CN109730677A - Signal processing method, device and the storage medium of irrelevant movement imaging in voxel - Google Patents
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Abstract
The invention discloses signal processing method, device and the storage mediums of movement imaging irrelevant in a kind of voxel, this method comprises: the b Distribution value of setting non-zero, and IVIM Diffusion Imaging magnetic resonance imaging is carried out at each b value based on MRI scanner, export the corresponding image of each b value；The b value is related to the intensity of Diffusion Imaging gradient magnetic；Region of interest on the corresponding IVIM Diffusion Imaging image of each b value is subjected to attenuation model fitting, output indicates the IVIM parameter of b value and imaging signal strength relationship.The present invention is fitted by using the image of the b value of non-zero, reduces fitting difficulty, and calculated result is more stable, is conducive to embody the relationship between Diffusion Imaging gradient magnetic field strength and picture signal, is conducive to the extensive use on clinical medicine.
Description
Technical field
The present invention relates in the Diffusion MR Images and technical field of medical image processing more particularly to a kind of voxel
Signal processing method, device and the storage medium of irrelevant movement imaging.
Background technique
Irrelevant movement (intravoxel incoherent motion, IVIM) passes through the Diffusion MR Images in voxel
(diffusion weighted magnetic resonance imaging) is fast come the movement for observing hydrone in organ-tissue
Degree.The movement velocity of hydrone in living tissue includes the hydrone (perfusion) fast moved in blood vessel structure and general thin
Slower hydrone (disperse) is shifted in intracellular or space between cells, the latter one are caused by Brownian movement.IVIM imaging system
Imaging (b=0s/mm of the composition of column generally by no Diffusion Imaging gradient magnetic2) and a series of varying strengths (or difference is held
The continuous time) Diffusion Imaging gradient magnetic imaging.Diffusion Imaging gradient magnetic is higher (b value is bigger), and the signal of imaging is lower.
As indicated in attached drawing 2, the relationship that b value is bigger and picture signal is lower is related to comprising the mobile speed of hydrone in organizing.Water
Molecule movement is faster, and picture signal reduces faster.In many organs of human body, such as liver, the relationship one of b value and imaging signal
As be divided into two parts: (1): when low b-values signal rapid decrease with tissue in hemoperfusion caused by quickly hydrone displacement have
It closes；(2) the in relatively slow decline of signal is related to the hydrone disperse in tissue when high b value.These relationships substantially show as b
Value series and the exponential damping of signal decline relationship.
In the prior art, when calculating IVIM parameter, b=0s/mm is mainly used2Image and b thereafter when being greater than 0
Image carries out attenuation model fitting, but this mode is fitted difficulty, and measurement result is unstable, it is difficult to real in clinical medicine
Border applies.
Therefore, the existing technology needs to be improved and developed.
Summary of the invention
The technical problem to be solved in the present invention is that in view of the above drawbacks of the prior art, not phase is provided in a kind of voxel
Signal processing method, device and the storage medium of dry movement imaging, it is intended to it solves in the prior art when calculating IVIM parameter,
Mainly use b=0s/mm2Image of image when being greater than 0 with b thereafter carry out attenuation model fitting, cause formula fitting tired
The problems such as difficulty, measurement result is unstable.
The technical proposal for solving the technical problem of the invention is as follows:
The signal processing method of irrelevant movement imaging in a kind of voxel, wherein the described method includes:
(being greater than zero) b Distribution value of non-zero is set, and IVIM Diffusion Imaging is carried out at each b value based on MRI scanner
Magnetic resonance imaging exports the corresponding image of each b value；The b value represents the intensity of Diffusion Imaging gradient magnetic；
Region of interest signal strength on the corresponding IVIM Diffusion Imaging image of each b value is carried out attenuation model to intend
It closes, output indicates the IVIM parameter of b value and imaging signal strength relationship.
The signal processing method of irrelevant movement imaging in the voxel, wherein the b value can have 15, and divide
Cloth is in 1000s/mm2Below.
The signal processing method of irrelevant movement imaging in the voxel, wherein the b value includes: b=3, and 10,25,
30,40,45,50,80,200,300,400,500,600,700,800s/mm2。
The signal processing method of irrelevant movement imaging in the voxel, wherein the attenuation model includes two fingers number
Attenuation model or three exponential decay models.
The signal processing method of irrelevant movement imaging in the voxel, wherein when each b value is corresponding
When region of interest carries out double exponential decay model fittings on IVIM Diffusion Imaging image, formula are as follows:
SI (b)=SIlowestb×[(1-PF)×exp(-b×Dslow)+PF×exp(-b×Dfast)],
Wherein, SIlowestbFor the minimum corresponding image intensity signal of non-zero b value, SI (b) is the figure that some b value obtains
As signal strength, the DslowReflect the speed of hydrone disperse displacement, DfastReflect the fast of the hydrone displacement of hemoperfusion
Slowly, the percentage that PF reflection perfusion accounts for.
The signal processing method of irrelevant movement imaging in the voxel, wherein when each b value is corresponding
When region of interest carries out the fitting of three exponential decay models on IVIM Diffusion Imaging image, formula are as follows:
SI (b)=SIlowestb×[F’slow×exp(-b×D’slow)+F’fast×exp(-b×D’fast)+F’Vfast×
exp(-b×D’Vfast)],
Wherein, SIlowestbFor the minimum corresponding image intensity signal of non-zero b value, SI (b) is the figure that some b value obtains
As signal strength, the D 'slowReflect the speed of hydrone disperse displacement, (D 'Vfast, F 'Vfast) it is the hemoperfusion phase being exceedingly fast
The hydrone of pass shifts, (D 'fast, F 'fast) it is the relevant hydrone displacement of faster hemoperfusion.
The signal processing apparatus of irrelevant movement imaging in a kind of voxel, wherein described device includes:
Scanning imagery module carries out IVIM for establishing the b Distribution value of non-zero, and based on MRI scanner at each b value
Diffusion Imaging magnetic resonance imaging exports the corresponding image of each b value；
The Fitting Calculation module, for carrying out region of interest on the corresponding IVIM Diffusion Imaging image of each b value
Attenuation model fitting, output indicate the IVIM parameter of b value and imaging signal strength relationship.
The signal processing apparatus of irrelevant movement imaging in the voxel, wherein the b value has 15, and is distributed in
1000s/mm2Below.
The signal processing apparatus of irrelevant movement imaging in the voxel, wherein the b value includes: b=1, and 3,10,
25,30,40,50,80,200,300,400,500,600,700,800s/mm2。
A kind of storage medium is stored thereon with a plurality of instruction, wherein and described instruction is suitable for being loaded and being executed by processor,
To execute the step of realizing the signal processing method of irrelevant movement imaging in voxel described in any of the above embodiments.
Beneficial effects of the present invention: the present invention calculating IVIM parameter is carried out by using the image of the b value of non-zero
Fitting reduces fitting difficulty, and calculated result is more stable, is conducive to embody Diffusion Imaging gradient magnetic field strength and picture signal
Between relationship, be conducive to the extensive use on clinical medicine.
Detailed description of the invention
Fig. 1 is the flow chart of the preferred embodiment of the signal processing method of irrelevant movement imaging in voxel of the present invention.
Fig. 2 is the disperse magnetic resonance imaging schematic diagram of liver.
Fig. 3 is the disperse magnetic resonance imaging of liver with the attenuation relation of b value.
Fig. 4 is b=0 in liver disperse magnetic resonance imaging, 1,2,15s/mm2Image is shown.
Fig. 5 is liver IVIM b=100s/mm2The relationship of b value and liver parenchyma signal when following.
The signal processing method that irrelevant movement is imaged in voxel Fig. 6 more of the invention and traditional method is having
The comparison of body application effect.
Fig. 7 is that the signal processing method being imaged using movement irrelevant in voxel of the invention and traditional method is existed
Concrete application effect contrast figure.
Fig. 8 is the schematic diagram of the function of the signal processing apparatus of irrelevant movement imaging in voxel of the invention.
Specific embodiment
To make the objectives, technical solutions, and advantages of the present invention clearer and more explicit, right as follows in conjunction with drawings and embodiments
The present invention is further described.It should be appreciated that the specific embodiments described herein are merely illustrative of the present invention, and do not have to
It is of the invention in limiting.
Due to when calculating IVIM parameter, mainly using b=0s/mm in the prior art2Image and b thereafter be not 0
When image carry out attenuation model fitting, but this mode is fitted difficulty, and measurement result is unstable, it is difficult in clinical medicine
Middle practical application is got up.To solve the above-mentioned problems, a kind of signal of irrelevant movement imaging in voxel is provided in the present embodiment
Processing method, it is specific as shown in fig. 1, this method comprises:
Step S100, the b Distribution value of non-zero is set, and IVIM Diffusion Imaging is carried out at each b value based on MRI scanner
Magnetic resonance imaging exports the corresponding image of each b value；The b value represents the intensity of Diffusion Imaging gradient magnetic；
Step S200, region of interest on the corresponding IVIM Diffusion Imaging image of each b value is subjected to attenuation model
Fitting, output indicate the IVIM parameter of b value and imaging signal strength relationship.
According to double exponential decay models, IVIM parameter is indicated by three parameters, respectively Dslow(D), Dfast(D*), PF
(f).D by and largeslowReflect the speed of hydrone disperse displacement, DfastReflect the speed of the hydrone displacement of hemoperfusion,
The percentage that PF reaction perfusion accounts for, the state of certain organ-tissues can be represented by these three parameters, as shown in figs 2-4
Liver disperse magnetic resonance imaging accompanying drawings.In traditional IVIM calculation method of parameters, b=is mainly used
0s/mm2Image carry out attenuation model fitting with image when b is not 0 thereafter (shown in such as Fig. 2, Fig. 3).But due to b
=0s/mm2When (when no additional Diffusion Imaging gradient magnetic) in the magnetic resonance imaging sequence echoplanar of imaging
Blood vessel (including tiny blood vessels) is high RST on imaging (EPI) image, and when having additional Diffusion Imaging gradient magnetic, even if b
=1s/mm2When, blood vessel (including tiny blood vessels) is shown as low signal on image, as shown in Figure 4.And it can be very from Fig. 3
It is apparent from, the sharp fall of signal between image display b=0 image and b=1 image, and b=1 image and b=2 image
Between signal decline it is less.And exponential type decline is not presented between 1,2 image in as shown in Figure 5, b=0；B=0 has with b=1
Very quick blackout, and when b=1 and b=2, liver parenchyma signal is substantially close to (b=2 is slightly lower).Therefore, using b=
0s/mm2Image carry out attenuation model fitting with image when b is not 0 thereafter, caused calculated result is simultaneously unstable, and
And be difficult to apply in specific clinical medicine, for example, in clinical medicine, it is difficult to distinguish normal and abnormal organ-tissue
(Fig. 6 and Fig. 7 is shown in such as hepatic fibrosis-renal tubular ectasia syndrome, illustration).For this purpose, not using b=0 to scheme when calculating IVIM parameter in the present embodiment
As being fitted, to improve the stability of calculated result.
Specifically, the b Distribution value that non-zero is preset in the present embodiment is then based on MRI (Magnetic Resonance
Imaging, magnetic resonance imaging) scanner carries out IVIM Diffusion Imaging magnetic resonance imaging at each b value, export each b value pair
The image answered.For example, b value is arranged 15, and it is distributed in 1000s/mm2Hereinafter, for example, can use b=3,10,25,
30,40,50,80,200,300,400,500,600,700,800s/mm2.As Fig. 4 and Fig. 5 in liver with disperse magnetic resonance at
As for, in figures 4 and 5 scan when include b=0 image, specifically carry out IVIM parameter calculate when, do not use b
=0 image.
Further, need sampler in image acquisition process when carrying out Diffusion Imaging magnetic resonance imaging in the present embodiment
Tranquil regular breathing into magnetic resonance imaging.After by magnetic resonance imaging, image corresponding to each b value is obtained.Citing
Illustrate, the region of interest in embodiment is drawn in the image based on low b-values, the mode drawn can using manually draw or
Person draws automatically, and as shown in Figure 2, disperse magnetic resonance imaging region of interest letter is shown in lower row image lower right in Fig. 2
Attenuation relation number with b value, similar double exponential decay models, enlarged drawing is similar to Fig. 3.According to piecewise fitting side in the present embodiment
Method (segmented fitting) is divided when determining low b-values and high b value using threshold value b value.Threshold value b value is used for
Disperse and perfusion part are separated, uses b=200s/mm in the present embodiment2As threshold value b value, as shown in Figure 3.Certainly, threshold value
B value is not one quantitative, such as b=60s/mm can be used in the IVIM Diffusion Imaging image of liver organ2As threshold value b
Value.With the difference that threshold value b value selects, PF, D is imaged in the same IVIMslow, DfastValue can be different therewith.
Further, the present embodiment declines region of interest on the corresponding IVIM Diffusion Imaging image of each b value
Subtract models fitting, output indicates the IVIM parameter of b value and imaging signal strength relationship.Preferably, it when being fitted, can be used
Double exponential decay model fittings or three Exponential Models.Specifically, the IVIM Diffusion Imaging corresponding when each b value
When region of interest carries out double exponential decay model fittings on image, formula are as follows:
SI (b)=SIlowestb×[(1-PF)×exp(-b×Dslow)+PF×exp(-b×Dfast)],
Wherein, SIlowestbFor the minimum corresponding image intensity signal of non-zero b value, SI (b) is the figure that some b value obtains
As signal strength, the DslowReflect the speed of hydrone disperse displacement, DfastReflect the fast of the hydrone displacement of hemoperfusion
Slowly, the percentage that PF reflection perfusion accounts for.
Due to not using the image of b=0 to be fitted in this implementation, first start fitting be exactly IVIM disperse
A minimum non-zero image, can be b=3s/mm in image2, it is also possible to b=15s/mm2。
For example, b=3s/mm2Starting point as double exponential dampings.It is greater than b=3s/mm corresponding to remaining2Each b value
Signal is calculated as relative to b=3s/mm in disperse image2The ratio of picture signal simultaneously assumes b=3s/mm2Picture signal is 100, i.e.,
SInorm=(SI/SI3)×100SInormThat is relative signal, SI are corresponding to signal in the disperse image of some value, SI3For b=
3s/mm2Picture signal.According to double exponential decay models, signal decaying is simulated according to following formula:
SI (b)=SI3×[(1-PF)×exp(-b×Dslow)+PF×exp(-b×Dfast)]；
If b=3 is most low b-values, 1 (or 100) are set as to induction signal.If according to segmented fitting
(piecewise fitting), first calculates Dslow, with least square linear Linear Quasi it is worthwhile >=thresholdb-values (the above b of threshold values b)
It is worth corresponding image signals logarithm.The D of acquisitionslowThe above double exponential decay models are substituted into, according to nonlinear least square fitting,
The signal strength obtained according to different b value actual measurements is by the Levenberg-Marquardt algorithm (or according to Trust-
Region algorithm) acquire PF and Dfast.Alternatively, as Fig. 3 is shown, the D of acquisitionslowLater according to calculate DslowStraight line reversely prolong
Length intersects with starting point ordinate, SI3The distance of signal and crosspoint is PF.
Further, can also will feel on the corresponding IVIM Diffusion Imaging image of each b value in this present embodiment
Region of interest carries out three exponential decay model fittings, formula are as follows:
SI (b)=SIlowestb×[F’slow×exp(-b×D’slow)+F’fast×exp(-b×D’fast)+F’Vfast×
exp(-b×D’Vfast)],
Wherein, SIlowestbFor the minimum corresponding image intensity signal of non-zero b value, SI (b) is the figure that some b value obtains
As signal strength, the D 'slowReflect the speed of hydrone disperse displacement, (D 'Vfast, F 'Vfast) it is the hemoperfusion phase being exceedingly fast
The hydrone of pass shifts, (D 'fast, F 'fast) it is the relevant hydrone displacement of faster hemoperfusion.
Other than piecewise fitting presented above, either double exponential decay models or three exponential decay models,
IVIM parameter can be calculated with full fitting (full fitting).
It is worth noting that in the application primarily directed to traditional calculating IVIM parameter when, using b=0s/mm2Figure
As image when with b not thereafter being 0 improves to carry out the mode of attenuation model fitting, propose a kind of to use b value to be non-zero
Approximating method guarantees the stability of calculated result to calculate more precisely IVIM parameter, and is conducive to clinical medical
Using.
For example, Fig. 6 shows the IVIM with a collection of 4 Healthy Peoples and 3 hepatic fibrosis-renal tubular ectasia syndrome patients in Fig. 6 and Fig. 7
Data DslowWith the result of PF.Healthy People and hepatic fibrosis-renal tubular ectasia syndrome patient are by D when calculating when with b=0slowOr PF cannot area
Point, and do not have to Healthy People and hepatic fibrosis-renal tubular ectasia syndrome patient when b=0 and press DslowOr PF can be distinguished.Again as shown in Figure 7, Fig. 7
In A figure illustrate using in the present embodiment in voxel irrelevant movement imaging the hepatic fibrosis that is obtained of signal processing method
The differentiation effect of change, the B chart in Fig. 7 show the hepatic fibrosis-renal tubular ectasia syndrome obtained using traditional IVIM calculation method of parameters
Distinguish effect.A and B is with a batch IVIM scan data.When calculating IVIM parameter, b=0 is not included in the Fitting Calculation in A figure, can
To show hepatic fibrosis-renal tubular ectasia syndrome patient (substantive bead) PF, D compared with Healthy People (hollow beads)slowAnd DfastDecline, therefore
Hepatic fibrosis-renal tubular ectasia syndrome and normal sampler can obviously be distinguished.And when calculating IVIM parameter, b=0 is included in fitting meter in B figure
It calculates, calculated result is unstable, therefore hepatic fibrosis-renal tubular ectasia syndrome (substantive bead) and normal sampler (hollow beads) cannot be distinguished.It can
See, by not using the image the Fitting Calculation of b=0 in method of the invention so that IVIM parameter calculate it is more stable with it is accurate,
Be conducive to the extensive use on clinical medicine.
Those of ordinary skill in the art will appreciate that realizing all or part of the process in above-described embodiment method, being can be with
Relevant hardware is instructed to complete by computer program, the computer program can be stored in a non-volatile computer
In read/write memory medium, the computer program is when being executed, it may include such as the process of the embodiment of above-mentioned each method.Wherein,
To any reference of memory, storage, database or other media used in each embodiment provided by the present invention,
Including non-volatile and/or volatile memory.Nonvolatile memory may include read-only memory (ROM), programming ROM
(PROM), electrically programmable ROM (EPROM), electrically erasable ROM (EEPROM) or flash memory.Volatile memory may include
Random access memory (RAM) or external cache.By way of illustration and not limitation, RAM is available in many forms,
Such as static state RAM (SRAM), dynamic ram (DRAM), synchronous dram (SDRAM), double data rate sdram (DDRSDRAM), enhancing
Type SDRAM (ESDRAM), synchronization link (Synchlink) DRAM (SLDRAM), memory bus (Rambus) direct RAM
(RDRAM), direct memory bus dynamic ram (DRDRAM) and memory bus dynamic ram (RDRAM) etc..
It based on the above embodiment, should the present invention also provides a kind of signal processing apparatus of movement imaging irrelevant in voxel
Processing unit may include the computer-readable storage medium in above-described embodiment, can also be as shown in Figure 8, comprising: sweep
Retouch image-forming module 810 and the Fitting Calculation module 820.Specifically, scanning imagery module 810, for setting up the b value point of non-zero
Cloth, and IVIM Diffusion Imaging magnetic resonance imaging is carried out at each b value based on MRI scanner, export the corresponding figure of each b value
Picture, the b value are related to the intensity of Diffusion Imaging gradient magnetic；The Fitting Calculation module 820, for each b value is right with it
Region of interest carries out attenuation model fitting on the IVIM Diffusion Imaging image answered, and output indicates b value and imaging signal strength relationship
IVIM parameter.For example, the b value in embodiment there are 15, and it is distributed in 1000s/mm2Hereinafter, and the b value includes: b
=3,10,25,30,40,45,50,80,200,300,400,500,600,700,800s/mm2.The device of this implementation is carrying out
When IVIM parameter fitting calculates, the image of b=0 is not used to be fitted, to calculate more precisely IVIM parameter, guaranteed
The stability of calculated result, and be conducive to clinical medical application.
In conclusion the invention discloses a kind of signal processing method of movement imaging irrelevant in voxel, device and depositing
Storage media.This method comprises: set up the b Distribution value of non-zero, and based on MRI scanner carried out at each b value IVIM disperse at
As magnetic resonance imaging, the corresponding image of each b value is exported；The b value is related to the intensity of Diffusion Imaging gradient magnetic；It will be each
Region of interest carries out attenuation model fitting on the corresponding IVIM Diffusion Imaging image of a b value, and output indicates that b value and imaging are believed
The IVIM parameter of number strength relationship.The present invention is fitted by using the image of the b value of non-zero, reduces fitting difficulty, and
Calculated result is more stable, is conducive to embody the relationship between Diffusion Imaging gradient magnetic field strength and picture signal, be conducive to
Extensive use on clinical medicine.
It should be understood that the application of the present invention is not limited to the above for those of ordinary skills can
With improvement or transformation based on the above description, all these modifications and variations all should belong to the guarantor of appended claims of the present invention
Protect range.Especially it is worth noting that, application of the invention is both not limited to hepatic fibrosis-renal tubular ectasia syndrome, is also not limited to liver.It can be with
Infer, present invention could apply to the diseases such as tumour, inflammation, inborn variation, also can be applied to such as brain, mammary gland, pancreas,
Kidney, prostate etc. organ and tissue.
Claims (10)
1. the signal processing method of irrelevant movement imaging in a kind of voxel, which is characterized in that the described method includes:
The b Distribution value of non-zero is set up, and IVIM Diffusion Imaging magnetic resonance imaging is carried out at each b value based on MRI scanner, it is defeated
The corresponding image of each b value out；The b value represents the intensity of Diffusion Imaging gradient magnetic；
Region of interest on the corresponding IVIM Diffusion Imaging image of each b value is subjected to attenuation model fitting, output indicates b
The IVIM parameter of value and imaging signal strength relationship.
2. the signal processing method of irrelevant movement imaging in voxel according to claim 1, which is characterized in that the b
Value has 15, and is distributed in 1000s/mm2Below.
3. the signal processing method of irrelevant movement imaging in voxel according to claim 2, which is characterized in that the b
Value includes: b=3, and 10,25,30,40,45,50,80,200,300,400,500,600,700,800s/mm2。
4. the signal processing method of irrelevant movement imaging in voxel according to claim 3, which is characterized in that described to decline
Subtracting model includes double exponential decay models or three exponential decay models.
5. the signal processing method of irrelevant movement imaging in voxel according to claim 4, which is characterized in that when each
When region of interest carries out double exponential decay model fittings on the corresponding IVIM Diffusion Imaging image of a b value, formula are as follows:
SI (b)=SIlowestb×[(1-PF)×exp(-b×Dslow)+PF×exp(-b×Dfast)],
Wherein, SIlowestbFor the minimum corresponding image intensity signal of non-zero b value, SI (b) is the picture signal that some b value obtains
Intensity, the DslowReflect the speed of hydrone disperse displacement, DfastReflect that the speed of the hydrone displacement of hemoperfusion, PF are anti-
Reflect the percentage that perfusion accounts for.
6. the signal processing method of irrelevant movement imaging in voxel according to claim 4, which is characterized in that when each
When region of interest carries out the fitting of three exponential decay models on the corresponding IVIM Diffusion Imaging image of a b value, formula are as follows:
SI (b)=SIlowestb×[F’slow×exp(-b×D’slow)+F’fast×exp(-b×D’fast)+F’Vfast×exp(-
b×D’Vfast)],
Wherein, SIlowestbFor the minimum corresponding image intensity signal of non-zero b value, SI (b) is the picture signal that some b value obtains
Intensity, the D 'slowReflect the speed of hydrone disperse displacement, (D 'Vfast, F 'Vfast) reflect that the hemoperfusion being exceedingly fast is relevant
Hydrone displacement, (D 'fast, F 'fast) the relevant hydrone displacement of the faster hemoperfusion of reflection.
7. the signal processing apparatus of irrelevant movement imaging in a kind of voxel, which is characterized in that described device includes:
Scanning imagery module carries out IVIM disperse for setting the b Distribution value of non-zero, and based on MRI scanner at each b value
Magnetic resonance imaging is imaged, exports the corresponding image of each b value；
The Fitting Calculation module, for region of interest on the corresponding IVIM Diffusion Imaging image of each b value to be decayed
Models fitting, output indicate the IVIM parameter of b value and imaging signal strength relationship.
8. the signal processing apparatus of irrelevant movement imaging in voxel according to claim 7, which is characterized in that the b
Value has 15, and is distributed in 1000s/mm2Below.
9. the signal processing apparatus of irrelevant movement imaging in voxel according to claim 8, which is characterized in that the b
Value includes: b=3, and 10,25,30,40,45,50,80,200,300,400,500,600,700,800s/mm2。
10. a kind of storage medium is stored thereon with a plurality of instruction, which is characterized in that described instruction is suitable for by processor load simultaneously
It executes, to execute the signal processing method for realizing irrelevant movement imaging in the described in any item voxels of the claims 1-7
The step of.
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| CN111407278A (en) * | 2020-03-31 | 2020-07-14 | 浙江大学 | Method and device for measuring placental blood flow by using flow velocity compensated and uncompensated diffusion magnetic resonance |
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| CN114646913B (en) * | 2020-12-21 | 2023-06-02 | 北京大学第三医院（北京大学第三临床医学院） | Non-invasive measurement method for microstructure of biological tissue |
| CN115421086A (en) * | 2022-09-02 | 2022-12-02 | 哈尔滨医科大学 | Incoherent motion tensor magnetic resonance imaging method in super-fusion voxel for accurately analyzing complex histological features of living heart |
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