention described herein. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover non-exclusive inclusion; for example, a process, method, system, product, or apparatus that comprises a series of steps or units is not necessarily limited to those steps or units explicitly listed, but may include other steps or units not explicitly listed or inherent to such processes, methods, products, or apparatus.

[0021] It should be noted that, where there is no conflict, the embodiments and features of the present invention can be combined with each other. The embodiments of the present invention will now be described in detail with reference to the accompanying drawings.

[0022] Figure 1 This is a flowchart illustrating a method for effectively reducing X-ray radiation dose during electrocardiogram (ECG) scanning, as described in this invention. Figure 1 As shown, the method for effectively reducing X-ray radiation dose in an electrocardiogram scanning scenario provided by the embodiments of the present invention includes the following steps S101 to S106.

[0023] S101: Acquire real-time electrocardiogram (ECG) signals of the subject, identify the R waves and their occurrence times in the real-time ECG signals, and calculate the RR interval between adjacent R waves.

[0024] The electrocardiogram signal is subjected to signal processing, which includes filtering, baseline drift correction, and QRS wave detection. The peak of the R wave and the time of R wave occurrence in the real-time electrocardiogram signal are identified by a combination of threshold discrimination and time constraints.

[0025] The signal processing module performs the following on the raw ECG: Bandpass filtering eliminates power frequency interference and high-frequency noise; Baseline drift correction reduces baseline drift caused by factors such as respiration; The QRS complex is identified and the R-wave peak is located using known QRS detection algorithms (such as the Pan-Tompkins algorithm or improved algorithms).

[0026] After detecting the k-th R wave and the (k+1)-th R wave, calculate their time interval RRk. Simultaneously, define the time interval [Rk, Rk+1) as a complete cardiac cycle, and calculate the relative time proportion α = (t−Rk) / RRk for any time point t within this cardiac cycle, where α ∈ [0,1).

[0027] The filtering process is used to remove power frequency interference, electromyographic interference, and environmental noise from the ECG signal, ensuring the stability and accuracy of the ECG signal. The baseline drift correction process is used to eliminate baseline shifts in the ECG signal caused by poor electrode contact, respiratory interference, etc., ensuring signal reference consistency. The QRS wave detection process is used to accurately identify the waveform characteristics of the QRS wave, providing support for R wave identification. The threshold discrimination is used to determine the amplitude standard of the R wave peak. The time constraint is used to limit the time range for R wave identification, avoid misidentification, and ensure the accuracy of R wave and R wave occurrence time identification.

[0028] S102, based on the RR interval and the time of R wave appearance, divides the cardiac cycle of the subject and determines the intense cardiac motion phase and the diastolic phase of each cardiac cycle.

[0029] Using the R wave as a reference, the time range of the intense cardiac exercise phase is determined by the interval of the preset relative time window before and after the R wave. The onset and end points of the P wave, QRS complex, and P wave are detected based on the electrocardiogram waveform. The time interval from the onset of the P wave to the end of the QRS complex is taken as the stage of intense cardiac exercise.

[0030] The diastolic phase of the heart refers to the remaining time intervals within the cardiac cycle, excluding the phases of intense cardiac activity.

[0031] S103 is a dose-reduction mA value that controls the reduction of the X-ray tube mA value to below the source mA value during periods of intense cardiac activity.

[0032] like Figure 2 As shown, the dose reduction mA value is 10% to 50% of the source mA value, and the dose reduction mA value can be adaptively adjusted according to the subject's weight, body type, heart rate, and scanning protocol parameters.

[0033] The recovery process of the source mA value is step-type or ramp-type. After the recovery is completed, a first stabilization time threshold is set. After the first stabilization time threshold is exceeded, the trigger signal is allowed to take effect.

[0034] The PQR phase (the phase of intense cardiac exercise) is divided based on a fixed relative time window of α, for example: α∈[0,0.3] is set as the approximate range covering the P wave and QRS wave, i.e., the PQR phase; Alternatively, based on statistical experience, slightly different parameters can be used for different heart rate zones (e.g., [0, 0.35] for patients with low heart rate and [0, 0.25] for patients with high heart rate).

[0035] When the scanning control module determines that the α corresponding to the current t falls within the above PQR interval, it sends a dose reduction command to the X-ray tube control module to reduce the X-ray tube mA value from the source mA value (e.g., 400mA) to the preset dose reduction mA value (e.g., 100mA).

[0036] To avoid the impact of transient current changes on the X-ray tube and power supply system, a linear or exponential ramp descent is preferred, with the transition completed within the range of tens to hundreds of milliseconds. Throughout the PQR phase, the X-ray tube maintains a dose reduction mA value or fluctuates within a small range around the dose reduction mA value, so that even if the acquired view data cannot be used for high-quality reconstruction due to rapid cardiac motion, there will be no significant dose waste.

[0037] S104, when the current time enters the diastolic phase of the heart, the control tube mA value is restored from the dose-reduction mA value to the source mA value.

[0038] like Figure 2 As shown, the ST phase (diastolic phase) typically corresponds to myocardial repolarization and late diastole, and is the preferred phase for obtaining clear coronary artery images in clinical practice. The ST phase is defined as α∈[0.6,0.8] or other ranges optimized according to clinical needs.

[0039] When the current α corresponding to the current t is detected to enter the preset range of the ST stage, the scan control module issues an mA recovery command, controlling the X-ray tube current to recover from the reduced dose mA value to the source mA value. The recovery process can be as follows: Stepwise approach: Increment mA in fractional steps until the source mA value is reached; Ramp mode: Smoothly transitions from the dose mA to the source mA value within a preset time (e.g., 100ms~300ms).

[0040] Meanwhile, the system records the time point of mA recovery and further monitors a short stable time window (e.g., 10~50ms) after mA reaches the source mA value to ensure that the X-ray tube output current does not fluctuate significantly.

[0041] S105: After determining that the X-ray tube mA value has recovered and stabilized at the source mA value, the trigger signal takes effect, and the acquisition of projection data is started based on the trigger signal.

[0042] When the X-ray tube current recovers and stabilizes at the source mA value, the trigger logic is activated, and the scan control module sends a trigger signal to the data acquisition module. During the active period of the trigger, the data acquisition module samples and integrates the detector output to form view data within the corresponding angle range.

[0043] Within a cardiac cycle, one or more acquisition windows can typically be deployed during the ST phase to meet single-phase or multi-phase reconstruction requirements. Each acquisition window is triggered within a high-dose region where mA is stable to ensure the image signal-to-noise ratio.

[0044] For subsequent cardiac cycles, the system repeats the cycle of RR detection, mA reduction during the PQR phase, mA recovery during the ST phase, and trigger acquisition. Once the preset number of scans is reached or the preset anatomical range is covered, the scan ends and the reconstruction phase begins.

[0045] The method for effectively reducing X-ray radiation dose in electrocardiogram scanning scenarios also includes: After the projection data acquisition is completed, the ECG signal of the subsequent cardiac cycle is continuously monitored, and the steps of RR interval detection, dose reduction control during the intense cardiac exercise phase, source mA value recovery during the diastolic phase, and triggering projection data acquisition are executed in a loop.

[0046] Before scanning, the system automatically recommends a combination of source mA and dose-reduction mA values ​​based on the pre-scanned images, the subject's body type information, and the subject's clinical needs.

[0047] To further improve the accuracy of phase division, this invention also introduces waveform feature point detection such as the P-wave start point, QRS start and end point, and ST segment start point, to provide a more refined definition of the PQR and ST stages.

[0048] Based on R-wave detection, the starting point of P-wave is identified by using algorithms such as morphological features and energy distribution on signals within a certain time window before the R-wave. Threshold detection or derivative-based inflection point detection is performed on the leading and trailing edges of the QRS group to determine the start and end points of the QRS wave.

[0049] After the QRS complex ends, slope and amplitude analysis are performed on the ECG signal to identify the start of the ST segment. The ST segment typically appears as a plateau near the isoelectric line, followed by the T wave.

[0050] PQR phase: from the start of the detected P wave to the end of the QRS wave; ST phase: A specific relative time range from several milliseconds (e.g., 20-60 ms) after the end of the QRS wave to near the peak of the T wave or before the end of the T wave.

[0051] With the above more refined definition, the CT system can implement mA reduction control in a more accurate high-motion-rate-restriction (PQR) range and maintain high mA and trigger acquisition in the truly stable ST segment, thereby further reducing ineffective doses while ensuring image stability and clarity.

[0052] Based on the above, an adaptive parameter optimization strategy is introduced.

[0053] Before scanning, the system acquires information such as the patient's height, weight, body type, and gender, and can combine this information with pre-scan or historical examination data to estimate the patient's radiation penetration requirements. The system uses a built-in dose optimization model to automatically provide recommended combinations of source mA and dose reduction mA values, for example: For patients with smaller body size and lower heart rate, a lower source mA value should be used, and the proportion of dose-reduction mA value can be even lower. For patients with larger body size and higher heart rate, the source mA value is appropriately increased to ensure the quality of key phase images, while the dose-reduction mA value is relatively high but still significantly lower than the source mA value to balance noise and dose.

[0054] During the scanning process, the system continuously monitors the changing trend of the RR spacing: If the heart rate is stable and the RR interval fluctuation is within the preset threshold (e.g., ±10%), then the current parameters will be used. If a drastic change in the RR interval is detected or an arrhythmia (such as premature atrial contractions) occurs, the system can automatically adjust the relative time windows of PQR and ST to better match the actual waveform characteristics and avoid the critical phase deviating from the high mA range.

[0055] For severe cases of arrhythmia, safety strategies can be implemented: widening the mA adjustment range or briefly pausing the dose reduction mode within a specific cardiac cycle to avoid missing critical diagnostic phase data.

[0056] In situations requiring multiple scans to acquire sufficient z-axis coverage or multi-phase imaging, the system can perform overall optimization of the mA strategy for different scans: Some loops prioritize acquiring high-quality ST phase data to maintain a high source mA value; Some loops can further increase the dose reduction ratio in the PQR phase or even temporarily shut down X-rays to achieve more aggressive dose compression.

[0057] Through the aforementioned adaptive and optimization strategies, the method of this invention not only achieves fine control of mA within a single cardiac cycle, but also achieves a comprehensive balance between overall dose and image quality over multiple cycles and time scales.

[0058] One embodiment is as follows: In this embodiment, the ECG scan scenario is a cardiac CT scan, the subject is an adult female weighing 60kg with a heart rate of 80 beats / minute, the source mA value is determined to be 180mA after the pre-scan, and the dose reduction mA value is set to 30% of the source mA value (i.e., 54mA).

[0059] S101. The real-time electrocardiogram (ECG) signal of the subject is collected by the ECG monitoring device. The ECG signal is filtered (50Hz power frequency interference and electromyographic interference are filtered out), and baseline drift correction is performed. Then, the QRS wave is detected and processed. Based on the combination of threshold discrimination and time constraint, the peak of the R wave and the time of R wave occurrence are identified, and the RR interval between adjacent R waves is calculated to be 0.75s.

[0060] S102. Based on the RR interval and the time of R wave appearance, the cardiac cycle is divided into 0.75s. Taking the R wave as a reference, the time interval of 0.2s before and after the R wave (a total of 0.4s) is determined as the stage of intense cardiac exercise. At the same time, the P wave start point, QRS wave start point and end point of the electrocardiogram waveform are detected. The time interval from the P wave start point to the QRS wave end point (0.3s) is combined with the time interval before and after the R wave to determine the final time range of the intense cardiac exercise stage as 0.4s.

[0061] S103. During periods of intense cardiac activity, control the X-ray tube mA value to reduce to 54 mA (30% of the source mA value) and perform low-dose scanning to reduce radiation exposure.

[0062] S104. When the heart enters the diastolic phase, the control tube mA value is restored to 180mA (source mA value) in a ramp manner. The first stable time threshold is set to 2s. When the mA value is stably restored to 180mA and lasts for 2s, the trigger signal takes effect.

[0063] S105. Based on the trigger signal, initiate projection data acquisition to ensure that the acquired cardiac images are clear and meet clinical diagnostic needs.

[0064] S106. After the current projection data acquisition is completed, continuously monitor the real-time electrocardiogram signal of the subsequent cardiac cycle, and repeat the steps S101 to S105 above until the entire cardiac CT scan task is completed.

[0065] In this embodiment, through the above control method, the radiation exposure of the examinee is reduced by more than 60% compared with the existing fixed-dose scanning, while the acquired cardiac images are clear and fully meet the clinical diagnostic needs, verifying the effectiveness and practicality of this method.

[0066] Figure 3 This is a schematic diagram of the main components of a system for effectively reducing X-ray radiation dose during electrocardiogram (ECG) scanning, as described in an embodiment of the present invention. Figure 3As shown, the system 1 for effectively reducing X-ray radiation dose in an electrocardiogram (ECG) scanning scenario provided by this embodiment of the invention includes an ECG acquisition module 10, a period division module 20, a dose control module 30, and an acquisition trigger module 40.

[0067] ECG acquisition module 10 is used to acquire real-time ECG signals of the subject, identify the R waves and the time of R wave occurrence of the real-time ECG signals, and calculate the RR interval between adjacent R waves; The cycle division module 20 is used to divide the cardiac cycle of the subject based on the RR interval and the time of R wave occurrence, and to determine the intense cardiac movement phase and the diastolic phase of each cardiac cycle. The dose control module 30 is used to control the X-ray tube mA value to decrease to a dose reduction mA value below the source mA value during the intense cardiac exercise phase, and to control the X-ray tube mA value to recover to the source mA value from the dose reduction mA value when the current time enters the cardiac diastolic phase. The acquisition trigger module 40 is used to trigger a signal after determining that the mA value of the X-ray tube has recovered and stabilized at the source mA value, and to start the acquisition of projection data based on the trigger signal.

[0068] Figure 4 This is a schematic diagram of the physical structure of an electronic device provided in an embodiment of the present invention, such as... Figure 4 As shown, the electronic device 50 includes: a processor 501, a memory 502, and a bus 503; The processor 501 and the memory 502 communicate with each other via the bus 503. The processor 501 is used to call program instructions in the memory 502 to execute the methods provided in the above-described method embodiments, and to execute the methods provided in the embodiments of the present invention.

[0069] This embodiment provides a non-transitory computer-readable storage medium that stores computer instructions, which cause a computer to execute the method provided in this embodiment of the invention.

[0070] Those skilled in the art will understand that all or part of the steps of the above method embodiments can be implemented by hardware related to program instructions. The aforementioned program can be stored in a computer-readable storage medium. When the program is executed, it performs the steps of the above method embodiments. The aforementioned storage medium includes various storage media capable of storing program code, such as ROM, RAM, magnetic disk, or optical disk.

[0071] The specific embodiments described above do not constitute a limitation on the scope of protection of this invention. Those skilled in the art should understand that various modifications, combinations, sub-combinations, and substitutions can occur depending on design requirements and other factors. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of this invention should be included within the scope of protection of this invention.

Claims

1. A method for effectively reducing X-ray radiation dose during electrocardiogram (ECG) scanning, characterized in that, include: Real-time electrocardiogram (ECG) signals of the subjects are collected, the R waves and their occurrence times are identified, and the RR interval between adjacent R waves is calculated. Based on the RR interval and the time of R wave occurrence, the cardiac cycle of the subject is divided, and the intense cardiac movement phase and the diastolic phase of each cardiac cycle are determined. During the intense cardiac activity phase, the dose reduction mA value in the control tube is reduced to below the source mA value. When the current time enters the diastolic phase of the heart, the control tube mA value is restored from the downdose mA value to the source mA value; After determining that the mA value of the X-ray tube has recovered and stabilized at the source mA value, the trigger signal takes effect, and the acquisition of projection data is started based on the trigger signal.

2. The method for effectively reducing X-ray radiation dose in electrocardiogram scanning scenarios according to claim 1, characterized in that, The process of collecting real-time electrocardiogram (ECG) signals from the subject and identifying the R wave and its occurrence time includes: The electrocardiogram signal is subjected to signal processing, which includes filtering, baseline drift correction, and QRS wave detection. The peak of the R wave and the time of R wave occurrence in the real-time electrocardiogram signal are identified by a combination of threshold discrimination and time constraints.

3. The method for effectively reducing X-ray radiation dose in electrocardiogram scanning scenarios according to claim 2, characterized in that, The process of dividing the cardiac cycle of the subject based on the RR interval and the time of R wave occurrence, and determining the intense cardiac motion phase and diastolic phase of each cardiac cycle, includes: Using the R wave as a reference, the time range of the intense cardiac exercise phase is determined by the interval of the preset relative time window before and after the R wave. The onset and end points of the P wave, QRS complex, and P wave are detected based on the electrocardiogram waveform. The time interval from the onset of the P wave to the end of the QRS complex is taken as the stage of intense cardiac exercise.

4. The method for effectively reducing X-ray radiation dose in electrocardiogram scanning scenarios according to claim 1, characterized in that, The dose reduction mA value is 10% to 50% of the source mA value, and the dose reduction mA value can be adaptively adjusted according to the subject's weight, body type, heart rate, and scanning protocol parameters.

5. The method for effectively reducing X-ray radiation dose in electrocardiogram scanning scenarios according to claim 1, characterized in that, The recovery process of the source mA value is step-type or ramp-type. After the recovery is completed, a first stabilization time threshold is set. After the first stabilization time threshold is exceeded, the trigger signal is allowed to take effect.

6. The method for effectively reducing X-ray radiation dose in electrocardiogram scanning scenarios according to claim 1, characterized in that, After the projection data acquisition is completed, the ECG signal of the subsequent cardiac cycle is continuously monitored, and the steps of RR interval detection, dose reduction control during the intense cardiac exercise phase, source mA value recovery during the diastolic phase, and triggering projection data acquisition are executed cyclically until all scanning tasks are completed.

7. The method for effectively reducing X-ray radiation dose in electrocardiogram scanning scenarios according to claim 1, characterized in that, The method for effectively reducing X-ray radiation dose in electrocardiogram scanning scenarios further includes: Before scanning, the system automatically recommends a combination of source mA and dose-reduction mA values ​​based on the pre-scanned images, the subject's body type information, and the subject's clinical needs.

8. A system for effectively reducing X-ray radiation dose during electrocardiogram (ECG) scanning, characterized in that, include: The ECG acquisition module is used to acquire the real-time ECG signal of the subject, identify the R wave and the time of R wave occurrence of the real-time ECG signal, and calculate the RR interval between adjacent R waves; The cycle division module is used to divide the cardiac cycle of the subject based on the RR interval and the time of R wave occurrence, and to determine the intense cardiac motion phase and the diastolic phase of each cardiac cycle. The dose control module is used to control the X-ray tube mA value to decrease to a dose reduction mA value below the source mA value during the intense cardiac exercise phase, and to control the X-ray tube mA value to recover to the source mA value from the dose reduction mA value when the current time enters the diastolic phase of the heart. The acquisition trigger module is used to trigger a signal after determining that the mA value of the X-ray tube has recovered and stabilized at the source mA value, and to start the acquisition of projection data based on the trigger signal.

9. An electronic device comprising a memory, a processor, and a computer program stored in the memory and running on the processor, characterized in that, When the processor executes the computer program, it implements the steps of the method as described in any one of claims 1 to 7.

10. A non-transitory computer-readable medium having a computer program stored thereon, characterized in that, When the computer program is executed by a processor, it implements the steps of the method as described in any one of claims 1 to 7.

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