A multi-nuclear magnetic resonance method and device for evaluating blood flow-dependent energy metabolism

Abstract

The present invention discloses a multi-nuclear magnetic resonance method for evaluating blood flow-dependent energy metabolism, which collects the blood flow of the subject in the test area. 31 P chemical shift spectroscopy imaging data and 129 Xe chemical shift spectral imaging data; calculating the average chemical shift spectral image of creatine phosphate and the blood perfusion efficiency image of red blood cells; after stimulating the subject, obtaining the average chemical shift spectral image of creatine phosphate and the blood perfusion efficiency image of red blood cells in the test area of ​​the stimulated subject; calculating the blood flow-dependent energy metabolism parameter map of the test area of ​​the subject. The present invention also discloses a multi-nuclear magnetic resonance device for evaluating blood flow-dependent energy metabolism. The present invention combines 31 The response parameters of energy metabolism obtained by P magnetic resonance spectroscopy imaging 129 The blood perfusion response parameters obtained by Xe magnetic resonance spectroscopy were normalized to obtain blood flow-dependent energy metabolism changes.

Description

Technical Field

[0001] The present invention relates to the field of magnetic resonance spectroscopy technology, and in particular to a multi-nuclear magnetic resonance method for evaluating blood flow-dependent energy metabolism, and also to a multi-nuclear magnetic resonance device for evaluating blood flow-dependent energy metabolism, which is suitable for performing precise measurement of blood flow-related energy metabolism based on multi-nuclear magnetic resonance technology. Background Art

[0002] The brain's energy production mainly relies on the supply of glucose in the blood. When brain energy metabolism increases, local blood flow will increase and glucose consumption will increase. Testing these two can obtain information on brain energy metabolism. The current methods for monitoring brain energy metabolism mainly include magnetic resonance imaging and 18-Fluoro-deoxyglucose positron emission tomography (FDG-PET). MRI indirectly measures brain energy metabolism by detecting changes in cerebral blood flow. Active brain areas require more energy, so blood flow increases. This method is also called functional magnetic resonance imaging (fMRI). In addition, Magnetic Resonance Spectroscopy Imaging (MRSI) in MRI can evaluate brain energy metabolism by detecting the levels of metabolites such as lactate and creatine phosphate in the brain. However, 1 In clinical MRI / MRSI, where H is the signal source, images are interfered by strong tissue background signals. In addition, since both oxygen consumption and increased blood flow appear as signal enhancement in fMRI, it is difficult to decouple the two. FDG-PET can assess brain energy metabolism by measuring brain FDG uptake, but PET is radioactive and is difficult to use as a routine means of detecting brain energy in patients. Most importantly, none of the above methods can detect blood flow and metabolites simultaneously, both of which are affected by brain energy metabolism. Therefore, simultaneous measurement of brain energy metabolites and cerebral blood flow to achieve cerebral blood flow-dependent metabolite assessment is expected to achieve accurate assessment of brain energy metabolism.

[0003] Apart from 1 In addition to H, there are many other nuclei that can be used for magnetic resonance imaging, called multi-nuclear MRI. 31 P-MRSI can provide important information related to energy metabolism non-invasively. Various high-energy metabolites in the human body and phospholipids on cell membranes contain 31 P. 31 P-MRSI compared with 1 H-MRSI has a larger chemical shift range for metabolites ( 31P: 30 ppm, 1 H: 5 ppm), and there is no background signal interference, so compared with 1 H MRI can better detect energy metabolites. Among them, the basic high-energy metabolite phosphocreatine (PCr) is 31 The main signal in P-MRSI, PCr, is an immediately available energy reserve that can generate adenosine tri-phosphate (ATP) during consumption.

[0004] Hyperpolarization 129 Xe gas MRI is an imaging technology that has been rapidly promoted in clinical practice in recent years. 129 After Xe gas is inhaled into the lungs, it first enters the alveoli, then passes through the alveolar wall into the capillaries and dissolves in the blood (called dissolved state). 129 Xe) is transported throughout the body through the bloodstream. 129 Xe images have no background signal interference, so they naturally have the advantage of evaluating brain perfusion information and can effectively detect changes in cerebral blood flow related to brain energy metabolism.

[0005] In summary, combined 31 Advantages of energy metabolite detection of P 129 The advantage of Xe blood perfusion detection is that it can achieve simultaneous measurement of metabolites and blood flow changes, which is of great significance for obtaining changes in metabolites that are dependent on cerebral blood flow and accurately evaluating brain energy metabolism. Summary of the invention

[0006] The purpose of the present invention is to provide a multi-nuclear magnetic resonance method for evaluating blood flow dependence on energy metabolism and a multi-nuclear magnetic resonance device for evaluating blood flow dependence on energy metabolism in order to address the above-mentioned problems existing in the prior art.

[0007] The above-mentioned purpose of the present invention is achieved by the following technical means:

[0008] A multi-nuclear magnetic resonance method for assessing blood flow-dependent energy metabolism comprises the following steps:

[0009] Step 1: Collect the data of the test area of ​​n groups of subjects. 31 P chemical shift spectroscopy imaging data; collect n groups of subjects in the area to be tested 129 Xe chemical shift spectroscopy imaging data;

[0010] Step 2: Based on 31 P chemical shift spectroscopy imaging data and 129 Xe chemical shift spectroscopy imaging data is used to calculate the average chemical shift spectroscopy image of creatine phosphate and the blood perfusion efficiency image of red blood cells;

[0011] Step 3, after stimulating the subject, repeating steps 1 and 2 to obtain an average chemical shift spectrum image of creatine phosphate in the test area of ​​the stimulated subject and a blood perfusion efficiency image of red blood cells in the test area after stimulation;

[0012] Step 4: Calculate the blood flow-dependent energy metabolism parameter of the test area of ​​the subject based on the average chemical shift spectrum image of creatine phosphate before and after stimulation and the blood perfusion efficiency image. EN-RBC .

[0013] As mentioned in step 1 31 P chemical shift spectroscopy imaging data and 129 The acquisition of Xe chemical shift spectroscopy imaging data consists of the following steps:

[0014] Step 1.1. The subject lies prone on the MRI bed and is connected to 129 Xe gas delivery system;

[0015] Step 1.2: The subject passes 129 Xe Gas Delivery System for Sustained Breathing Hyperpolarization 129 A mixture of Xe gas and oxygen is used to 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequence scanning, obtain 31 P chemical shift spectroscopy imaging data and 129 Xe chemical shift spectroscopy imaging data.

[0016] As mentioned above in step 1.1, the subject wears 31 P synchronous transceiver RF coil and 129 Xe synchronous transceiver RF coil, 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coils partially overlap and are both located on the coil substrate. 129 Xe synchronous transceiver RF coil 31 P trap circuit, 129 Xe transmit receive switch 129 Xe signal filter connection, 129 Xe signal filters and 129 Xe preamplifier connections, 31 P synchronous transceiver RF coil 129 Xe trap circuit, 31 P transmit receive switch and 31 P signal filter connection, 31 P signal filter and 31 P Preamplifier connections.

[0017] As mentioned in step 1.2 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequences all include a periodic processing part, which includes a pre-damage part and a data acquisition part. In the pre-damage part, 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coil simultaneously emits a 90° pulse, and then immediately applies a damage gradient Gsp to the original area to be tested. 129 Xe magnetic resonance signal and 31 P MRI signal saturation, during the data acquisition section, 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequence was performed by 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coil simultaneously transmits 90° pulses and small angle pulses; after encoding gradient Genc, ​​they are respectively 31 P Magnetic resonance signals and 129 Acquisition of Xe magnetic resonance signals.

[0018] As mentioned above, the encoded gradient Genc = BW / (γ( 31 P)×FOV), BW is the sampling bandwidth, FOV is the imaging field of view, γ( 31 P) is 31 The gyromagnetic ratio of P.

[0019] As described above in steps 2 and 3, the average chemical shift spectrum image of creatine phosphate and the blood perfusion efficiency image are calculated based on the following steps:

[0020] Step 2.1: According to 31 Chemical shift spectroscopy imaging data P (i) with 129 Xe chemical shift spectroscopy imaging data S Xe (i) Obtain 31 P Chemical shift spectroscopy image I P (i) with 129 Xe chemical shift spectrum image I Xe (i) Then, through 31 P Chemical shift spectroscopy image I P (i) with 129 Xe chemical shift spectrum image I Xe The spectrum in each pixel of (i) is peak-fitted to obtain the chemical shift spectrum image I of creatine phosphate PCr (i) Chemical shift spectrum image of red blood cells I RBC(i), i = 1, 2,… n ,

[0021] Step 2.2: The chemical shift spectrum image of creatine phosphate PCr (i) averaging to obtain an average chemical shift spectrum image of creatine phosphate; and averaging the chemical shift spectrum image of red blood cells in the test area. RBC (i) Perform point-by-point fitting according to the following formula to obtain the blood perfusion efficiency V and the signal constant factor S0,

[0022] ,

[0023] Where TR is the repetition time of the data acquisition part, S(iTR) is I RBC (i) The pixel signal intensity, α is 129 The distribution of blood perfusion efficiency V obtained by fitting the flip angle of the small-angle pulse of the Xe synchronous chemical shift spectroscopy imaging sequence is the blood perfusion efficiency image.

[0024] As described above, the average chemical shift spectrum image of creatine phosphate before stimulation in step 4 and the blood perfusion efficiency image are respectively denoted as I PCr1 and I RBC_V1 The average chemical shift spectrum image of creatine phosphate and the blood perfusion efficiency image after stimulation are respectively denoted as I PCr2 and I RBC_V2 ,

[0025] In step 4, energy metabolism parameter diagram I EN-RBC = (I PCr2 -I PCr1 )×I RBC_V1’ / ((I RBC_V2’ -I RBC_V1’ ) ×I PCr1 ),

[0026] Among them, I RBC_V1’ To transform the blood perfusion efficiency image I of the area to be tested RBC_v1 Image clipping and interpolation are performed to the average chemical shift spectrum image I of creatine phosphate in the area to be measured PCr1 Images obtained with the same FOV and resolution; I RBC_V2’ The blood perfusion efficiency image I of the stimulated area to be tested is RBC_V2 The image is cut and interpolated to the average chemical shift spectrum image I of the creatine phosphate in the test area of ​​the stimulated subject. PCr2 Images obtained with the same FOV and resolution.

[0027] A multi-nuclear magnetic resonance apparatus for evaluating blood flow-dependent energy metabolism, comprising:

[0028] Chemical shift spectroscopy imaging module: used to utilize 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 The Xe synchronous chemical shift spectroscopy imaging sequence performs chemical shift spectroscopy imaging on the test area of ​​the subject to obtain the test area of ​​the subject before stimulation. 31 Chemical shift spectroscopy imaging data P (i) and the area to be tested 129 Xe chemical shift spectroscopy imaging data S Xe (i) We also obtained the subjects' 31 Chemical shift spectroscopy imaging data P (i) and the area to be tested 129 Xe chemical shift spectroscopy imaging data S Xe (i);

[0029] Spectral image calculation module: used to calculate the spectral image of the area to be tested before stimulation. 31 Chemical shift spectroscopy imaging data P (i) and the area to be tested 129 Xe chemical shift spectroscopy imaging data S Xe (i) Calculate the average chemical shift spectrum image I of creatine phosphate in the test area before stimulation PCr1 Blood perfusion efficiency image I of red blood cells in the area to be tested RBC_V1 ; Used to determine the area to be tested after stimulation 31 Chemical shift spectroscopy imaging data P (i) and the area to be tested 129 Xe chemical shift spectroscopy imaging data S Xe (i) Calculate the average chemical shift spectrum image I of creatine phosphate in the stimulated area to be tested PCr2 Blood perfusion efficiency image I of red blood cells in the area to be tested RBC_V2 ;

[0030] Energy metabolism parameter map calculation module: used to calculate the blood flow-dependent energy metabolism parameter map I of the subject's test area based on the average chemical shift spectrum image of creatine phosphate before and after stimulation and the blood perfusion efficiency image EN-RBC .

[0031] As mentioned above, in the spectrum image calculation module,

[0032] according to 31 Chemical shift spectroscopy imaging data P (i) with 129 Xe chemical shift spectroscopy imaging data S Xe (i) Obtain 31 P Chemical shift spectroscopy image I P(i) with 129 Xe chemical shift spectrum image I Xe (i) Then, through 31 P Chemical shift spectroscopy image I P (i) with 129 Xe chemical shift spectrum image I Xe The spectrum in each pixel of (i) is peak-fitted to obtain the chemical shift spectrum image I of creatine phosphate PCr (i) Chemical shift spectrum image of red blood cells I RBC (i), i = 1, 2, … n ,

[0033] The chemical shift spectrum image of creatine phosphate I PCr (i) averaging to obtain an average chemical shift spectrum image of creatine phosphate; and averaging the chemical shift spectrum image of red blood cells in the test area. RBC (i) Perform point-by-point fitting according to the following formula to obtain the blood perfusion efficiency V and the signal constant factor S0,

[0034] ,

[0035] Where TR is the repetition time of the data acquisition part, S(iTR) is I RBC (i) The pixel signal intensity, α is 129 The distribution of blood perfusion efficiency V obtained by fitting the flip angle of the small-angle pulse of the Xe synchronous chemical shift spectroscopy imaging sequence is the blood perfusion efficiency image.

[0036] In the energy metabolism parameter diagram calculation module as described above,

[0037] The average chemical shift spectrum image of creatine phosphate and the blood perfusion efficiency image before stimulation are respectively denoted as I PCr1 and I RBC_V1 The average chemical shift spectrum image of creatine phosphate and the blood perfusion efficiency image after stimulation are respectively denoted as I PCr2 and I RBC_V2 ,

[0038] Energy metabolism parameters Figure I EN-RBC = (I PCr2 -I PCr1 )×I RBC_V1’ / ((I RBC_V2’ -I RBC_V1’ ) ×I PCr1 ),

[0039] Among them, I RBC_V1’ To transform the blood perfusion efficiency image I of the area to be tested RBC_v1Image clipping and interpolation are performed to the average chemical shift spectrum image I of creatine phosphate in the area to be measured PCr1 Images obtained with the same FOV and resolution; I RBC_V2’ The blood perfusion efficiency image I of the stimulated area to be tested is RBC_V2 The image is cut and interpolated to the average chemical shift spectrum image I of the creatine phosphate in the test area of ​​the stimulated subject. PCr2 Images obtained with the same FOV and resolution.

[0040] Compared with the prior art, the present invention has the following characteristics:

[0041] 1. By design 31 P / 129 Xe synchronous transceiver RF coil, and related control circuit, to achieve 31 P / 129 Delay-free synchronous excitation and reception of Xe magnetic resonance signals.

[0042] 2. Combination 31 P and 129 Xe multi-core MRI signal characteristics, realized in one sequence 31 P and 129 Data acquisition of Xe magnetic resonance spectroscopy images.

[0043] 3. By 31 P Magnetic resonance spectroscopy imaging obtained energy metabolism response parameters 129 The blood perfusion response parameters obtained by Xe magnetic resonance spectroscopy were normalized to obtain blood flow-dependent energy metabolism changes. BRIEF DESCRIPTION OF THE DRAWINGS

[0044] Figure 1 It is a flow chart of the present invention.

[0045] Figure 2 Schematic diagram of the structure of the radio frequency coil used in step 1 of the present invention.

[0046] Figure 3 It is used in step 1 of the present invention 31 P / 129 Partial schematic diagram of the Xe synchronous transmit and receive RF coil circuit.

[0047] Figure 4 It is used in step 1 of the present invention 31 P / 129 Schematic diagram of the Xe synchronized chemical shift spectroscopy imaging sequence.

[0048] Figure 5 It is a schematic diagram of the calculation process of the average chemical shift spectrum image of creatine phosphate and the blood perfusion efficiency image in step 2 of the present invention.

[0049] Reference numerals and corresponding component names:

[0050] 101—coil integrated cable trough; 102— 31 P transmitting and receiving control board; 103- 129 Xe transmitting and receiving control board; 104 - coil substrate; 105 - 31 P synchronous transceiver radio frequency coil; 106- 129 Xe synchronous transmit and receive RF coil. DETAILED DESCRIPTION

[0051] In order to facilitate ordinary technicians in this field to understand and implement the present invention, the present invention is further described in detail below in conjunction with the embodiments taking magnetic resonance imaging of subjects as an example. The embodiments described here are only used to illustrate and explain the present invention, and are not intended to limit the present invention.

[0052] Embodiment 1:

[0053] like Figure 1 As shown, this embodiment provides a multi-nuclear magnetic resonance method for evaluating blood flow-dependent energy metabolism, comprising the following steps, wherein the area to be tested is the brain, but the method of this embodiment is not limited to the area to be tested being the brain, and may also be other areas to be tested of the subject, such as the lungs, heart, kidneys, etc.:

[0054] Step 1: Adopt 31 P synchronous transceiver RF coil and 31 P synchronized chemical shift spectroscopy imaging sequence, collecting brain images of n groups of subjects 31 Chemical shift spectroscopy imaging data P (i) Adoption 129 Xe synchronous transceiver RF coil and 129 Xe synchronous chemical shift spectroscopy imaging sequence, collecting brain images of n groups of subjects 129 Xe chemical shift spectroscopy imaging data S Xe (i), i = 1,2,…, n:

[0055] Step 1.1. The subject lies prone on the MRI bed and is connected to 129 Xe Gas Delivery System, Wearable 31 P synchronous transceiver RF coil and 129 Xe synchronous transceiver RF coil ( Figure 2 ). The subjects are animals or humans.

[0056] In this embodiment, 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coils partially overlap and are both located on the coil substrate 104. 129Xe synchronous transceiver RF coil 31 P trap circuit, 129 Xe transmit receive switch and 129 Xe signal filter connection, 129 Xe signal filters and 129 Xe preamplifier connections. 31 P synchronous transceiver RF coil 129 Xe trap circuit, 31 P transmit receive switch and 31 P signal filter connection, 31 P signal filter and 31 P Preamplifier connections.

[0057] 129 Xe transmit and receive switch, 129 Xe signal filter, 129 The Xe preamplifier is integrated in 129 On the Xe transmitting and receiving control board 103; 31 P Transmit and receive switch, 31 P signal filter, 31 The preamplifier is integrated in 31 P on the transmitting and receiving control board 102; 129 Xe transmission and reception control board 103 and 31 The P transmitting and receiving control board 102 is installed on a mounting base, and a coil integrated cable groove 101 is provided on the mounting base.

[0058] In addition to the conventional preamplifier and transmitting and receiving switch, the above circuit also 31 P and 129 Filters and notch circuits are set in the respective Xe links to avoid crosstalk caused by the RF signal of another nuclide during synchronous excitation and reception.

[0059] Step 1.2: The subject passes 129 Xe Gas Delivery System for Sustained Breathing Hyperpolarization 129 A mixture of Xe gas and oxygen is used to 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequence scanning, such as Figure 4 shown. 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 The radio frequency / data acquisition processes of the Xe synchronous chemical shift spectroscopy imaging sequence are independent of each other, but they share the same set of imaging gradients G, which include the destruction gradient Gsp and the encoding gradient Genc. 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129Xe synchronous chemical shift spectroscopy imaging sequences all include a periodic processing part, which includes a pre-damage part and a data acquisition part. 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coil simultaneously emits a 90° pulse, and then immediately applies a damaging gradient Gsp to the original brain 129 Xe magnetic resonance signal and 31 P magnetic resonance signal saturation. In the data acquisition part, 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequence was performed by 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coil simultaneously transmits 90° pulses and small-angle pulses, and the flip angle of the small-angle pulse is α; after the encoding gradient Genc, 31 P Magnetic resonance signals and 129 The entire data acquisition part is repeated n times, and then the pre-damage part and the n-time data acquisition part are repeated m times, that is, the periodic processing part is repeated m times. Where m is the total number of codes in the chemical shift spectroscopy imaging sequence, that is, the total number of codes in the periodic processing part. The coding gradient Genc is calculated according to 31 The gyromagnetic ratio γ( 31 P) calculation, that is, Genc = BW / (γ( 31 P)×FOV), BW is the sampling bandwidth, FOV is the imaging field of view, which is related to the size of the subject's brain. In each cycle processing part, n groups of signals with the same amplitude are obtained. 31 Chemical shift spectroscopy imaging data P (i) The amplitude of the signal is different from that of the n groups 129 Xe chemical shift spectroscopy imaging data S Xe (i), i = 1, 2, … n. This step ensures that the energy metabolism process and blood perfusion process of the subject's brain are collected simultaneously.

[0060] Step 2: Obtain the average chemical shift spectrum image I of creatine phosphate PCr1 and blood perfusion efficiency image I RBC_v1 The specific steps include:

[0061] Step 2.1: Figure 5 As shown, according to step 1, the n groups of signals with the same amplitude are obtained. 31 Chemical shift spectroscopy imaging data P (i) The amplitude of the signal is different from that of the n groups 129 Xe chemical shift spectroscopy imaging data S Xe(i) Obtain n groups of brain samples from the subjects 31 P Chemical shift spectroscopy image I P (i) and n groups 129 Xe chemical shift spectrum image I Xe (i) Then through the brain 31 P Chemical shift spectroscopy image I P (i) Related to the brain 129 Xe chemical shift spectrum image I Xe (i) The spectrum within each pixel is peak fitted to obtain n groups 31 Chemical shift spectroscopic image of creatine phosphate in the brain obtained by P chemical shift spectroscopy imaging I PCr (i) with 129 Chemical shift spectroscopic image of red blood cells in the brain obtained by Xe chemical shift spectroscopy imaging I RBC (i), i = 1, 2, …n .

[0062] Step 2.2: Figure 5 As shown, due to 31 The magnetic resonance spectroscopy images of P generally have weak signal-to-noise ratio. PCr (i) Averaging to obtain the average chemical shift spectrum image I of creatine phosphate PCr1 ; and for 129 Xe, the chemical shift spectrum image I of n groups of brain red blood cells RBC (i) Perform point-by-point fitting according to the following formula to obtain the blood perfusion efficiency V and the signal constant factor S0.

[0063] ,

[0064] Where TR is the repetition time of the data acquisition part in step 1, S(iTR) is I RBC (i) pixel signal intensity (i = 1, 2, … n), α is the pixel signal intensity in step 1 129 The flip angle of the small-angle pulse of the Xe synchronous chemical shift spectroscopy imaging sequence. The distribution of the blood perfusion efficiency V obtained by fitting is the blood perfusion efficiency image I RBC_V1 .

[0065] Step 3: After the subject is stimulated, such as finger movement or injection of capsaicin, steps 1 to 2 are repeated to obtain an average chemical shift spectrum image I of creatine phosphate in the brain of the stimulated subject. PCr2 Image of brain blood perfusion efficiency after stimulation I RBC_V2 .

[0066] Step 4: Calculate and obtain the energy metabolism parameter diagram I of the blood flow dependence of the subject's brainEN-RBC , specifically including the following steps.

[0067] Step 4.1: From step 1, we can see that under the same coding gradient Genc and sampling bandwidth BW, 129 The field of view (FOV) of Xe chemical shift spectroscopy imaging is 31 P's γ( 31 P) / γ( 129 Therefore, the brain blood perfusion efficiency image I RBC_v1 Image cropping and interpolation to the average chemical shift spectrum image of brain creatine phosphate I PCr1 With the same FOV and resolution, we can obtain image I RBC_V1’ ; The brain blood perfusion efficiency image I after stimulation RBC_V2 The image is cropped and interpolated to the average chemical shift spectrum image I of the stimulated brain creatine phosphate PCr2 The same FOV and resolution, denoted as image I RBC_V2’ .

[0068] Step 4.2: Obtaining the response parameter diagram of brain energy metabolism before and after stimulation EN = (I PCr2 -I PCr1 ) / I PCr1 Figure I CBF = (I RBC_V2’ -I RBC_V1’ ) / I RBC_V1’ Finally, the blood flow dependent energy metabolism parameters were obtained. EN-RBC , calculated by the following formula:

[0069] I EN-RBC = I EN / I CBF = (I PCr2 -I PCr1 )×I RBC_V1’ / ((I RBC_V2’ -I RBC_V1’ ) ×I PCr1 ).

[0070] Embodiment 2:

[0071] This embodiment provides a multi-nuclear magnetic resonance device for evaluating blood flow-dependent energy metabolism, including (in the following description, the area to be tested is the brain, but this embodiment is not limited to the area to be tested being the brain, and may also be other areas to be tested of the subject):

[0072] Chemical shift spectroscopy imaging module: used to perform chemical shift spectroscopy imaging on the subject's brain to obtain the subject's brain before stimulation. 31 Chemical shift spectroscopy imaging data P (i) and brain 129 Xe chemical shift spectroscopy imaging data S Xe (i) We also obtained the subjects' 31 Chemical shift spectroscopy imaging data P (i) and brain 129 Xe chemical shift spectroscopy imaging data S Xe (i).

[0073] Spectral image calculation module: used to calculate the 31 Chemical shift spectroscopy imaging data P (i) and brain 129 Xe chemical shift spectroscopy imaging data S Xe (i) Reconstruct the subject's brain 31 P Chemical shift spectroscopy image I P (i) Brain 129 Xe chemical shift spectrum image I Xe (i) by targeting the brain 31 P Chemical shift spectroscopy image I P (i) Brain 129 Xe chemical shift spectrum image I Xe (i) The spectrum in each pixel is peak-fitted to further obtain the chemical shift spectrum image I of creatine phosphate in the brain PCr (i) Chemical shift spectroscopic image of red blood cells in the brain I RBC (i), i = 1,2, … n.

[0074] The chemical shift spectra of creatine phosphate in the brain of group n are PCr (i) averaging to obtain the average chemical shift spectrum image of creatine phosphate; and averaging the chemical shift spectrum images I of the red blood cells of the n groups of brains. RBC (i) Perform point-by-point fitting according to the following formula to obtain the blood perfusion efficiency V and the signal constant factor S0.

[0075] ,

[0076] Where TR is the repetition time of the data acquisition part in step 1, S(iTR) is I RBC (i) pixel signal intensity (i = 1, 2, … n), α is the pixel signal intensity in step 1 129The flip angle of the small-angle pulse of the Xe synchronous chemical shift spectroscopy imaging sequence. The distribution of the blood perfusion efficiency V obtained by fitting is the blood perfusion efficiency image.

[0077] The subjects' brains before stimulation 31 Chemical shift spectroscopy imaging data P (i) and brain 129 Xe chemical shift spectroscopy imaging data S Xe (i) Input to the spectrum image calculation module to obtain the average chemical shift spectrum image I of creatine phosphate in the brain before stimulation PCr1 Image of blood perfusion efficiency of red blood cells in the brain RBC_V1 ; The brain of the subject after stimulation 31 Chemical shift spectroscopy imaging data P (i) and brain 129 Xe chemical shift spectroscopy imaging data S Xe (i) Input to the spectrum image calculation module to obtain the average chemical shift spectrum image I of creatine phosphate in the stimulated brain PCr2 Image of blood perfusion efficiency of red blood cells in the brain RBC_v2 .

[0078] Energy metabolism parameter map calculation module: the blood perfusion efficiency image of the red blood cells in the brain RBC_V1 Image cropping and interpolation to the average chemical shift spectrum image of brain creatine phosphate I PCr1 With the same FOV and resolution, we can obtain image I RBC_V1’ ; The blood perfusion efficiency image of the red blood cells in the brain after stimulation I RBC_v2 The image is cropped and interpolated to the average chemical shift spectrum image I of the stimulated brain creatine phosphate PCr2 The same FOV and resolution, denoted as image I RBC_v2’ ; Calculation of response parameters of brain energy metabolism before and after stimulation Figure I EN = (I PCr2 -I PCr1 ) / I PCr1 Figure I CBF = (I RBC_v2’ -I RBC_V1’ ) / I RBC_V1’ The energy metabolism parameters of blood flow dependence were obtained based on the following formula: EN-RBC ,

[0079] I EN-RBC = I EN / I CBF = (I PCr2 -IPCr1 ) × I RBC_V1’ / ((I RBC_v2’ -I RBC_V1’ ) × I PCr1 ).

[0080] A person skilled in the art can understand that the implementation of the spectral image calculation module and the energy metabolism parameter diagram calculation module of the above-mentioned embodiment can be completed by instructing the relevant hardware through a computer program. The computer program can be stored in a non-volatile computer-readable storage medium. When the computer program is executed, it can include the execution process of the above-mentioned modules.

[0081] Embodiment 3:

[0082] A computer device includes a memory and a processor, wherein a computer program is stored in the memory, and when the processor executes the computer program, the execution process of the spectral image calculation module and the energy metabolism parameter diagram calculation module in the above-mentioned embodiment 2 is implemented.

[0083] Embodiment 4:

[0084] A computer-readable storage medium stores a computer program, which, when executed by a processor, implements the execution process of the spectral image calculation module and the energy metabolism parameter diagram calculation module in the above-mentioned embodiment 2.

[0085] Embodiment 5:

[0086] A computer program product includes a computer program, which, when executed by a processor, implements the execution process of the spectral image calculation module and the energy metabolism parameter map calculation module in the above-mentioned embodiment 2.

[0087] It should be noted that the embodiments described in the present invention are merely examples of the spirit of the present invention. Those skilled in the art may make various modifications or additions to the described embodiments or replace them in similar ways, but they will not deviate from the spirit of the present invention or exceed the scope defined by the attached claims.

Claims

1. A multi-nuclear magnetic resonance method for evaluating blood flow-dependent energy metabolism, characterized in that: The following steps are involved: Step 1: Collect the data of the test area of ​​n groups of subjects. 31 P chemical shift spectroscopy imaging data; collecting the n groups of subjects in the area to be tested 129 Xe chemical shift spectroscopy imaging data; Step 2: Based on 31 P chemical shift spectroscopy imaging data and 129 Xe chemical shift spectroscopy imaging data is used to calculate the average chemical shift spectroscopy image of creatine phosphate and the blood perfusion efficiency image of red blood cells; Step 3, after stimulating the subject, repeating steps 1 and 2 to obtain an average chemical shift spectrum image of creatine phosphate in the test area of ​​the stimulated subject and a blood perfusion efficiency image of red blood cells in the test area after stimulation; Step 4: Calculate the blood flow-dependent energy metabolism parameter of the test area of ​​the subject based on the average chemical shift spectrum image of creatine phosphate before and after stimulation and the blood perfusion efficiency image. EN-RBC , In step 1 31 P chemical shift spectroscopy imaging data and 129 The acquisition of Xe chemical shift spectroscopy imaging data consists of the following steps: Step 1.

1. The subject lies prone on the MRI bed and is connected to 129 Xe gas delivery system; Step 1.2: The subject passes 129 Xe Gas Delivery System for Sustained Breathing Hyperpolarization 129 A mixture of Xe gas and oxygen is used to 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequence scanning, obtain 31 P chemical shift spectroscopy imaging data and 129 Xe chemical shift spectroscopy imaging data, 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 The RF emission / data acquisition process of the Xe synchronous chemical shift spectroscopy imaging sequence is independent of each other and uses the same set of imaging gradients G, which include the destruction gradient Gsp and the encoding gradient Genc. In step 1.2 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequences all include a periodic processing part, which includes a pre-damage part and a data acquisition part. In the pre-damage part, 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coil simultaneously emits a 90° pulse, and then immediately applies a damage gradient Gsp to the original area to be tested. 129 Xe magnetic resonance signal and 31 P MRI signal saturation, during the data acquisition section, 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequence was performed by 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coil simultaneously transmits 90° pulses and small angle pulses; after being processed by coded gradient Genc, 31 P magnetic resonance signal and 129 Xe magnetic resonance signal acquisition, The encoding gradient Genc = BW / (γ( 31 P)×FOV), BW is the sampling bandwidth, FOV is the imaging field of view, γ( 31 P) is 31 Gyromagnetic ratio of P; The average chemical shift spectrum image of creatine phosphate and the blood perfusion efficiency image before stimulation in step 4 are respectively denoted as I PCr1 and I RBC_V1 The average chemical shift spectrum image of creatine phosphate and the blood perfusion efficiency image after stimulation are respectively denoted as I PCr2 and I RBC_V2 , In step 4, the energy metabolism parameter diagram , Among them, I RBC_V1’ To transform the blood perfusion efficiency image I of the area to be tested RBC_v1 Image clipping and interpolation are performed to the average chemical shift spectrum image I of creatine phosphate in the area to be measured PCr1 Images obtained with the same FOV and resolution; I RBC_V2’ The blood perfusion efficiency image I of the stimulated area to be tested is RBC_V2 The image is cut and interpolated to the average chemical shift spectrum image I of the creatine phosphate in the test area of ​​the stimulated subject. PCr2 Images obtained with the same FOV and resolution.

2. A multi-nuclear magnetic resonance method for evaluating blood flow-dependent energy metabolism according to claim 1, characterized in that: In step 1.1, the subject wears 31 P synchronous transceiver RF coil and 129 Xe synchronous transceiver RF coil, 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coils partially overlap and are both located on the coil substrate. 129 Xe synchronous transceiver RF coil 31 P trap circuit, 129 Xe transmit receive switch 129 Xe signal filter connection, 129 Xe signal filters and 129 Xe preamplifier connections, 31 P synchronous transceiver RF coil 129 Xe trap circuit, 31 P transmit receive switch and 31 P signal filter connection, 31 P signal filter and 31 P Preamplifier connections.

3. A multi-nuclear magnetic resonance method for evaluating blood flow-dependent energy metabolism according to claim 1, characterized in that: In steps 2 and 3, the average chemical shift spectrum image of creatine phosphate and the blood perfusion efficiency image are calculated based on the following steps: Step 2.1: According to 31 Chemical shift spectroscopy imaging data P (i) with 129 Xe chemical shift spectroscopy imaging data S Xe (i) Obtain 31 P Chemical shift spectroscopy image I P (i) with 129 Xe chemical shift spectrum image I Xe (i) Then, through 31 P Chemical shift spectroscopy image I P (i) with 129 Xe chemical shift spectrum image I Xe The spectrum in each pixel of (i) is peak-fitted to obtain the chemical shift spectrum image I of creatine phosphate PCr (i) Chemical shift spectrum image of red blood cells I RBC (i), i = 1, 2, …n, Step 2.2: The chemical shift spectrum image of creatine phosphate PCr (i) averaging to obtain an average chemical shift spectrum image of creatine phosphate; and averaging the chemical shift spectrum image of red blood cells in the test area. RBC (i) Perform point-by-point fitting according to the following formula to obtain the blood perfusion efficiency V and the signal constant factor S0, ， Where TR is the repetition time of the data acquisition part, S(iTR) is I RBC (i) The pixel signal intensity, α is 129 The distribution of blood perfusion efficiency V obtained by fitting the flip angle of the small-angle pulse of the Xe synchronous chemical shift spectroscopy imaging sequence is the blood perfusion efficiency image.

4. A multi-nuclear magnetic resonance device for evaluating blood flow-dependent energy metabolism, characterized in that: include: Chemical shift spectroscopy imaging module: used to utilize 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 The Xe synchronous chemical shift spectroscopy imaging sequence performs chemical shift spectroscopy imaging on the test area of ​​the subject to obtain the test area of ​​the subject before stimulation. 31 Chemical shift spectroscopy imaging data P (i) and the area to be tested 129 Xe chemical shift spectroscopy imaging data S Xe (i) We also obtained the subjects' 31 Chemical shift spectroscopy imaging data P (i) and the area to be tested 129 Xe chemical shift spectroscopy imaging data S Xe (i); 31 P chemical shift spectroscopy imaging data and 129 The acquisition of Xe chemical shift spectroscopy imaging data includes: The subject lies prone on the MRI bed and is connected to 129 Xe gas delivery system; The subjects passed 129 Xe Gas Delivery System for Sustained Breathing Hyperpolarization 129 A mixture of Xe gas and oxygen is used to 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequence scanning, obtain 31 P chemical shift spectroscopy imaging data and 129 Xe chemical shift spectroscopy imaging data, 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 The RF emission / data acquisition process of the Xe synchronous chemical shift spectroscopy imaging sequence is independent of each other and uses the same set of imaging gradients G, which include the destruction gradient Gsp and the encoding gradient Genc. 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequences all include a periodic processing part, which includes a pre-damage part and a data acquisition part. In the pre-damage part, 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coil simultaneously emits a 90° pulse, and then immediately applies a damage gradient Gsp to the original area to be tested. 129 Xe magnetic resonance signal and 31 P MRI signal saturation, during the data acquisition section, 31 P Synchronous Chemical Shift Spectroscopy Sequence and 129 Xe synchronous chemical shift spectroscopy imaging sequence was performed by 31 P synchronous transceiver RF coil and 129 The Xe synchronous transceiver RF coil simultaneously transmits 90° pulses and small angle pulses; after being processed by coded gradient Genc, 31 P magnetic resonance signal and 129 Xe magnetic resonance signal acquisition, The encoding gradient Genc = BW / (γ( 31 P)×FOV), BW is the sampling bandwidth, FOV is the imaging field of view, γ( 31 P) is 31 Gyromagnetic ratio of P; Spectral image calculation module: used to calculate the spectral image of the area to be tested before stimulation. 31 Chemical shift spectroscopy imaging data P (i) and the area to be tested 129 Xe chemical shift spectroscopy imaging data S Xe (i) Calculate the average chemical shift spectrum image I of creatine phosphate in the test area before stimulation PCr1 Blood perfusion efficiency image I of red blood cells in the area to be tested RBC_V1 ; Used to determine the area to be tested after stimulation 31 Chemical shift spectroscopy imaging data P (i) and the area to be tested 129 Xe chemical shift spectroscopy imaging data S Xe (i) Calculate the average chemical shift spectrum image I of creatine phosphate in the stimulated area to be tested PCr2 Blood perfusion efficiency image I of red blood cells in the area to be tested RBC_V2 ; Energy metabolism parameter map calculation module: used to calculate the blood flow-dependent energy metabolism parameter map I of the subject's test area based on the average chemical shift spectrum image of creatine phosphate before and after stimulation and the blood perfusion efficiency image EN-RBC； In the energy metabolism parameter graph calculation module, The average chemical shift spectrum image of creatine phosphate and the blood perfusion efficiency image before stimulation are respectively denoted as I PCr1 and I RBC_V1 The average chemical shift spectrum image of creatine phosphate and the blood perfusion efficiency image after stimulation are respectively denoted as I PCr2 and I RBC_V2 , Energy metabolism parameters diagram , Among them, I RBC_V1’ To transform the blood perfusion efficiency image I of the area to be tested RBC_v1 Image clipping and interpolation are performed to the average chemical shift spectrum image I of creatine phosphate in the area to be measured PCr1 Images obtained with the same FOV and resolution; I RBC_V2’ The blood perfusion efficiency image I of the stimulated area to be tested is RBC_V2 The image is cut and interpolated to the average chemical shift spectrum image I of the creatine phosphate in the test area of ​​the stimulated subject. PCr2 Images obtained with the same FOV and resolution.

5. A multi-nuclear magnetic resonance device for evaluating blood flow-dependent energy metabolism according to claim 4, characterized in that: In the spectral image calculation module, according to 31 Chemical shift spectroscopy imaging data P (i) with 129 Xe chemical shift spectroscopy imaging data S Xe (i) Obtain 31 P Chemical shift spectroscopy image I P (i) with 129 Xe chemical shift spectrum image I Xe (i) Then, through 31 P Chemical shift spectroscopy image I P (i) with 129 Xe chemical shift spectrum image I Xe The spectrum in each pixel of (i) is peak-fitted to obtain the chemical shift spectrum image I of creatine phosphate PCr (i) Chemical shift spectrum image of red blood cells I RBC (i), i = 1, 2, … n, The chemical shift spectrum image of creatine phosphate I PCr (i) averaging to obtain an average chemical shift spectrum image of creatine phosphate; and averaging the chemical shift spectrum image of red blood cells in the test area. RBC (i) Perform point-by-point fitting according to the following formula to obtain the blood perfusion efficiency V and the signal constant factor S0, ， Where TR is the repetition time of the data acquisition part, S(iTR) is I RBC (i) The pixel signal intensity, α is 129 The distribution of blood perfusion efficiency V obtained by fitting the flip angle of the small-angle pulse of the Xe synchronous chemical shift spectroscopy imaging sequence is the blood perfusion efficiency image.

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