CN105093145B - Coil sensitivity modification method - Google Patents
Coil sensitivity modification method Download PDFInfo
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- CN105093145B CN105093145B CN201410211234.0A CN201410211234A CN105093145B CN 105093145 B CN105093145 B CN 105093145B CN 201410211234 A CN201410211234 A CN 201410211234A CN 105093145 B CN105093145 B CN 105093145B
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Abstract
The present invention provides coil sensitivity modification method, including obtains the distribution of coil three-dimensional sensitibility reciprocal；Had in projection depth according to coil received signal and obtains an effectively projection depth with the physical characteristic apart from monotone decreasing；Curve of the three-dimensional sensitivity profile of the coil on coil projecting direction is modified based on effective projection depth.The technical program is modified the sensitivity of coil by the physical characteristic for coil.The efficient diagnosis region that the calibration result of this method can reach in image close to coil obtains good homogeneity correction, and good noise suppressed is obtained without diagnostic value region far from coil, it also avoids after calculating sensitivity profile using pre-scan information, the complex calculation that the difference of energy information and noise level based on clinical image pixel to be corrected is modified sensitivity profile.
Description
Technical field
The present invention relates to field of magnetic resonance imaging more particularly to a kind of coil sensitivity modification methods.
Background technique
In mr imaging technique, image inhomogeneities refers to the different regional areas of identical tissue in the picture, figure
As grey scale pixel value, image statistics feature mean value, variance etc. have relatively large deviation.Image is unevenly in magnetic resonance imaging
Since local coil is there are non-uniform spatial sensitivity, imaging signal is decayed with the distance of coil.It is a kind of relatively conventional
Uniformity correcting method be the method based on coil sensitivity, be that the priori knowledge based on prescan obtains region to be imaged
Coil sensitivity carries out homogeneity correction to image using the sensitivity.The school is based on VTC with uniform coil sensitivity
Spend being distributed it is assumed that basic thought is real by multiplying a property field to the imaging of coil sensitivity profiles non-uniform phased-array coil
Existing homogeneity correction, keeps the uniformity of imaging consistent with the uniformity that VTC is imaged.
The scene that Breast Coil is used alone in the above method has the disadvantage that in routine clinical imaging region, leans on
The signal of nearly Breast Coil unit has a good signal-to-noise ratio, and side (inside the wall of the chest) signal-to-noise ratio far from Breast Coil is then very
Low, tissue signal energy can decay to and reach unanimity and cannot be distinguished with background noise level.This is partially away from coil unit
Tissue regions be usually in galactophore scanning without diagnostic value.According to the principle of homogeneity correction, if the spirit to the region
Sensitivity distribution do not do correcting process (sensitivity profile of coil has corresponding value on each point of entire three-dimensional space,
Therefore whole region have sensitivity profile), the area pixel gray value can be lifted to during homogeneity correction with just
, there is the spot of more strong sand shape, i.e. noise quilt in identical tissue pixels gray value phase same level in normal signal-to-noise ratio region
Shown in the visual effect raised, following Fig. 1 and Fig. 2, Fig. 1 is that uncorrected original image is imaged in Breast Coil, is multiplied by one
Property field realize homogeneity correction after as shown in Fig. 2, through multiplying property field correction after, in figure 2 lower half portion occur it is more strong
The spot of strong sand shape, and this part is the region of not diagnostic value.
Same problem is also present in the scene of spine coil exclusive use, such as the scanning of lumbar vertebrae, thoracic vertebrae.In routine clinical
In imaging region, the signal close to the back of spine coil is with good signal-to-noise ratio, and the side noise far from spine coil
Very lower than then, tissue signal energy can be decayed to and be reached unanimity with background noise level, and cannot be distinguished.
In clinical application, above-mentioned sand shape speckle regions be do not allow it is existing.The prior art is believed using prescan
After breath calculates sensitivity profile, the difference of energy information and noise level based on clinical image pixel to be corrected is to sensitive
Degree distribution is modified.Correction based on clinical image information to be corrected can bring certain algorithm complexity, and for facing
The advanced post-processing (such as DWI) of bed image will cause certain influence.
Summary of the invention
To solve the above-mentioned problems, the present invention provides a kind of coil sensitivity modification method, face without using with to be corrected
The relevant information of bed image, but it is directed to the physical characteristic of coil, it devises sensitive under the scene for coil to be used alone
Degree is distributed modified prioritization scheme.
A kind of coil sensitivity modification method, includes the following steps:
Obtain the distribution of coil three-dimensional sensitibility reciprocal；
Had on coil projecting direction according to coil received signal and obtains one with the physical characteristic apart from monotone decreasing
Effectively projection depth, effective projection depth representing have in coil projecting direction coil reference line to tissue maximum to be imaged
Imitate the distance on areas imaging boundary；
Curve based on effective projection depth to the three-dimensional sensitivity profile of the coil on coil projecting direction
Carry out inhibition amendment.
Preferably, the form of expression of the three-dimensional sensitivity profile of the coil under physical space is the matrix of M*N*P, should
Being distributed on coil projecting direction has M*N curve.
Preferably, the region in effectively projection depth bounds is tissue signal-to-noise ratio height to be imaged and the area for having diagnostic value
Domain, the region beyond effective projection depth is signal-to-noise ratio is low and loses the region of diagnostic value；To beyond effectively projection depth
The coil sensitivity profiles in region carry out inhibition amendment.
Preferably, by following formula to every curve in the three-dimensional sensitivity profile of the coil in coil projection side
Carry out inhibition amendment upwards:
Padj_opt(y)=Padj(y) * γ (y, d)+Sn* (1- γ (y, d))
Wherein, PadjIt (y) is the sensitivity curve before amendment,For the sensitivity curve after amendment, γ
(y, d) is filter function, and y is image pixel coordinates independent variable, and d is effectively to project depth, SnFor the noise factor of setting, instead
It is horizontal to reflect the noise suppressed far from coil one end.
Preferably, use Fermi function as filter γ (y) function:
Wherein function Fermi (y) is window curve, and the parameter t is the window curve smoothing intermediate zone width control coefrficient.
Preferably, the noise factor SnValue range be 0.3~0.8.
Preferably, effective projection depth d=0.005m, the window curve smoothing intermediate zone width control coefrficient t=
0.018, noise factor value Sn=0.6.
Preferably, the coil is spine coil or Breast Coil.
Compared with prior art, the coil sensitivity modification method that the technical program provides, for the physical characteristic of coil
The sensitivity of coil is modified.The efficient diagnosis region that the calibration result of this method can reach in image close to coil obtains
To good homogeneity correction, and good noise suppressed is obtained without diagnostic value region far from coil；It avoids and is using
After pre-scan information calculates sensitivity profile, the difference of energy information and noise level based on clinical image pixel to be corrected
The different complex calculation that sensitivity profile is modified.
Detailed description of the invention
Fig. 1 is uncorrected Breast Coil image；
Fig. 2 is based on the prior art by the Breast Coil image after homogeneity correction；
Fig. 3 is the flow chart of coil sensitivity modification method provided by the invention；
Fig. 4 is Fermi window curve described in one embodiment；
Fig. 5 a is the imaging distribution curve that used VTC coil is scanned in one embodiment；
Fig. 5 b is the imaging distribution curve of Breast Coil used in corresponding diagram 5a embodiment scans；
Fig. 5 c is the sensitibility reciprocal distribution curve based on Fig. 5 a Yu the Breast Coil of Fig. 5 b；
Fig. 6 is the sensitibility reciprocal distribution curve after the technical solution amendment that Fig. 5 C is provided through the invention；
Fig. 7 is based on technical solution of the present invention to the Breast Coil image after spine coil sensitivity amendment；
Fig. 8 is uncorrected spine coil image；
Fig. 9 is based on the prior art by the spine coil image after homogeneity correction；
Figure 10 is based on technical solution of the present invention to the spine coil image after spine coil sensitivity amendment.
Specific embodiment
In the following description, numerous specific details are set forth in order to facilitate a full understanding of the present invention.But the present invention can be with
Much it is different from other way described herein to implement, those skilled in the art can be without prejudice to intension of the present invention the case where
Under do similar popularization, therefore the present invention is not limited to the specific embodiments disclosed below.Secondly, the present invention is carried out using schematic diagram
Detailed description for purposes of illustration only, the schematic diagram is example, should not limit this when describing the embodiments of the present invention herein
Invent the range of protection.
As stated in the background art, the prior art is after calculating sensitivity profile using pre-scan information, based on to be corrected
The energy information of clinical image pixel and the difference of noise level are modified sensitivity profile.Based on clinical figure to be corrected
As the correction of information can bring certain algorithm complexity, and the advanced post-processing (such as DWI) of clinical image can be made
At certain influence.Therefore technical solution of the present invention is proposed without using the coil sensitivity with clinical image relevant information to be corrected
Spend prioritization scheme.
As shown in figure 3, a kind of coil sensitivity modification method, comprising:
Step S10 obtains the distribution of coil three-dimensional sensitibility reciprocal.
The form of expression of the three-dimensional sensitivity profile of the coil under physical space is the matrix of M*N*P, i.e., in coil
Projecting direction (direction y under physical coordinates system) has M*N curve.
Step S20 has on coil projecting direction with the physical characteristic apart from monotone decreasing according to coil received signal
Obtain an effectively projection depth.
Currently, have receive signal on coil projecting direction and have with the coil of the physical characteristic apart from monotone decreasing include
Breast Coil, spine coil etc..
Effective projection depth representing on coil projecting direction, coil reference line to tissue to be imaged it is maximum effectively at
As the distance of range boundary.The coil reference line be it is predetermined, generally, the reference line of Breast Coil is located at mammary gland line
Enclose the position of front end.
Region in effectively projection depth bounds is tissue signal-to-noise ratio height to be imaged and the region for having diagnostic value, is exceeded
Effectively the region of projection depth is signal-to-noise ratio is low and loses the region of diagnostic value.
Priori knowledge based on prescan obtains the coil sensitivity in region to be imaged, is carried out using the sensitivity to image
Homogeneity correction.According to the principle of homogeneity correction, if do not done to the sensitivity profile beyond the effectively region of projection depth
Inhibit correcting process, the area pixel gray value can be lifted to during homogeneity correction and group in normal signal-to-noise ratio region
Knit grey scale pixel value phase same level, the visual effect that the more strong sand shape spot of appearance, i.e. noise are elevated.
Shown in following Fig. 1 and Fig. 2, Fig. 1 is that uncorrected image is imaged in Breast Coil, is realized by multiplying a property field uniform
Property correction after as shown in Fig. 2, after the correction of multiplying property field, there is more strong sand shape spot in 2 lower half portion in figure
Point, and this part is the region of not diagnostic value.In clinical application, above-mentioned sand shape speckle regions are not allow to exist
's.
Therefore, the technical program needs to press down the coil sensitivity profiles curve beyond the effectively region of projection depth
System amendment.
Step S30, based on effective projection depth to the three-dimensional sensitivity profile of the coil in coil projecting direction
Curve carry out inhibition amendment.
Every curve in the three-dimensional sensitivity profile of the coil is carried out in coil projecting direction by following formula
Amendment, if being modified to the curve in every direction y under physical coordinates system:
Padj_opt(y)=Padj(y) * γ (y, d)+Sn* (1- γ (y, d))
Wherein, PadjIt (y) is the sensitivity curve before amendment,For the sensitivity curve after amendment, γ
(y, d) is filter function, and y is image pixel coordinates independent variable, and d is effectively to project depth, SnFor the noise factor of setting, instead
It reflects horizontal far from coil one end noise suppressed.The noise factor value SnValue range be 0.3~0.8.
In one embodiment, as shown in figure 4, using Fermi window curve as filter γ (y) function:
Fermi window curve in formula is smooth to 0 from 1 in the y-direction, and the parameter t is the narrow bandwidth control of curve middle transition
Coefficient processed effectively projects depth d and controls window point of inflexion on a curve position.
In one embodiment, effective projection depth d=0.005m, intermediate zone width control coefrficient t=0.018,
Noise factor Sn=0.6.
Fig. 5 a is that distribution curve is imaged in volume emission coil (VTC), and Fig. 5 b is that distribution curve is imaged in Breast Coil, described
The ratio between VTC imaging distribution curve and Breast Coil imaging distribution curve individually make the sensitivity in scene for Breast Coil
Distribution curve (as shown in Figure 5 c) reciprocal.Breast Coil is open coil, positioned at the unilateral side of tissue when imaging is used alone, i.e.,
Shirtfront side, it is possible to find out tissue regions of the back close to coil, the signal energy of local coil imaging in image 5b
It is higher, and as coordinate is moved far from coil direction along Y-coordinate, signal energy is with a faster velocity attenuation.This causes
Image organizational region, the curved profile of sensitibility reciprocal distribution be one and be similar to linear incremental curve, and far from coil
One end, sensitivity estimation is very high, thus in correction directly using the sensitivity i.e. occur described in background technique
Problem.
The sensitibility reciprocal distribution curve in correction map 5, correction result such as Fig. 6 institute are gone to using the Fermi window curve of such as Fig. 4
Show.In effectively projection depth bounds, the value of sensitivity still maintains original value or close to original value, and effectively projects depth model
Outside enclosing, the value of sensitivity is gradually smooth to the noise factor value an of reduced levels, realizes the effect of noise suppressed.In this method
It can be by adjusting effectively projection depth value d, noise factor value SnAnd window curve smoothing intermediate zone width control coefrficient t, it reaches
To different correction effects.The above parameter, available ideal calibration result are reasonably set.What needs to be explained here is that
The curve of other similar property can also be used in the technical program, such as Gaussian curve, Tukey window curve etc..
The Breast Coil sensitivity optimized using technical solution of the present invention and then progress homogeneity correction, are obtained such as Fig. 7
As a result, compared with Fig. 2, the lower half portion of Fig. 7, i.e. the spot of the sand shape far from Breast Coil unit this portion of tissue
It has disappeared.
Fig. 8 is uncorrected original image after being imaged using spine coil, and Fig. 9 is based on the prior art to spine coil
The image later of homogeneity correction is carried out, there is the spot of apparent sand shape in the side (region far from spine coil) of image,
Figure 10 is to optimize the image obtained after spine coil sensitivity profile, compared with Fig. 9, sand grains using technical solution of the present invention
Shape speckle regions obviously disappear.
The coil sensitivity modification method that the technical program provides, the spirit by being directed to the physical characteristic of coil, to coil
Sensitivity is modified, and the efficient diagnosis region that the calibration result of this method can reach in image close to coil obtains well
Even property correction, and good noise suppressed is obtained without diagnostic value region far from coil.It avoids and is using pre-scan information
After calculating sensitivity profile, the difference of energy information and noise level based on clinical image pixel to be corrected is to sensitivity
It is distributed the complex calculation being modified.
Although present disclosure is as above, present invention is not limited to this.Anyone skilled in the art are not departing from this
It in the spirit and scope of invention, can make various changes or modifications, therefore protection scope of the present invention should be with claim institute
Subject to the range of restriction.
Claims (7)
1. a kind of coil sensitivity modification method, which comprises the steps of:
The three-dimensional sensitivity profile of coil is obtained, the three-dimensional sensitivity profile of the coil is according to the imaging point of volume emission coil
The sensitibility reciprocal distribution curve that the ratio between cloth curve and coil imaging distribution curve determine；
Had on coil projecting direction according to coil received signal and obtains one effectively with the physical characteristic apart from monotone decreasing
Project depth, effective projection depth representing coil projecting direction coil reference line to tissue to be imaged maximum effectively at
As the distance of range boundary；
Curve of the three-dimensional sensitivity profile of the coil on coil projecting direction is carried out based on effective projection depth
Inhibit amendment；
The three-dimensional sensitivity profile of the coil includes a plurality of curve in coil projecting direction, by following formula to the coil
Three-dimensional sensitivity profile in every curve inhibition amendment is carried out on coil projecting direction:
Padj_opt(y)=Padj(y)*γ(y,d)+Sn*(1-γ(y,d))
Wherein, PadjIt (y) is the sensitivity curve before amendment,For the sensitivity curve after amendment, γ (y, d)
For filter function, y is image pixel coordinates independent variable, and d is effectively to project depth, SnFor the noise factor of setting, reflection is far
The noise suppressed of offline circle one end is horizontal.
2. coil sensitivity modification method as described in claim 1, which is characterized in that the three-dimensional sensitivity profile of the coil
The matrix that the form of expression under physical space is M*N*P, this, which is distributed on coil projecting direction, M*N curve.
3. coil sensitivity modification method as described in claim 1, which is characterized in that the area in effectively projection depth bounds
Domain is tissue signal-to-noise ratio height to be imaged and the region for having diagnostic value, and the region beyond effective projection depth is signal-to-noise ratio is low and loses
Go to the region of diagnostic value；Inhibition amendment is carried out to the coil sensitivity profiles beyond the effectively region of projection depth.
4. coil sensitivity modification method as described in claim 1, which is characterized in that use Fermi function as filter
γ (y) function:
Wherein function Fermi (y) is window curve, and the parameter t is the window curve smoothing intermediate zone width control coefrficient.
5. coil sensitivity modification method as claimed in claim 4, which is characterized in that the noise factor SnValue range
It is 0.3~0.8.
6. coil sensitivity modification method as claimed in claim 5, which is characterized in that effective projection depth d=
0.005m, the window curve smoothing intermediate zone width control coefrficient t=0.018, noise factor value Sn=0.6.
7. coil sensitivity modification method as described in claim 1, which is characterized in that the coil is spine coil or mammary gland
Coil.
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| CN1191709A (en) * | 1996-12-30 | 1998-09-02 | 通用电气公司 | Method for correcting inhomogeneity of spatial intensity in acquired MR image |
| JP2003144410A (en) * | 2001-11-13 | 2003-05-20 | Ge Medical Systems Global Technology Co Llc | Fluid quantity measuring device |
| CN1905836A (en) * | 2004-11-12 | 2007-01-31 | 株式会社东芝 | Magnetic resonance imaging apparatus, image data correction apparatus, and image data correction method |
| CN101023867A (en) * | 2006-02-17 | 2007-08-29 | 株式会社东芝 | Data correction apparatus, data correction method, magnetic resonance imaging apparatus and X-ray CT apparatus |
| CN102548472A (en) * | 2010-08-16 | 2012-07-04 | 株式会社东芝 | Magnetic resonance imaging apparatus |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| JP2008229277A (en) * | 2007-03-23 | 2008-10-02 | Ge Medical Systems Global Technology Co Llc | Magnetic resonance imaging device, magnetic resonance imaging method, and sensitivity distribution measuring device |
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Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1191709A (en) * | 1996-12-30 | 1998-09-02 | 通用电气公司 | Method for correcting inhomogeneity of spatial intensity in acquired MR image |
| JP2003144410A (en) * | 2001-11-13 | 2003-05-20 | Ge Medical Systems Global Technology Co Llc | Fluid quantity measuring device |
| CN1905836A (en) * | 2004-11-12 | 2007-01-31 | 株式会社东芝 | Magnetic resonance imaging apparatus, image data correction apparatus, and image data correction method |
| CN101023867A (en) * | 2006-02-17 | 2007-08-29 | 株式会社东芝 | Data correction apparatus, data correction method, magnetic resonance imaging apparatus and X-ray CT apparatus |
| CN102548472A (en) * | 2010-08-16 | 2012-07-04 | 株式会社东芝 | Magnetic resonance imaging apparatus |
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Address after: 201815 No. 1180 Xingxian Road, Jiading Industrial Zone, Jiading District, Shanghai Patentee after: Shanghai Lianying Medical Technology Co., Ltd Address before: 201815 No. 1180 Xingxian Road, Jiading Industrial Zone, Jiading District, Shanghai Patentee before: SHANGHAI UNITED IMAGING HEALTHCARE Co.,Ltd. |
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Address after: 201807 2258 Chengbei Road, Jiading District, Shanghai Patentee after: Shanghai Lianying Medical Technology Co.,Ltd. Address before: 201815 No. 1180 Xingxian Road, Jiading Industrial Zone, Jiading District, Shanghai Patentee before: Shanghai Lianying Medical Technology Co.,Ltd. |