Method for generating a cardiac magnetic resonance imaging sequence and method for cardiac magnetic resonance scanning

Abstract

The application relates to a cardiac magnetic resonance imaging sequence generation method and a cardiac magnetic resonance scanning method, which comprises the following steps: acquiring a cycle T of a cardiac cycle of an electrocardiosignal and determining a number N of cardiac cycles required for generating an imaging sequence; setting whether a magnetization pulse signal is applied, a type of the magnetization pulse signal and a signal acquisition time T1 of each cardiac cycle in the N cardiac cycles; in a cardiac cycle in which the magnetization pulse signal is applied, determining a magnetization preparation time T2 and a waiting time T3 according to the type of the magnetization pulse signal; the waiting time T3 is a time for waiting for the magnetization pulse signal to recover; and generating the imaging sequence according to the type of the magnetization pulse signal, the magnetization preparation time T2, the waiting time T3 and the signal acquisition time T1 of each cardiac cycle. Through the application, a sequence can be compatible with multiple timing types, and the problem that one sequence cannot be compatible with multiple timing types in the prior art is solved.

Description

Technical Field

[0001] This application relates to the field of magnetic resonance imaging technology, and in particular to a method for generating cardiac magnetic resonance imaging sequences and a method for cardiac magnetic resonance scanning. Background Technology

[0002] A typical magnetic resonance imaging (MRI) system comprises the following components: a magnet, gradient coils, a radio frequency (RF) transmitting coil, an RF receiving coil, and a signal processing and image reconstruction unit. The spin of a hydrogen nucleus in the human body can be represented by a small magnetic needle. In the strong magnetic field provided by the magnet, the hydrogen nucleus transitions from a disordered thermal equilibrium state to one where it is partially aligned with and partially opposed to the main magnetic field. The difference between these two states forms the net magnetization vector. The hydrogen nucleus precesses around the main magnetic field, with the precession frequency proportional to the magnetic field strength. The gradient unit generates a magnetic field whose intensity varies with spatial position, used for spatial signal encoding. The RF transmitting coil flips the hydrogen nucleus from the direction of the main magnetic field to the transverse plane, causing it to precess around the main magnetic field. A current signal is induced in the RF receiving coil. The signal processing and image reconstruction unit then obtains an image of the imaged tissue.

[0003] Longitudinal quantitative imaging (T1 mapping) of the heart is of significant diagnostic value for diseases such as myocardial infarction, fibrosis, and scarring because it can reflect the inherent properties of myocardial tissue. Existing cardiac T1 mapping imaging techniques offer many different time series types, and a single sequence cannot be compatible with multiple time series types.

[0004] There is currently no effective solution to the problem that a single sequence cannot be compatible with multiple time series types in existing technologies. Summary of the Invention

[0005] This embodiment provides a method for generating cardiac magnetic resonance imaging sequences and a method for cardiac magnetic resonance scanning, in order to solve the problem in the prior art that a single sequence cannot be compatible with multiple time series types.

[0006] Firstly, this embodiment provides a method for generating cardiac magnetic resonance imaging sequences, the method comprising:

[0007] The period T of the cardiac cycle of the electrocardiogram signal is acquired, and the number N of cardiac cycles required to generate the imaging sequence is determined.

[0008] Set whether to apply magnetization pulse signals within N cardiac cycles, the type of application, and the signal acquisition time T1 for each cardiac cycle;

[0009] During the cardiac cycle in which the magnetization pulse signal is applied, the magnetization preparation time T2 and the waiting time T3 are determined according to the type of magnetization pulse signal applied; the waiting time T3 is the time to wait for the magnetization pulse signal to recover.

[0010] The imaging sequence is generated based on the type of magnetization pulse signal applied, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1 for each cardiac cycle.

[0011] In some embodiments, generating the imaging sequence based on the type of magnetization pulse signal applied, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1 for each cardiac cycle includes:

[0012] During the cardiac cycle in which the magnetization pulse signal is applied, a blank time T4 is generated based on the magnetization preparation time T2, the waiting time T3, the signal acquisition time T1, and the period T of the cardiac cycle.

[0013] A first sequence is generated based on the type of magnetization pulse signal applied, the blank time T4, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1;

[0014] During a cardiac cycle in which no magnetization pulse signal is applied, a second sequence is generated based on the signal acquisition time T1;

[0015] The imaging sequence is generated based on the first sequence and the second sequence.

[0016] In some embodiments, generating a blank time T4 within the cardiac cycle during which the magnetization pulse signal is applied, based on the magnetization preparation time T2, the waiting time T3, the signal acquisition time T1, and the period T of the cardiac cycle, includes:

[0017] The blank time T4 is calculated based on the magnetization preparation time T2, the waiting time T3, the signal acquisition time T1, the signal acquisition parameter β, the cardiac cycle period T, and the cardiac diastolic parameter α.

[0018] In some embodiments, generating the first sequence based on the type of magnetization pulse signal applied, the blank time T4, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1 includes:

[0019] After waiting for the blank time T4 of the current cardiac cycle at the first moment of the current cardiac cycle, the magnetization preparation stage is entered and the magnetization pulse signal of the current cardiac cycle is applied; the first moment is determined according to the cardiac diastolic parameter α and the period T of the cardiac cycle;

[0020] After reaching the magnetization preparation time T2 of the current cardiac cycle, the system enters a waiting phase and the magnetization pulse signal is restored.

[0021] After the waiting time T3 of the current cardiac cycle is reached, the signal acquisition stage begins and the echo signal of the heart is acquired.

[0022] The duration of the magnetization preparation phase is the magnetization preparation time T2, the duration of the waiting phase is the waiting time T3, and the duration of the signal acquisition phase is the acquisition time T1.

[0023] In some embodiments, the number N of cardiac cycles required to generate the imaging sequence is determined based on the evolution fitting function of the acquired signals, wherein the magnetization pulse signal of each cardiac cycle is different.

[0024] In some embodiments, the magnetization pulse signal is: a longitudinal relaxation pulse signal, a transverse relaxation pulse signal, an inversion recovery pulse signal, and a saturation recovery pulse signal.

[0025] Secondly, this embodiment provides a cardiac magnetic resonance imaging (MRI) scanning method, the method comprising:

[0026] The period T of the cardiac cycle of the electrocardiogram signal is acquired and the number N of cardiac cycles required to generate the imaging sequence is determined, and at least one of the cardiac cycles is divided into a magnetization preparation period, a waiting period and an acquisition period.

[0027] During the magnetization preparation period, the application of a magnetization pulse signal and the type of the magnetization pulse signal are specified.

[0028] A signal acquisition time T1 for at least one cardiac cycle is set during the acquisition period;

[0029] During the cardiac cycle in which the magnetization pulse signal is applied, the magnetization preparation time T2 and the waiting time T3 of the waiting period are determined according to the type of magnetization pulse signal applied; the waiting time T3 is the time to wait for the magnetization pulse signal to recover.

[0030] The imaging sequence is generated based on the type of magnetization pulse signal applied, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1;

[0031] The imaging sequence is executed to generate cardiac magnetic resonance images.

[0032] In some embodiments, the N cardiac cycles include a first cardiac cycle and a second cardiac cycle, and the types of magnetization pulse signals within the first cardiac cycle and the second cardiac cycle are set via a drop-down list.

[0033] In some embodiments, during the acquisition period, signal acquisition is set to be performed via a selection button.

[0034] Thirdly, this embodiment provides a cardiac magnetic resonance imaging sequence generation device, characterized in that it includes:

[0035] The acquisition module is used to acquire the period T of the cardiac cycle of the electrocardiogram signal and determine the number N of cardiac cycles required to generate the imaging sequence;

[0036] The setting module is used to set whether a magnetization pulse signal is applied within N cardiac cycles, the type of application, and the signal acquisition time T1 for each cardiac cycle;

[0037] The first determining module is used to determine the magnetization preparation time T2 and the waiting time T3 according to the type of magnetization pulse signal applied during the cardiac cycle in which the magnetization pulse signal is applied; the waiting time T3 is the time to wait for the magnetization pulse signal to recover.

[0038] The second determining module is used to generate the imaging sequence based on the type of magnetization pulse signal applied, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1 of each cardiac cycle.

[0039] Compared with the prior art, the cardiac magnetic resonance imaging sequence generation method, apparatus, electronic device, storage medium and cardiac magnetic resonance scanning method provided in this embodiment, according to the number N of cardiac cycles required to generate the imaging sequence, sets whether a magnetization pulse signal is applied in N cardiac cycles, the type of application, and the signal acquisition time T1 of each cardiac cycle, determines the magnetization preparation time T2, waiting time T3 and signal acquisition time T1 in the cardiac cycle in which the magnetization pulse signal is applied based on the selected magnetization pulse signal, determines the timing of the imaging sequence to be generated, and thus generates the imaging sequence. This realizes that one sequence can be compatible with multiple timing types, and solves the problem in the prior art that one sequence cannot be compatible with multiple timing types.

[0040] Details of one or more embodiments of this application are set forth in the following drawings and description to make other features, objects and advantages of this application more readily apparent. Attached Figure Description

[0041] The accompanying drawings, which are included to provide a further understanding of this application and form part of this application, illustrate exemplary embodiments of this application and are used to explain this application, but do not constitute an undue limitation of this application. In the drawings:

[0042] Figure 1 This is a hardware structure block diagram of a terminal that generates a cardiac magnetic resonance imaging sequence in this embodiment;

[0043] Figure 2 This is a flowchart of a method for generating cardiac magnetic resonance imaging sequences according to this embodiment;

[0044] Figure 3 This is a flowchart of a method for generating cardiac magnetic resonance imaging sequences according to a preferred embodiment of the present invention;

[0045] Figure 4 This is a schematic diagram of the electrocardiogram timing and sequence timing of this preferred embodiment;

[0046] Figure 5 This is a schematic diagram of the parameter card for the imaging sequence parameters of this preferred embodiment;

[0047] Figure 6 This is a schematic diagram of the cardiac magnetic resonance imaging sequence generated according to this preferred embodiment;

[0048] Figure 7 This is a schematic diagram of how the cardiac magnetic resonance T1 mapping imaging sequence in this embodiment is configured to form a corrected review inversion recovery sequence;

[0049] Figure 8 This is a structural block diagram of a cardiac magnetic resonance imaging sequence generation device according to this embodiment. Detailed Implementation

[0050] To better understand the purpose, technical solution, and advantages of this application, the application is described and illustrated below in conjunction with the accompanying drawings and embodiments.

[0051] Unless otherwise defined, the technical or scientific terms used in this application shall have the general meaning as understood by one of ordinary skill in the art to which this application pertains. Words such as “a,” “an,” “an,” “the,” “the,” and “these,” used in this application, do not indicate quantitative limitation and may be singular or plural. The terms “comprising,” “including,” “having,” and any variations thereof used in this application are intended to cover non-exclusive inclusion; for example, a process, method, system, product, or device that comprises a series of steps or modules (units) is not limited to the listed steps or modules (units) but may include steps or modules (units) not listed, or may include other steps or modules (units) inherent to such processes, methods, products, or devices. The terms “connected,” “linked,” and “coupled,” used in this application, are not limited to physical or mechanical connections but may include electrical connections, whether direct or indirect. The term “multiple” used in this application refers to two or more. The "and / or" operator describes the relationship between related objects, indicating that three relationships can exist. For example, "A and / or B" can represent three cases: A alone, A and B simultaneously, and B alone. Typically, the character " / " indicates that the objects before and after it are in an "or" relationship. The terms "first," "second," and "third," etc., used in this application are merely for distinguishing similar objects and do not represent a specific ordering of the objects.

[0052] The method embodiments provided in this example can be executed on a terminal, computer, or similar computing device. For example, it can run on a terminal. Figure 1 This is a hardware structure block diagram of a terminal that generates a cardiac magnetic resonance imaging sequence according to this embodiment. Figure 1 As shown, a terminal may include one or more ( Figure 1 Only one is shown in the diagram. A processor 102 and a memory 104 for storing data are also included. The processor 102 may be, but is not limited to, a microprocessor (MCU) or a programmable logic device (FPGA). The terminal may also include a transmission device 106 for communication functions and an input / output device 108. Those skilled in the art will understand that… Figure 1 The structure shown is for illustrative purposes only and does not limit the structure of the terminal described above. For example, the terminal may also include components that are larger than... Figure 1 The more or fewer components shown, or having the same Figure 1 The different configurations shown are illustrated.

[0053] The memory 104 can be used to store computer programs, such as application software programs and modules, like the computer program corresponding to the generation of a cardiac magnetic resonance imaging sequence in this embodiment. The processor 102 executes various functional applications and data processing by running the computer program stored in the memory 104, thereby implementing the above-described method. The memory 104 may include high-speed random access memory, and may also include non-volatile memory, such as one or more magnetic storage devices, flash memory, or other non-volatile solid-state memory. In some instances, the memory 104 may further include memory remotely located relative to the processor 102, and these remote memories can be connected to the terminal via a network. Examples of such networks include, but are not limited to, the Internet, corporate intranets, local area networks, mobile communication networks, and combinations thereof.

[0054] The transmission device 106 is used to receive or send data via a network. This network includes a wireless network provided by the terminal's communication provider. In one example, the transmission device 106 includes a Network Interface Controller (NIC), which can connect to other network devices via a base station to communicate with the Internet. In another example, the transmission device 106 can be a Radio Frequency (RF) module used for wireless communication with the Internet.

[0055] This embodiment provides a method for generating cardiac magnetic resonance imaging sequences. Figure 2 This is a flowchart of a cardiac magnetic resonance imaging sequence generation method according to this embodiment, such as... Figure 2 As shown, the process includes the following steps:

[0056] Step S210: Obtain the period T of the cardiac cycle of the electrocardiogram signal and determine the number N of cardiac cycles required to generate the imaging sequence.

[0057] Specifically, the period T of the cardiac cycle of the electrocardiogram (ECG) signal of the tested user is acquired, and the number N of cardiac cycles of the ECG signal of the tested user required to generate the imaging sequence is determined, where N is a positive integer. For different users, the period T of the cardiac cycle of their ECG signal is different. Based on the evolution fitting function of the acquired signal, the number N of cardiac cycles required to generate the imaging sequence is determined, and the magnetization pulse signal of each cardiac cycle is different. For example, if the evolution fitting function of the acquired signal contains n parameters to be determined, then the number of cardiac cycles required to generate the imaging sequence is at least n, where n is a positive integer. Further exemplarily, the evolution fitting function can adopt the two-parameter model corresponding to formula (1) or the corresponding formula.

[0058] (2) is represented by the three-parameter model:

[0059]

[0060] S(t)=A-Bexp(-t / T1*) Formula (2)

[0061] Where A and B are constants to be solved, t is the inversion time (TI) value, T1 is the longitudinal relaxation time, and T1* is the conjugate function of T1. Each scanned image is represented by S(t), and multiple scanned images can yield multiple S(t). By fitting multiple S(t), A and B can be solved.

[0062] Step S220: Set whether magnetization pulse signals are applied within N cardiac cycles, the type of application, and the signal acquisition time T1 for each cardiac cycle.

[0063] Specifically, based on the number N of cardiac cycles required to generate the imaging sequence determined in step S210, the application of magnetization pulse signals, their types, and the signal acquisition time T1 for each of the N cardiac cycles are set. To obtain the evolution fitting function of the acquired signals, each of the N cardiac cycles is divided into a magnetization preparation period, a waiting period, and an acquisition period. The magnetization preparation periods in two or more cardiac cycles need to be set to different magnetization pulse signals (magnetization preparation pulse signals), and the corresponding signal acquisition times T1 for these different magnetization pulse signals are also different. Within the acquisition time T1 of the imaging sequence, the signal acquisition phase begins, and the echo signals of the heart are acquired.

[0064] The magnetization pulse signal here can be an inversion recovery pulse (IR), a saturation recovery pulse (SR), a transverse relaxation pulse signal (T2Prep), or a longitudinal relaxation pulse signal (T1).

[0065] Step S230: During the cardiac cycle in which the magnetization pulse signal is applied, determine the magnetization preparation time T2 and the waiting time T3 according to the type of magnetization pulse signal applied; the waiting time T3 is the time to wait for the magnetization pulse signal to recover.

[0066] Specifically, N magnetization pulse signals can be applied over N cardiac cycles. The magnetization preparation time T2 and the waiting time T3 for each cardiac cycle are determined based on the type of magnetization pulse signal within each cardiac cycle. For different magnetization pulse signals, the magnetization preparation time T2 and the waiting time T3 for each cardiac cycle are different. After the waiting time T3 of the current cardiac cycle is reached, the signal acquisition phase begins, and the echo signal from the heart is acquired. The waiting time T3 for each cardiac cycle is used to wait for the recovery of the magnetization pulse signal, maximizing the difference in the acquired signals for different analytes.

[0067] Step S240: Generate an imaging sequence based on the type of magnetization pulse signal applied, magnetization preparation time T2, waiting time T3, and signal acquisition time T1 for each cardiac cycle.

[0068] Specifically, an imaging sequence is generated based on the type of magnetization pulse signal applied, magnetization preparation time T2, waiting time T3, and signal acquisition time T1 determined in the preceding steps. Image scanning is then performed based on the generated imaging sequence.

[0069] Through the above steps, based on the number N of cardiac cycles required to generate the imaging sequence, the application of magnetization pulse signals within N cardiac cycles is set, along with the type of magnetization pulse signal and the signal acquisition time T1 for each cardiac cycle. The magnetization preparation time T2, waiting time T3, and signal acquisition time T1 within the cardiac cycle for which the magnetization pulse signal is applied are determined based on the selected magnetization pulse signal. This determines the timing of the imaging sequence to be generated, thus generating the imaging sequence. This achieves compatibility of multiple timing types with a single sequence, solving the problem in existing technologies where a single sequence cannot be compatible with multiple timing types.

[0070] In some embodiments, an imaging sequence is generated based on the type of magnetization pulse signal applied, magnetization preparation time T2, waiting time T3, and signal acquisition time T1. This includes: generating a blank time T4 within the cardiac cycle in which the magnetization pulse signal is applied, based on the magnetization preparation time T2, waiting time T3, signal acquisition time T1, and the period T of the cardiac cycle; generating a first sequence based on the type of magnetization pulse signal applied, blank time T4, magnetization preparation time T2, waiting time T3, and signal acquisition time T1; generating a second sequence within the cardiac cycle in which no magnetization pulse signal is applied, based on the signal acquisition time T1; and generating an imaging sequence based on the first and second sequences. Within the cardiac cycle in which no magnetization pulse signal is applied, the timing can be determined based on the signal acquisition time T1, thereby generating the second sequence. Here, the blank time T4 can be the time interval between the start time of the magnetization preparation time T2 and the R wave of the cardiac signal.

[0071] Specifically, during the cardiac cycle in which the magnetization pulse signal is applied, the blank time T4 of the cardiac cycle is calculated based on the magnetization preparation time T2, the waiting time T3, the signal acquisition time T1, the signal acquisition parameter β, the period T of the cardiac cycle, and the diastolic parameter α. For example, the blank time T4 can be calculated using the following formula: T4 = α*T - T2 - T3 - β*T1, where α is the diastolic parameter and β is the signal acquisition parameter.

[0072] For example, the diastolic parameter α can be determined based on the position of mid-diastole within the cardiac cycle. For instance, α can be set to 0.75, indicating that mid-diastole is approximately at the 75th percentile of the entire cardiac cycle. The signal acquisition parameter β can be determined based on the characteristics of the signal acquisition. For example, β can be set to 0.5, indicating that the entire acquisition is linear, transitioning from a negative gradient to a positive gradient, with the K-space center passing through 0 at the 50th percentile.

[0073] In some embodiments, an imaging sequence is generated based on the type of magnetization pulse signal applied, a blank time T4, a magnetization preparation time T2, a waiting time T3, and a signal acquisition time T1. This includes: waiting for the blank time T4 of the current cardiac cycle at the first moment of the current cardiac cycle, entering the magnetization preparation stage and applying the magnetization pulse signal of the current cardiac cycle; the first moment is determined based on the cardiac diastolic parameter α and the period T of the cardiac cycle, where the first moment can be the moment when the R wave of the cardiac signal is located; after reaching the magnetization preparation time T2 of the current cardiac cycle, entering the waiting stage and recovering the magnetization pulse signal; and after reaching the waiting time T3 of the current cardiac cycle, entering the signal acquisition stage and acquiring the echo signal of the heart.

[0074] Within the cardiac cycle in which the magnetization pulse signal is applied, the duration of the magnetization preparation phase is magnetization preparation time T2, the duration of the waiting phase is waiting time T3, and the duration of the signal acquisition phase is acquisition time T1. After determining the blank time T4, magnetization preparation time T2, waiting time T3, and signal acquisition time T1, an imaging sequence can be generated based on the corresponding times determined by the cardiac cycle; within the cardiac cycle in which no magnetization pulse signal is applied, an imaging sequence is generated based on the signal acquisition time T1.

[0075] The present embodiment will now be described and illustrated through preferred embodiments.

[0076] Figure 3 This is a flowchart of a method for generating cardiac magnetic resonance imaging sequences according to a preferred embodiment of the present invention, such as... Figure 3 The process includes the following steps:

[0077] Step S310: Select the number N required for the time map of the imaging sequence to span the cardiac cycle.

[0078] Step S320: Generate the number of combined image blocks to be collected based on the selected number of cardiac cycles N.

[0079] Specifically, such as Figure 4 As shown, the top row is the ECG timing diagram, and the bottom row is the sequence correlation diagram. You can see three squares at the diastolic position of each cardiac cycle, representing the magnetization preparation module 401, the waiting time module 402, and the acquisition module 403, respectively. The blank time between the ECG R wave and the magnetization preparation module is automatically calculated by the system based on different heart rates and cardiac cycles. Assuming the cardiac cycle is RR, the magnetization preparation time is set to tMP, the waiting time is set to TT, and the total acquisition time is set to TA, then the blank time TD between the ECG R wave and the magnetization preparation module can be calculated as: TD = 0.75 * RR - tMP - TT - TA * 0.5. Here, 0.75 represents approximately 75% of the total cardiac cycle length during mid-diastole, and 0.5 is because the entire acquisition is linear, from a negative gradient to a positive gradient, so the center of K-space passes through 0 at the 50% position. After waiting for the blank time TD of the current cardiac cycle at the R wave moment of the current cardiac cycle, the magnetization preparation phase begins. The magnetization preparation module 401 applies the magnetization pulse signal of the current cardiac cycle. After the magnetization preparation time tMP of the current cardiac cycle is reached, the waiting phase begins. The waiting time module 402 recovers the magnetization pulse signal. After the waiting time TT of the current cardiac cycle is reached, the signal acquisition phase begins. The acquisition module 403 acquires the echo signal of the heart. The duration of the magnetization preparation phase, i.e. the duration of the magnetization preparation module 401, is the magnetization preparation time tMP. The duration of the waiting phase, i.e. the duration of the waiting time module 402, is the waiting time TT. The duration of the signal acquisition phase, i.e. the duration of the acquisition module 403, is the total acquisition time TA.

[0080] Step S330: Based on the magnetization preparation pulse set according to the requirements, set the magnetization preparation for the modules to be acquired before each cardiac cycle.

[0081] Through the user interface, the magnetization preparation module component is provided to the user via a drop-down menu, allowing them to select which type of magnetization preparation pulse to apply. The module to be acquired before each cardiac cycle refers to the aforementioned magnetization preparation module, which can be set to T1rho, T2prepare, IR, SR, etc. These settings can be edited, and the timing can be adjusted accordingly.

[0082] Step S340: Set whether the acquisition module needs to collect data for each cardiac cycle.

[0083] You can set whether the acquisition module needs to collect data for each cardiac cycle through the interface. When selected as the acquisition module, there will be a border prompt.

[0084] Step S350: Based on whether the acquisition module acquires and the number of magnetization preparation pulses, the blank time that needs to be set is obtained.

[0085] The blank time is equal to the start time of the magnetization preparation module. For example, if it is a flip-recovery module, the start point is the center point of the flip-recovery pulse, minus half of the acquisition module time. This blank time can be summarized into a list through the interface for easy user configuration. For example, if you select to open 3 magnetization preparation modules, you need to set 3 magnetization preparation pulses.

[0086] Step S360: Scan according to the set timing sequence.

[0087] Through interface interaction, the imaging sequence is scanned according to the time sequence set by the interface.

[0088] In some embodiments, the input / output device can display a parameter card of imaging sequence parameters, in which multiple sequence parameters can be set. For example... Figure 5 As shown, the parameter card includes a magnetization type selection box (MPType), a magnetization preparation time setting box (MPTime), and a magnetization / non-magnetization button (AOrN). AOrN is a selection button that determines whether a magnetization pulse signal is applied during the magnetization preparation period; MPType is a drop-down list that specifies the type of magnetization pulse signal; and MPTime is a free input box that allows setting the magnetization preparation time.

[0089] In some of these embodiments, such as Figure 6 As shown, the number of cardiac cycles, N=4, includes a first cardiac cycle, a second cardiac cycle, a third cardiac cycle, and a fourth cardiac cycle (the time interval between two R-wave pulses is one cardiac cycle). The type of magnetization pulse signal in the first cardiac cycle and the other cardiac cycles is set to be different via a drop-down list. Specifically, in the first cardiac cycle, a magnetization pulse signal is applied during the magnetization preparation period, and the type of magnetization pulse signal is IR pulse; signal acquisition occurs during the acquisition period. In the second cardiac cycle, no magnetization pulse signal is applied during the magnetization preparation period, and signal acquisition occurs during the acquisition period. In the third and fourth cardiac cycles, a magnetization pulse signal is applied during the magnetization preparation period, and the type of magnetization pulse signal is T2p pulse; signal acquisition occurs during the acquisition period. Through the above settings, a fingerprint acquisition sequence for cardiac imaging is formed.

[0090] This embodiment provides a cardiac magnetic resonance imaging (MRI) scan method, the method comprising:

[0091] The period T of the cardiac cycle of the electrocardiogram signal is acquired and the number N of cardiac cycles required to generate the imaging sequence is determined, and at least one cardiac cycle is divided into a magnetization preparation period, a waiting period and an acquisition period.

[0092] During the magnetization preparation period, you can set whether a magnetization pulse signal is applied and what type of magnetization pulse signal is used.

[0093] Set a signal acquisition time T1 for at least one cardiac cycle during the acquisition period;

[0094] During the cardiac cycle in which the magnetization pulse signal is applied, the magnetization preparation time T2 and the waiting time T3 are determined according to the type of magnetization pulse signal applied; the waiting time T3 is the time to wait for the magnetization pulse signal to recover.

[0095] The imaging sequence is generated based on the type of magnetization pulse signal applied, magnetization preparation time T2, waiting time T3, and signal acquisition time T1;

[0096] Execute the imaging sequence to generate cardiac magnetic resonance images.

[0097] In this embodiment, the cardiac magnetic resonance T1 mapping imaging sequence is configured to form a modified look-locker inversion recover (MOLLI) sequence, such as... Figure 7 As shown, Figure 7 The first row shows the ECG monitoring signal of the tested object changing over time, with one cardiac cycle occurring between two R-wave peaks. The second row is a timing diagram of the radiofrequency pulse signal of the MOLLI sequence, with the horizontal axis representing time and the vertical axis representing the flip angle. The third row is a schematic diagram of the magnetization vector changing over time after the application of the radiofrequency pulse. During the magnetization preparation period within the first cardiac cycle, a magnetization pulse signal is applied, which is an IR pulse (180°), followed by an excitation pulse (35°) for signal acquisition. The excitation pulse (35°) is applied during the second and third cardiac cycles after the first cardiac cycle for signal acquisition. After three waiting cardiac cycles following the third cardiac cycle, the second magnetization pulse signal is executed, and the process is similar.

[0098] In some of these embodiments, the shMOLLI sequence (Shortened Modified Look-Locker Inversion recovery) can also be formed based on the timing of the magnetization preparation period, waiting period, and acquisition period within the cardiac cycle.

[0099] This embodiment also provides a cardiac magnetic resonance imaging sequence generation device, which is used to implement the above embodiments and preferred embodiments, and will not be repeated as described previously. The terms "module," "unit," "subunit," etc., used below can refer to a combination of software and / or hardware that performs a predetermined function. Although the device described in the following embodiments is preferably implemented in software, hardware implementation, or a combination of software and hardware, is also possible and contemplated.

[0100] Figure 8 This is a structural block diagram of a cardiac magnetic resonance imaging sequence generation device according to this embodiment, as shown below. Figure 8 As shown, the device includes:

[0101] The acquisition module 510 is used to acquire the period T of the cardiac cycle of the electrocardiogram signal and determine the number N of cardiac cycles required to generate the imaging sequence;

[0102] The setting module 520 is used to set whether magnetization pulse signals are applied within N cardiac cycles, the type of application, and the signal acquisition time T1 for each cardiac cycle.

[0103] The first determining module 530 is used to determine the magnetization preparation time T2 and the waiting time T3 according to the type of magnetization pulse signal applied during the cardiac cycle in which the magnetization pulse signal is applied; the waiting time T3 is the time to wait for the magnetization pulse signal to recover.

[0104] The second determining module 540 is used to generate an imaging sequence based on the type of magnetization pulse signal applied, magnetization preparation time T2, waiting time T3, and signal acquisition time T1 for each cardiac cycle.

[0105] It should be noted that the above modules can be functional modules or program modules, and can be implemented through software or hardware. For modules implemented through hardware, the above modules can reside in the same processor; or the above modules can be located in different processors in any combination.

[0106] This embodiment also provides an electronic device including a memory and a processor, the memory storing a computer program and the processor being configured to run the computer program to perform the steps in any of the above method embodiments.

[0107] Optionally, the electronic device may further include a transmission device and an input / output device, wherein the transmission device is connected to the processor and the input / output device is connected to the processor.

[0108] Optionally, in this embodiment, the processor can be configured to perform the following steps via a computer program:

[0109] S1, acquire the period T of the cardiac cycle of the electrocardiogram signal and determine the number N of cardiac cycles required to generate the imaging sequence;

[0110] S2, set whether magnetization pulse signals are applied within N cardiac cycles, the type of application, and the signal acquisition time T1 for each cardiac cycle;

[0111] S3, During the cardiac cycle in which the magnetization pulse signal is applied, the magnetization preparation time T2 and the waiting time T3 are determined according to the type of magnetization pulse signal applied; the waiting time T3 is the time to wait for the magnetization pulse signal to recover.

[0112] S4. An imaging sequence is generated based on the type of magnetization pulse signal applied, magnetization preparation time T2, waiting time T3, and signal acquisition time T1 for each cardiac cycle.

[0113] It should be noted that the specific examples in this embodiment can refer to the examples described in the above embodiments and optional implementations, and will not be repeated in this embodiment.

[0114] Furthermore, in conjunction with the cardiac magnetic resonance imaging sequence generation method provided in the above embodiments, this embodiment can also provide a storage medium for implementation. The storage medium stores a computer program; when executed by a processor, the computer program implements the steps of any of the cardiac magnetic resonance imaging sequence generation methods in the above embodiments.

[0115] It should be understood that the specific embodiments described herein are merely illustrative of the application and not intended to limit it. All other embodiments derived by those skilled in the art based on the embodiments provided in this application without inventive effort are within the scope of protection of this application.

[0116] Obviously, the accompanying drawings are merely some examples or embodiments of this application. Those skilled in the art can apply this application to other similar situations based on these drawings without any creative effort. Furthermore, it is understood that although the work done in this development process may be complex and lengthy, for those skilled in the art, certain design, manufacturing, or production modifications made based on the technical content disclosed in this application are merely conventional technical means and should not be considered as insufficient disclosure of this application.

[0117] The term "embodiment" in this application refers to a specific feature, structure, or characteristic described in connection with an embodiment that may be included in at least one embodiment of this application. The appearance of this phrase in various places in the specification does not necessarily imply the same embodiment, nor does it imply that it is mutually exclusive with or independent of other embodiments. It will be clearly or implicitly understood by those skilled in the art that the embodiments described in this application may be combined with other embodiments without conflict.

[0118] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of patent protection. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the appended claims.

Claims

1. A method for generating cardiac magnetic resonance imaging sequences, characterized in that, The method includes: The period T of the cardiac cycle of the electrocardiogram signal is acquired, and the number N of cardiac cycles required to generate the imaging sequence is determined. Set whether to apply magnetization pulse signals within N cardiac cycles, the type of application, and the signal acquisition time T1 for each cardiac cycle; During the cardiac cycle in which the magnetization pulse signal is applied, the magnetization preparation time T2 and the waiting time T3 are determined according to the type of magnetization pulse signal applied; the waiting time T3 is the time to wait for the magnetization pulse signal to recover. The imaging sequence is generated based on the type of magnetization pulse signal applied, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1 for each cardiac cycle.

2. The method for generating cardiac magnetic resonance imaging sequences according to claim 1, characterized in that, The process of generating the imaging sequence based on the type of magnetization pulse signal applied, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1 for each cardiac cycle includes: During the cardiac cycle in which the magnetization pulse signal is applied, a blank time T4 is generated based on the magnetization preparation time T2, the waiting time T3, the signal acquisition time T1, and the period T of the cardiac cycle. A first sequence is generated based on the type of magnetization pulse signal applied, the blank time T4, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1; During a cardiac cycle in which no magnetization pulse signal is applied, a second sequence is generated based on the signal acquisition time T1; The imaging sequence is generated based on the first sequence and the second sequence.

3. The method for generating cardiac magnetic resonance imaging sequences according to claim 2, characterized in that, The step of generating a blank time T4 within the cardiac cycle during which the magnetization pulse signal is applied, based on the magnetization preparation time T2, the waiting time T3, the signal acquisition time T1, and the period T of the cardiac cycle, includes: The blank time T4 is calculated based on the magnetization preparation time T2, the waiting time T3, the signal acquisition time T1, the signal acquisition parameter β, the cardiac cycle period T, and the cardiac diastolic parameter α.

4. The method for generating cardiac magnetic resonance imaging sequences according to claim 2 or 3, characterized in that, The first sequence is generated based on the type of magnetization pulse signal applied, the blank time T4, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1, including: After waiting for the blank time T4 of the current cardiac cycle at the first moment of the current cardiac cycle, the magnetization preparation stage is entered and the magnetization pulse signal of the current cardiac cycle is applied; the first moment is determined according to the cardiac diastolic parameter α and the period T of the cardiac cycle; After reaching the magnetization preparation time T2 of the current cardiac cycle, the system enters a waiting phase and the magnetization pulse signal is restored. After the waiting time T3 of the current cardiac cycle is reached, the signal acquisition stage begins and the echo signal of the heart is acquired. The duration of the magnetization preparation phase is the magnetization preparation time T2, the duration of the waiting phase is the waiting time T3, and the duration of the signal acquisition phase is the acquisition time T1.

5. The method for generating cardiac magnetic resonance imaging sequences according to claim 1, characterized in that, Based on the evolution fitting function of the acquired signal, the number N of cardiac cycles required to generate the imaging sequence is determined, and the magnetization pulse signal of each cardiac cycle is different.

6. The method for generating cardiac magnetic resonance imaging sequences according to claim 1, characterized in that, The magnetization pulse signals are: longitudinal relaxation pulse signals, transverse relaxation pulse signals, inversion recovery pulse signals, and saturation recovery pulse signals.

7. A method for cardiac magnetic resonance scanning, characterized in that, The method includes: The period T of the cardiac cycle of the electrocardiogram signal is acquired and the number N of cardiac cycles required to generate the imaging sequence is determined, and at least one of the cardiac cycles is divided into a magnetization preparation period, a waiting period and an acquisition period. During the magnetization preparation period, the application of a magnetization pulse signal and the type of the magnetization pulse signal are specified. A signal acquisition time T1 for at least one cardiac cycle is set during the acquisition period; During the cardiac cycle in which the magnetization pulse signal is applied, the magnetization preparation time T2 and the waiting time T3 of the waiting period are determined according to the type of magnetization pulse signal applied; the waiting time T3 is the time to wait for the magnetization pulse signal to recover. The imaging sequence is generated based on the type of magnetization pulse signal applied, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1; The imaging sequence is executed to generate cardiac magnetic resonance images.

8. The cardiac magnetic resonance scanning method according to claim 7, characterized in that, The N cardiac cycles include a first cardiac cycle and a second cardiac cycle, and the types of magnetization pulse signals within the first cardiac cycle and the second cardiac cycle are set by a drop-down list.

9. The cardiac magnetic resonance scanning method according to claim 7, characterized in that, During the data acquisition period, select whether to perform signal acquisition by using the selection button.

10. A cardiac magnetic resonance imaging sequence generation device, characterized in that, include: The acquisition module is used to acquire the period T of the cardiac cycle of the electrocardiogram signal and determine the number N of cardiac cycles required to generate the imaging sequence; The setting module is used to set whether a magnetization pulse signal is applied within N cardiac cycles, the type of application, and the signal acquisition time T1 for each cardiac cycle; The first determining module is used to determine the magnetization preparation time T2 and the waiting time T3 according to the type of magnetization pulse signal applied during the cardiac cycle in which the magnetization pulse signal is applied; the waiting time T3 is the time to wait for the magnetization pulse signal to recover. The second determining module is used to generate the imaging sequence based on the type of magnetization pulse signal applied, the magnetization preparation time T2, the waiting time T3, and the signal acquisition time T1 of each cardiac cycle.

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