Magnetic resonance T1 quantification imaging method and apparatus

Abstract

The application discloses a magnetic resonance T1 quantitative imaging method and device, and relates to the technical field of magnetic resonance imaging. The application adds a blood flow signal module before reading out a gradient echo sequence each time, so that the image obtained by collection has a blood flow signal suppression effect, and since the gradient echo sequence is used for reading out, the influence of radio frequency field inhomogeneity is reduced. However, the use of the blood flow signal module also causes signal recovery to be not a simple exponential recovery relationship. In order to ensure the accuracy of T1 value measurement, a signal model of sequence imaging signal evolution is derived, accurate T1 quantitative values are obtained through calculation of the signal model, deviation caused by a direct simple exponential signal recovery curve fitting method is avoided, and therefore the accuracy of T1 quantitative imaging results can be improved.

Description

Technical Field

[0001] This invention relates to the field of magnetic resonance imaging technology, and in particular to a method and device for quantitative T1 magnetic resonance imaging. Background Technology

[0002] Studies have shown that the longitudinal relaxation time (T1) value in magnetic resonance imaging (MRI) can reflect physiological and pathological changes in tissues, laying the theoretical foundation for assessing plaque stability without contrast agents. Under various pathological conditions, the T1 value of biological tissues changes due to increased water content or alterations in the local molecular environment. Therefore, magnetic resonance imaging techniques for quantitatively measuring T1 time have been proposed and applied to the quantitative assessment of tissue pathological changes.

[0003] To perform T1 quantitative magnetic resonance imaging (MRI), multiple images with different inversion recovery times are typically acquired. Then, the T1 value of the tissue is fitted based on the exponential law of signal inversion recovery. Currently, most MRI T1 quantitative imaging techniques, in order to obtain relatively accurate T1 quantitative results, do not apply any preparation pulse after the inversion recovery pulse to avoid interference with signal recovery and inaccurate T1 quantification. Therefore, most MRI T1 quantitative imaging techniques, including the currently popular MP2RAGE, gradient echo sequences with varying inversion angles, and inversion recovery sequences, simultaneously quantify blood flow and static tissue. However, due to the influence of high blood flow signals, plaques on the vessel wall are not clearly observed, and the boundary between thrombi and blood within the vessel is lacking. This makes it difficult for traditional MRI T1 quantitative imaging results to accurately quantify vascular plaques and vascular thrombi.

[0004] To address this issue, two magnetic resonance T1 quantitative imaging techniques capable of suppressing blood flow signals have been proposed in recent years. One is the GOAL-SNAP technique proposed by Qi et al. This technique uses radial sampling trajectories and sliding window techniques to capture images at the zero-crossing point of blood flow recovery, thereby suppressing blood signals. However, this technique uses the principle of flip recovery to suppress blood flow signals, i.e., by capturing images at the zero-crossing point of blood flow recovery through radial sampling trajectories and sliding window techniques, it will suppress the signals of thrombi or plaques with T1 values ​​similar to blood. Therefore, it can only be used to measure hemorrhagic plaques with T1 values ​​much smaller than blood. Another technique is MSDE-bSSFP, which combines flow-sensitive astigmatism and equilibrium steady-state free precession sequences to achieve quantitative T1 imaging of the heart under blood flow signal suppression conditions. However, due to the introduction of pre-pulse technology in flow-sensitive astigmatism, this technique introduces T2 weights into the signal and has high requirements for field inhomogeneity. Furthermore, this technique still uses the traditional exponential recovery curve fitting method to calculate T1, so the quantitative T1 results of this technique have certain deviations. Summary of the Invention

[0005] To address the aforementioned problems in the existing technology, the present invention provides a magnetic resonance T1 quantitative imaging method and device.

[0006] To achieve the above objectives, the present invention provides the following solution:

[0007] A magnetic resonance T1 quantitative imaging method, comprising:

[0008] Imaging data acquisition is performed using scrambled gradient echo, and a blood flow signal module is added before each readout of the scrambled gradient echo sequence; the blood flow signal module consists of multiple radio frequency pulses and multiple astigmatic gradients.

[0009] Construct a signal model;

[0010] The signal model is used to construct a T1 lookup table based on the acquired imaging data;

[0011] The T1 relaxation value of the tissue to be imaged is determined using the difference method based on the T1 lookup table to obtain the T1 quantitative imaging result.

[0012] Optionally, perturbed gradient echo is used for imaging data acquisition, and a blood flow signal module is added before each perturbed gradient echo sequence readout, specifically including:

[0013] A 180° inversion pulse is used to reverse all the spins of the tissue to be imaged to the negative direction, and each spin is recovered according to its own inherent T1 relaxation time.

[0014] During the inversion recovery time, the imaging sequence was acquired using perturbed gradient echo. A blood flow signal module was added before each perturbed gradient echo sequence readout, and k-space data was acquired starting from the center line of k-space to obtain imaging data.

[0015] Optionally, when the acquired imaging data consists of two images with different inversion recovery times, the signal model construction process includes:

[0016] Based on the signal evolution pattern of the imaging sequence, the signal evolution of the imaging sequence is divided into three different periods;

[0017] Determine the longitudinal magnetization of tissues at different time periods;

[0018] Considering the conditions for steady-state sequence, a comprehensive equation is constructed based on the longitudinal magnetization of tissues at different time stages;

[0019] Solving the synthetic equation yields the steady-state solution;

[0020] Based on the steady-state solution, determine the signals corresponding to the two reversal times;

[0021] The signal model is constructed based on the signals corresponding to the two inversion times.

[0022] Optionally, the signal model is:

[0023]

[0024] In the formula, S UNI Indicates the output signal result. S represents the complex conjugate of SINV1, real(·) represents returning the real part of the function, and S INV1 S represents the signal corresponding to the first inversion time. INV2 This indicates the signal corresponding to the second inversion time.

[0025] According to specific embodiments provided by the present invention, the present invention discloses the following technical effects:

[0026] The magnetic resonance T1 quantitative imaging method provided by this invention adds a blood flow signal module before each gradient echo sequence readout, thereby giving the acquired image a blood flow signal suppression effect. Furthermore, the use of gradient echo sequences for readout reduces the influence of radio frequency field inhomogeneities. However, the use of the blood flow signal module means that signal recovery is not a simple exponential recovery relationship. To ensure the accuracy of T1 value measurement, a signal model of the sequence imaging signal evolution is derived. Accurate T1 quantitative values ​​are obtained by calculating this signal model, avoiding the bias caused by directly fitting a simple exponential signal recovery curve, thus improving the accuracy of T1 quantitative imaging results.

[0027] The present invention also provides a magnetic resonance T1 quantitative imaging device, the system comprising:

[0028] An image acquisition unit used for acquiring imaging data using phase-scrambled gradient echoes;

[0029] Memory, used to store computer programs;

[0030] The processor, connected to the image acquisition unit and the memory respectively, is used to retrieve and execute the computer program based on the acquired imaging data to implement the magnetic resonance T1 quantitative imaging method provided above.

[0031] Optionally, the image acquisition device includes at least two acquisition modules, and a blood flow signal module is provided in front of each acquisition module; the blood flow signal module consists of multiple radio frequency pulses and multiple astigmatic gradients.

[0032] Optionally, the processor includes:

[0033] Model building unit, used to build signal models;

[0034] The T1 lookup table construction unit is used to construct a T1 lookup table based on the acquired imaging data using the signal model.

[0035] The T1 quantitative imaging result determination unit is used to determine the T1 relaxation value of the tissue to be imaged based on the T1 lookup table using the difference method, so as to obtain the T1 quantitative imaging result.

[0036] Optionally, the memory is a computer-readable storage medium.

[0037] Since the technical effects achieved by the device provided by the present invention are the same as those achieved by the magnetic resonance T1 quantitative imaging method provided above, they will not be described again here. Attached Figure Description

[0038] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0039] Figure 1 A flowchart of the magnetic resonance T1 quantitative imaging method provided by the present invention;

[0040] Figure 2 This is a design diagram of the imaging sequence provided by the present invention;

[0041] Figure 3 The results of the water model experiment are as follows; among which, Figure 3 Image 'a' represents the T1 quantitative imaging result obtained using existing methods. Figure 3 b is the T1 quantitative imaging result image provided by the present invention. Figure 3 c represents the T1 value result graph provided by this invention;

[0042] Figure 4 This invention provides an imaging result image of a healthy volunteer; wherein, Figure 4 (a) is the imaging result of the second set of images using the existing method. Figure 4 (b) is the imaging result of the second set of images according to the method of the present invention. Figure 4 (c) is the imaging result of T1 quantitative images using existing methods. Figure 4 (d) is the imaging result of the T1 quantitative image of the method of the present invention. Detailed Implementation

[0043] 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 some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0044] The purpose of this invention is to provide a magnetic resonance T1 quantitative imaging method and device that can improve the accuracy of T1 quantitative imaging results.

[0045] To make the above-mentioned objects, features and advantages of the present invention more apparent and understandable, the present invention will be further described in detail below with reference to the accompanying drawings and specific embodiments.

[0046] like Figure 1 As shown, the magnetic resonance T1 quantitative imaging method provided by the present invention includes:

[0047] Step 100: Imaging data acquisition is performed using scrambled gradient echo, and a blood flow signal module is added before each readout of the scrambled gradient echo sequence. The blood flow signal module consists of multiple radio frequency pulses and multiple astigmatic gradients.

[0048] In this step, the imaging techniques used are as follows: Figure 2 As shown, a 180° non-selective inversion pulse is applied at the beginning, inverting all spins of the tissue to the negative direction. Each spin recovers according to its inherent T1 relaxation time. Imaging data is acquired using perturbed gradient echoes at two appropriate inversion recovery times TI (TI1 and TI2). An N-type pulse is added before each acquisition module. D The blood flow signal module consists of a radio frequency pulse and a phase gradient G, and the k-space data is collected starting from the center line of the k-space, thereby achieving the purpose of blood flow signal suppression.

[0049] Step 101: Construct the signal model.

[0050] To facilitate the derivation of the signal evolution model, the signal evolution is divided into three different periods based on the evolution law of sequence signals during the construction of the signal model:

[0051] ① First period: In the period without radio frequency pulses, since data acquisition is performed using scrambled gradient echoes, it is assumed that the transverse component is completely dephased, and the longitudinal magnetization vector can freely relax towards the equilibrium direction, as follows:

[0052]

[0053] In the formula, M z,0rf (·) represents the longitudinal magnetization vector before the start of the radio frequency pulse, Mz,ini M0 is the longitudinal magnetization vector at the start of the acquisition module, T1 is the longitudinal relaxation time of the tissue, and t is the time parameter.

[0054] ② Second period: In the case of N M In a GRE module with a constant gradient echo sequence and a flip angle α, the pulse interval between two adjacent gradient echo RF pulses is t. M The evolution expression of longitudinal magnetization is as follows:

[0055]

[0056] In the formula, It is the longitudinal magnetization vector after experiencing the nth gradient echo radio frequency pulse.

[0057] ③ The third period: in the period with N D In a blood flow signal module with a constant flip angle α, the pulse interval is t. D To simplify the signal model, this invention uses a more intuitive approximate signal expression. Ignoring blood flow velocity, after suppression by the blood flow signal module, the longitudinal magnetization of the tissue can be expressed as:

[0058]

[0059] In the formula, The longitudinal magnetization vector is the result of the radiofrequency pulse received by the nth blood flow signal module, and T1 and T2 are the longitudinal and transverse relaxation times of the tissue, respectively. M is the longitudinal magnetization vector of the blood flow signal module in steady state. z,ss For longitudinal magnetization before reversal, For static or flowing spin from the initial longitudinal magnetization vector, M z,ini M is transitioning to a steady state z,ss The rate.

[0060] Consider the condition for steady-state sequence: the longitudinal magnetization M before each reversal z,ss They are the same. Between two adjacent inverted pulses, M z,ss First, after experiencing a reversal pulse, it enters the signal recovery period (TA), and then experiences the first blood flow signal module (i.e. Figure 2 The blood flow signal suppression module 1 and the acquisition module (i.e.) Figure 2 The perturbation gradient echo acquisition module 1 enters the free recovery phase TB, and passes through the second blood flow signal module (i.e., Figure 2 The blood flow signal suppression module 2) and the acquisition module (i.e. Figure 2After the disturbance phase gradient echo acquisition module 2), it enters the free recovery period TC, and at the end, it recovers to the initial value. Combining formulas [1]-[3], the following comprehensive equation can be obtained:

[0061]

[0062] In the formula, TA, TB, and TC are... Figure 2 The delay time described in the text, α 1M For time interval t M The first constant flip angle during the time interval, α D For time interval t D The constant flip angle α during the time interval 2M For time interval t M The second constant flip angle during the time interval.

[0063] Solve for M in formula [4] z,ss The following steady-state solution can be obtained:

[0064]

[0065] In the formula, E 1M =exp(-t) M / T1), E 1D =exp(-t) D / T1), E 2D =exp(-t) D / T2). M Z (0) - and M Z (0) + These are the longitudinal magnetizations before and after the application of the pulse, respectively. Let the reversal efficiency of the adiabatic pulse be eff = 1 / 2(1-M). Z (0) + / M Z (0) - ).

[0066] Knowing the steady-state condition, the signal S corresponding to the two inversion times of this sequence is... INV1 and S INV2 They can be represented as follows:

[0067]

[0068]

[0069] The signals obtained at the two inversion times TI1 and TI2 are combined in the following way to obtain the signal model:

[0070]

[0071] Among them, S UNI Indicates the output signal result. Represents the complex conjugate of SINV1, and real(·) returns the real part of the function. Formula [8] can restrict all possible values ​​of the sequence signal to between -0.5 and 0.5, thus forming a predetermined image intensity range. It can be used to numerically invert the signal model within the T1 relaxation range of interest, and the combined expression has only one singular point (i.e., S). INV1 =S UNI =0), even when approaching this singularity, its value is still in the range of -0.5 to 0.5, which facilitates the selection of the dynamic range of the displayed image. Moreover, by combining the two time-reversed images in the manner of [8], M0, B0, B1 are eliminated. - T2 * The influence of proton weighting. Where M0 is the magnetization vector at equilibrium, B0 is the static magnetic field strength, and B1... - T2 represents the radio frequency field strength. * The transverse decay time is affected by magnetic field inhomogeneity.

[0072] Step 102: Construct a T1 lookup table based on the acquired imaging data using a signal model.

[0073] Step 103: Use the difference method based on the T1 lookup table to determine the T1 relaxation value of the tissue to be imaged, so as to obtain the T1 quantitative imaging results.

[0074] Steps 102 and 103 can effectively avoid the inherent T2 attenuation of the blood flow signal module and obtain a more accurate T1 calculation result.

[0075] The method described above was verified on a water model and healthy volunteers, and the results confirmed its feasibility.

[0076] (1) Water phantom experiment: Imaging was performed using the T1 standard phantom (T1MES, ResonanceHealth, Australia) manufactured by Resonance Health, Australia (e.g., Figure 3 As shown, this phantom contains no flowing liquid and is primarily used to evaluate the accuracy of the T1 value measurement in this invention. Imaging was performed on a Siemens 3.0T MRI system (SIEMINS, Prism), with detailed scanning parameters as follows: Echo Time (TE) of 2.77 ms and Field of View (FOV) of 199 × 199 mm. 2The matrix is ​​192×192. The resolution is 1.04mm, isotropic. The number of phase encoding steps is 192. The receiver bandwidth is 320Hz / pixel. The layer thickness is 1.25mm. D ≈1ms. G=18mT / m. t M = 6.4ms.

[0077] The results show that the T1 quantitative imaging results of the present invention are in very high agreement with existing methods, confirming that the T1 values ​​obtained by fitting the derived signal model after applying the blood flow signal module are highly accurate.

[0078] (2) Healthy Volunteer Experiment: The brains of volunteers were scanned using DANTE-MP2RAGE sequences with different acquisition parameters. Traditional MP2RAGE sequence scans were also performed under the same imaging settings as a reference for the DANTE-MP2RAGE sequences. The imaging results are as follows: Figure 4 As shown. The detailed scanning parameters used are: TE = 2.65ms, FOV = 225 × 240mm. 2 Matrix = 180 × 192. Resolution = 1.25 mm, isotropic. Number of Phase Encoding Steps = 180. Receiver Bandwidth = 320 Hz / pixel. Thickness = 1.25 mm. D ≈1ms. G=18mT / m. t M =6.7ms.

[0079] Based on Table 1 and Figure 4 The results show that the present invention can effectively suppress blood flow signals and obtain accurate quantitative results of T1 values.

[0080] Table 1. Quantitative results of T1 in white and gray matter of healthy volunteers without flowing blood vessels.

[0081]

[0082] Based on the above description, this invention adds a blood flow signal module before each gradient echo sequence readout, thereby enabling the acquired image to have a blood flow signal suppression effect. Furthermore, by using a gradient echo sequence for readout, the influence of B1 field inhomogeneity is reduced. A signal model is derived, and accurate T1 quantitative values ​​are obtained through calculations based on this model, avoiding the biases caused by directly using a simple exponential signal recovery curve fitting method. In application, this enables T1 quantitative imaging of vascular plaques and thrombi.

[0083] The present invention also provides a magnetic resonance T1 quantitative imaging device, the system comprising:

[0084] An image acquisition unit used for acquiring imaging data using phase-scratched gradient echoes.

[0085] Memory is used to store computer programs.

[0086] The processor, connected to the image acquisition unit and the memory respectively, is used to retrieve and execute computer programs based on the acquired imaging data to implement the magnetic resonance T1 quantitative imaging method provided above.

[0087] Furthermore, the image acquisition device used in this invention includes at least two acquisition modules, and a blood flow signal module is provided in front of each acquisition module. The blood flow signal module consists of multiple radio frequency pulses and multiple astigmatic gradients.

[0088] Furthermore, the processors used above include:

[0089] Model building unit, used to build signal models.

[0090] The T1 lookup table construction unit is used to construct a T1 lookup table based on the acquired imaging data using a signal model.

[0091] The T1 quantitative imaging result determination unit is used to determine the T1 relaxation value of the tissue to be imaged based on the T1 lookup table using the difference method, so as to obtain the T1 quantitative imaging result.

[0092] Furthermore, when the computer program in the aforementioned memory 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, the technical solution of the present invention, in essence, or the part that contributes to the prior art, or a part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to cause a computer device (which may be a personal computer, server, or network device, etc.) to execute all or part of the steps of the methods of the various embodiments of the present invention. The aforementioned storage medium includes various media capable of storing program code, such as USB flash drives, portable hard drives, read-only memory, random access memory, magnetic disks, or optical disks.

[0093] Based on the above description, compared with the prior art, the present invention also has the following advantages:

[0094] 1) In this invention, a blood flow signal module is added before each gradient echo sequence module, and the acquisition module adopts a k-space center priority acquisition method, so that each acquired image has a blood flow signal suppression effect.

[0095] 2) This invention uses the constructed signal model to create a T1 lookup table, and then uses interpolation to accurately calculate the T1 value of the tissue.

[0096] 3) This invention uses perturbed gradient echo for data acquisition, which allows the lateral component to be assumed to be completely dephased during model derivation, simplifying the model formula.

[0097] 4) A more intuitive approximate signal expression is used to express the signal suppression process in the blood flow signal module, thereby further simplifying the derivation of the signal pattern.

[0098] The various embodiments in this specification are described in a progressive manner, with each embodiment focusing on its differences from other embodiments. Similar or identical parts between embodiments can be referred to interchangeably. For the devices disclosed in the embodiments, since they correspond to the methods disclosed in the embodiments, the description is relatively simple; relevant parts can be referred to the method section.

[0099] This document uses specific examples to illustrate the principles and implementation methods of the present invention. The descriptions of the above embodiments are only for the purpose of helping to understand the method and core ideas of the present invention. Furthermore, those skilled in the art will recognize that, based on the ideas of the present invention, there will be changes in the specific implementation methods and application scope. Therefore, the content of this specification should not be construed as a limitation of the present invention.

Claims

1. A method for quantitative T1 magnetic resonance imaging, characterized in that, include: Imaging data acquisition was performed using scrambled gradient echo, and a blood flow signal module was added before each readout of the scrambled gradient echo sequence. The blood flow signal module consists of multiple radio frequency pulses and multiple astigmatic gradients; Construct a signal model; The signal model is used to construct a T1 lookup table based on the acquired imaging data; The T1 relaxation value of the tissue to be imaged is determined based on the T1 lookup table using interpolation to obtain T1 quantitative imaging results; In constructing the signal model, based on the evolution law of sequence signals, the signal evolution is divided into three different periods: ① First period: During the period without radio frequency pulses, since data acquisition is performed using scrambled gradient echoes, it is assumed that the transverse component is completely dephased, and the longitudinal magnetization vector relaxes freely towards the equilibrium direction, resulting in: [1] In the formula, This is the longitudinal magnetization vector before the start of the radio frequency pulse. This is the longitudinal magnetization vector at the start of the acquisition module. The magnetization vector in equilibrium state. For the organization's longitudinal relaxation time, t For time parameters; ②Second period: in the presence of N M Flip angle of a constant gradient echo sequence α In the GRE module, the pulse interval between two adjacent gradient echo RF pulses is t M The evolution expression of longitudinal magnetization is as follows: [2] In the formula, The longitudinal magnetization vector after experiencing the nth gradient echo radio frequency pulse; ③The third period: in the presence of N D A constant flip angle α In the blood flow signal module, the pulse interval is t D Ignoring blood flow velocity, after suppression by the blood flow signal module, the longitudinal magnetization of the tissue is represented as follows: [3] In the formula, T1 represents the longitudinal magnetization vector after experiencing the radiofrequency pulse of the nth blood flow signal module, and T2 represents the transverse relaxation time of the tissue. This represents the longitudinal magnetization vector of the blood flow signal module in steady state. For longitudinal magnetization before reversal, For static or flowing spin from the initial longitudinal magnetization vector, To transition to a steady state The rate; Consider the condition for steady-state sequence: longitudinal magnetization before each reversal They are the same; between two adjacent inverted pulses, First, after experiencing a reversal pulse, it enters the signal recovery period TA, then passes through the first blood flow signal module and acquisition module, and enters the free recovery period TB. After passing through the second blood flow signal module and acquisition module, it enters the free recovery period TC, and at the end, it returns to the initial value; combining formulas [1]-[3], the comprehensive equation is obtained as follows: [4] In the formula, Time interval t M The first constant flip angle during the time interval, Time interval t D A constant flip angle during the time interval, Time interval t M The second constant flip angle in the time interval; Solve the equation [4] The following steady-state solution is obtained: [5] In the formula, , , ; and These are the longitudinal magnetizations before and after the application of the pulse, respectively. Let the reversal efficiency of the adiabatic pulse be... ; Knowing the steady-state condition, the signals corresponding to the two inversion times of the sequence S INV1 and S INV2 They are represented as follows: [6] [7] The signal model obtained by combining the two signals corresponding to the inversion times in the following manner is as follows: [8] In the formula, Indicates the output signal result. Indicates signal S INV1 The complex conjugate, This indicates that the function returns the real part of the function.

2. The magnetic resonance T1 quantitative imaging method according to claim 1, characterized in that, Imaging data acquisition is performed using phase-scrambled gradient echo, and a blood flow signal module is added before each readout of the phase-scrambled gradient echo sequence. Specifically, this includes: A 180° inversion pulse is used to reverse all the spins of the tissue to be imaged to the negative direction, and each spin is recovered according to its own inherent T1 relaxation time. During the inversion recovery time, the imaging sequence was acquired using perturbed gradient echo. A blood flow signal module was added before each perturbed gradient echo sequence readout, and k-space data was acquired starting from the center line of k-space to obtain imaging data.

3. A magnetic resonance T1 quantitative imaging device, characterized in that, include: An image acquisition unit used for acquiring imaging data using phase-scrambled gradient echoes; Memory, used to store computer programs; The processor, connected to the image acquisition unit and the memory respectively, is used to retrieve and execute the computer program based on the acquired imaging data to implement the magnetic resonance T1 quantitative imaging method as described in any one of claims 1 and 2.

4. The magnetic resonance T1 quantitative imaging device according to claim 3, characterized in that, The image acquisition device includes at least two acquisition modules, and a blood flow signal module is provided in front of each acquisition module; the blood flow signal module consists of multiple radio frequency pulses and multiple astigmatic gradients.

5. The magnetic resonance T1 quantitative imaging device according to claim 4, characterized in that, The processor includes: Model building unit, used to build signal models; The T1 lookup table construction unit is used to construct a T1 lookup table based on the acquired imaging data using the signal model. The T1 quantitative imaging result determination unit is used to determine the T1 relaxation value of the tissue to be imaged based on the T1 lookup table using an interpolation method, so as to obtain the T1 quantitative imaging result.

6. The magnetic resonance T1 quantitative imaging device according to claim 4, characterized in that, The memory is a computer-readable storage medium.

Images