CN106872921A - MR imaging method and device - Google Patents
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- CN106872921A CN106872921A CN201710047816.3A CN201710047816A CN106872921A CN 106872921 A CN106872921 A CN 106872921A CN 201710047816 A CN201710047816 A CN 201710047816A CN 106872921 A CN106872921 A CN 106872921A
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- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
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- A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
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Abstract
The application provides a kind of MR imaging method.The MR imaging method includes：From echo-signal of the receiving coil array acquisition with position encoded information, the receiving coil array includes some coil units；Process the echo-signal and obtain the drop shadow intensity's signal with spatial positional information；The center of the receiving coil array is determined by gravity model appoach or correlation method according to drop shadow intensity's signal；The coil unit of the receiving coil array is selected according to the center；And the drop shadow intensity's signal reconstruction image obtained according to the echo-signal of the coil unit selected.The application also provides a kind of MR imaging apparatus.
Description
Technical field
The application is related to a kind of medical apparatus and instruments, more particularly to a kind of MR imaging method and device.
Background technology
Magnetic resonance imaging (Magnetic Resonance Imaging, MRI) be in modern medical service iconography it is main into
One of image space formula.It is one kind of fault imaging, high to soft tissue resolution, to the "dead" infringement of human body.Magnetic resonance imaging
Basic functional principle be：Using electromagnetic induction phenomenon by the Hydrogen Proton in RF excited exciting human, carried out using gradient fields
It is position encoded, the electromagnetic signal with positional information then is received with receiving coil, it is final to reconstruct image using Fourier transformation
Information.Conventional MRI imaging is general to carry out signal acquisition using single channel body coil or array coil, and array coil can be with
For improving signal to noise ratio, array coil can be fixed on one's sick bed, it is also possible to be freely placed at person under inspection, be such as placed on and received
Inspection person's imaging region interested.
In magnetic resonance imaging, signal to noise ratio is very important.In order to obtain optimum signal-noise ratio, it usually needs coil is put
Put near imaging region.If from imaging region farther out, coil will be unable to receive the signal of imaging region and leads coil
Signal to noise ratio is caused to be deteriorated.It is optimization scanning process with the development of array coil, it is to avoid more emat coil or to line in scanning process
Circle is put again, and nowadays high channel, large-scale many array coils are widely applied.This certainly will cause can only have partial line
Coil unit just possesses compared with high s/n ratio, and other then can not only reduce the image of imaging region away from the coil unit of imaging region
Signal to noise ratio, or even aliasing artefacts can be introduced.
The content of the invention
In view of this, the one side of the application provides a kind of MR imaging method.The MR imaging method includes：
From echo-signal of the receiving coil array acquisition with position encoded information, the receiving coil array includes some coil lists
Unit；Process the echo-signal and obtain the drop shadow intensity's signal with spatial positional information；It is logical according to drop shadow intensity's signal
Cross gravity model appoach or correlation method determines the center of the receiving coil array；The reception is selected according to the center
The coil unit of coil array；And the drop shadow intensity's signal reconstruction obtained according to the echo-signal of the coil unit selected
Image.
Further aspect of the application provides a kind of MR imaging apparatus.The MR imaging apparatus include：Receive line
Circle array, including some coil units；Receiving unit, for carrying position encoded information from the receiving coil array acquisition
Echo-signal；Processing unit, the drop shadow intensity's signal with spatial positional information is obtained for processing the echo-signal, according to
Drop shadow intensity's signal determines the center of the receiving coil array by gravity model appoach or correlation method, and according to described
Center selects the coil unit of the receiving coil array；And image reconstruction unit, for according to the line selected
Drop shadow intensity's signal reconstruction image that the echo-signal of coil unit is obtained.
Brief description of the drawings
Fig. 1 is the schematic diagram of one embodiment of MR imaging apparatus；
Fig. 2 is the schematic diagram of one embodiment of the receiving coil array of MR imaging apparatus；
Fig. 3 is the flow chart of one embodiment of MR imaging method；
Fig. 4 is the curve map of one embodiment of drop shadow intensity's signal；
Fig. 5 is the curve map of drop shadow intensity's signal and one embodiment of its autocorrelation signal.
Specific embodiment
Here exemplary embodiment will be illustrated in detail, its example is illustrated in the accompanying drawings.Following description is related to
During accompanying drawing, unless otherwise indicated, the same numbers in different accompanying drawings represent same or analogous key element.Following exemplary embodiment
Described in implementation method do not represent all implementation methods consistent with the application.Conversely, they be only with it is such as appended
The example of the consistent apparatus and method of some aspects described in detail in claims, the application.
It is the purpose only merely for description specific embodiment in term used in this application, and is not intended to be limiting the application.
Unless otherwise defined, technical term used in this application or scientific terminology should be has general skill in art of the present invention
The ordinary meaning that the personage of energy is understood.The class such as the " one " used in present specification and claims or " one "
Do not indicate that quantity is limited like word yet, but expression has at least one.The similar word such as " including " or "comprising" means
Now " including " or "comprising" before element or object cover and appear in " including " or "comprising" presented hereinafter unit
Part or object and its equivalent, it is not excluded that other elements or object.The similar word such as " connection " or " connected " is not
It is defined in physics or machinery connection, and electrical connection can be included, either directly still indirectly.At this
" one kind ", " described " and " being somebody's turn to do " of singulative used in application specification and appended claims is also intended to include many
Number form formula, unless context clearly shows that other implications.It is also understood that term "and/or" used herein refers to simultaneously
May be combined comprising one or more associated any or all of project listed.
Fig. 1 show the schematic diagram of the MR imaging apparatus 10 of one embodiment.MR imaging apparatus 10 include magnetic
Body component 12, with a cavity 13, for housing the person under inspection lain on supporting bed 18.Magnet assembly 12 is included for generating
The main magnet 14 of magnetostatic field, for generate in X direction, the gradient coil 15 of the gradient magnetic of Y-direction, Z-direction and for launching
The radio-frequency sending coil 16 of radio frequency (RF) pulse.Main magnet 14 generates magnetostatic field typically with superconducting coil.Main magnet 14
Permanent magnet or resistive magnet can also be used.In the case of using superconducting coil, main magnet 14 is included for cooling down superconducting line
The cryostat of the cooling system of circle, such as liquid helium cooling.
MR imaging apparatus 10 also include receiving coil array 17, for receiving echo-signal.Echo-signal can be put
Big device 19 amplifies.In the illustrated embodiment, MR imaging apparatus 10 also include coil handover module 21, coil handover module 21
Receiving coil array 17 is connected to by amplifier 19, for switching the coil unit of receiving coil array 17.Receiving unit 22
For gathering echo-signal.In the illustrated embodiment, receiving unit 22 is connected to coil handover module 21, receiving unit 22 with connect
When the passage for receiving the coil unit of coil array 17 is opened by coil handover module 21, the echo-signal of coil unit output can
Received with by receiving unit 22, otherwise echo-signal can not be received by receiving unit 22.Can be by by coil handover module 21
Unwanted echo-signal is masked.Can be received than the single of receiving unit 22 in the coil unit number of receiving coil array 17
Echo-signal number it is many when, receiving unit 22 can by coil handover module 21 several times receiving coil unit export return
Ripple signal.Coil handover module 21 can receive the instruction that master control unit 32 sends by coil interface unit 24.Coil switches
Module 21 can respond instruction that master control unit 32 sends to switch the coil unit of receiving coil array 17.
The echo-signal of collection is supplied to processing unit 23 to be processed by receiving unit 22.Processing unit 23 can be processed back
Ripple signal generation drop shadow intensity signal.Drop shadow intensity's signal is supplied to image reconstruction unit 31, image reconstruction by processing unit 23
Unit 31 is according to drop shadow intensity's signal reconstruction image.In the illustrated embodiment, processing unit 23 is independently of master control unit 32.
In another embodiment, processing unit 23 can be integrated in master control unit 32.
MR imaging apparatus 10 also include radio frequency control unit 25, gradient control unit 26, supporting bed control unit 27
With sequence control unit 28.Radio frequency control unit 25 controls radio-frequency sending coil 16 to be penetrated to launch by radio-frequency power amplifier 29
Frequency pulse.The instruction that radio frequency control unit 25 can respond master control unit 32 sends pulse signal, and radio-frequency power amplifier 29 will
The pulse signal carries out power amplification, and radio-frequency sending coil 16 is supplied to afterwards, to launch radio-frequency pulse.
Gradient control unit 26 controls gradient coil 15 by gradient magnetic (such as X side by gradient power amplifier 30
To gradient magnetic, the gradient magnetic of Y-direction and Z-direction gradient magnetic) be superimposed upon on magnetostatic field.Gradient magnetic is to subject
Interior magnetic spin is spatially encoded.Typically, multiple gradient coils 15 are included along three orthogonal intersection space directions (X-direction, Y sides
To and Z-direction) three single gradient coils being spatially encoded.Gradient control unit 26 can respond master control unit 32
Instruct to control gradient coil 15.
Supporting bed control unit 27 is used for controlling the motion of supporting bed 18.Sequence control unit 28 is used for generating gradient pulse
With the sequence of radio-frequency pulse.Master control unit 32 also can control supporting bed control unit 27 and sequence control unit 28, and it can bear
Duty overall control, input unit 33, such as keyboard, mouse, touch-screen etc. can be received, there is provided information.Display device 34 can use
To show data, parameter, the waveform etc. of the image of reconstruction, measurement.
The master control unit 32 of MR imaging apparatus 10, processing unit 23, image reconstruction unit 31, radio frequency control unit
25th, gradient control unit 26, supporting bed control unit 27 and sequence control unit 28 can be realized by software, it is also possible to be passed through
The mode of hardware or software and hardware combining is realized.MR imaging apparatus 10 can also include other elements (not shown), for example, deposit
Reservoir.Device embodiment described above is only schematical, wherein the unit illustrated as separating component can be with
It is or may not be physically separate, the part shown as unit can be or may not be physical location,
A place is may be located at, or can also be distributed on multiple NEs.Can select according to the actual needs wherein
Some or all of part realize the purpose of application scheme.
Fig. 2 show the schematic diagram of the receiving coil array 17 of one embodiment.Two groups of coil arrays 17 are shown in Fig. 2,
Placed near subject 35, respectively positioned at the both sides up and down of subject 35.If two groups of receiving coil arrays 17 include main line respectively
Coil unit 1-4 and 5-8, coil unit 1-8 is RF receiving coil, sense of the coil sections unit 1,2 and 5,6 near subject 35
Imaging region (or area-of-interest (ROI)) 36, such as chest area in figure of interest.Other coil units 3,4 and 7,8
Further away from imaging region 36.The signal to noise ratio of the echo-signal that coil unit 1,2 and 5,6 is received is higher, coil unit 3,4 and 7,8
The signal to noise ratio of the echo-signal of reception is relatively low, therefore coil unit 1,2 and 5,6 is the coil unit for needing to be selected.Fig. 2 is only
It is a nonrestrictive example, in other embodiments, receiving coil array 17 can include the coil unit of other numbers,
Coil unit can also form the array of multiple rows of multirow with shape array in a row.
Fig. 3 show the flow chart of the MR imaging method 38 of one embodiment.MR imaging method 38 includes step
Rapid 381-385.Wherein,
In step 381, from echo-signal of the receiving coil array acquisition with position encoded information.
Reading location coding is carried out to X-direction, Y-direction and/or Z-direction using gradient is read, the echo-signal of collection can include X
The position encoded information of direction, Y-direction and/or Z-direction.In one embodiment, when receiving coil array (is led along Z-direction
The length direction of magnet) arrangement when, collection with the position encoded information of Z-direction echo-signal.In another embodiment, when
When receiving coil array is arranged along Y-direction (i.e. perpendicular to the left and right directions of Z-direction), collection carries the position encoded information of Y-direction
Echo-signal.In yet another embodiment, when receiving coil array is along Z-direction and the two dimension arrangement of Y-direction both direction, adopt
Echo-signal of the collection with Z-direction and the position encoded information of Y-direction.
In step 382, treatment echo-signal obtains the drop shadow intensity's signal with spatial positional information.
The echo-signal of collection is carried out into Fourier transformation, modulus is worth to drop shadow intensity's signal.What echo-signal was carried
Position encoded information obtains spatial positional information after being fourier transformed.In one embodiment, treatment is compiled with Z-direction position
The echo-signal of code information, obtains the drop shadow intensity's signal with Z-direction spatial positional information.In another embodiment, locate
Echo-signal of the reason with the position encoded information of Y-direction, obtains the drop shadow intensity's signal with Y-direction spatial positional information.
In further embodiment, echo-signal of the treatment with Z-direction and the position encoded information of Y-direction is obtained and carries Z-direction and Y side
To drop shadow intensity's signal of spatial positional information.
In step 383, the center of receiving coil array is determined by gravity model appoach or correlation method according to drop shadow intensity's signal
Position.
In one embodiment, the center of receiving coil array is determined by gravity model appoach according to drop shadow intensity's signal.
Wherein it is determined that the position of centre of gravity of drop shadow intensity's signal, and the center of receiving coil array is determined according to position of centre of gravity.
The locus C of receiving coil arrayLCan be expressed as expression formula (1)：
Wherein, n is the data point position of drop shadow intensity's signal curve, and S (n) is the corresponding drop shadow intensity's value in nth point position,
N is the maximum number strong point position of drop shadow intensity's signal curve, and Δ d is the space length between the position of consecutive number strong point.In the reality
Apply in example, drop shadow intensity's signal curve is relation of drop shadow intensity's value relative to data point position.Drop shadow intensity's value can be real
Drop shadow intensity's value on border, or normalized drop shadow intensity.
In the present embodiment, the center-of-gravity value for asking weight to obtain drop shadow intensity's signal is carried out to drop shadow intensity's signal, and is obtained
The corresponding data point position of center-of-gravity value.The data point position is the position of centre of gravity of data point markers, and the position of centre of gravity in space is number
The position of centre of gravity of strong point mark is multiplied by the space length Δ d between the position of consecutive number strong point.Center-of-gravity value is used as drop shadow intensity value S
N (), corresponding data point position is brought into expression formula (1) as n to carry out calculating the locus C for obtaining receiving coil arrayL,
The locus C that this is calculatedLIt is the center of receiving coil array.The center of receiving coil array is to be close to imaging
The center of the coil unit in region, it is probably the geometric center of receiving coil array, it is also possible to be not receiving coil array
Geometric center.
In another embodiment, drop shadow intensity's signal curve can be pass of drop shadow intensity's value relative to locus
System, locus is the space length Δ d that data point position n is multiplied by between the position of consecutive number strong point.Drop shadow intensity's signal is entered
Row asks weight to obtain the center-of-gravity value of drop shadow intensity's signal, and obtains the corresponding locus of center-of-gravity value, and the locus is space
Position of centre of gravity.Further the position of centre of gravity according to center-of-gravity value and space calculates the center of receiving coil array.
With reference to Fig. 4 is referred to, Fig. 4 show the oscillogram of drop shadow intensity's signal of one embodiment.Abscissa in Fig. 4 is
Locus, ordinate is normalized drop shadow intensity.Can determine that the center of receiving coil array is 317 by gravity model appoach
Millimeter.In other embodiments, curve of the drop shadow intensity relative to data point position can be generated.
In one embodiment, according to the drop shadow intensity's signal with Z-direction spatial positional information, determined by gravity model appoach
Receiving coil array is in the center of Z-direction.In another embodiment, according to the throwing with Y-direction spatial positional information
Shadow strength signal, receiving coil array center in the Y direction is determined by gravity model appoach.In a further embodiment, according to
Drop shadow intensity's signal of Z-direction and Y-direction spatial positional information with receiving coil array, determines to receive line by gravity model appoach
Circle array is in Z-direction and the center of Y-direction.
In another embodiment, the centre bit of receiving coil array is determined by correlation method according to drop shadow intensity's signal
Put.Wherein it is determined that the autocorrelation signal of drop shadow intensity's signal, the position where determining the maximum of autocorrelation signal, and according to
Position where maximum determines the center of receiving coil array.Position where maximum can be data point position,
It can also be locus.
Autocorrelation signal can be determined by expression formula (2)：
Wherein, n is the data point position in drop shadow intensity's signal curve, and S (n) is the corresponding drop shadow intensity in nth point position
Value, N is the maximum number strong point position of drop shadow intensity's signal curve, and m is the position that auto-correlation is slided, and S (n-m) is the n-th-m points position
Put corresponding drop shadow intensity's value.
In the present embodiment, the data point position corresponding to the maximum and maximum of autocorrelation signal, the data are determined
The point space length Δ d that is multiplied by between the position of consecutive number strong point of position can obtain maximum where locus, the space bit
It is set to the center of receiving coil array.
With reference to Fig. 5 is referred to, Fig. 5 show drop shadow intensity's signal of one embodiment and the oscillogram of its autocorrelation signal.
Abscissa in Fig. 5 is locus, and ordinate is normalized intensity.Curve 51 is drop shadow intensity's signal curve, curve 52
It is autocorrelation signal curve.Can determine that center is 310 millimeters by correlation method.In other embodiments, may be used
Curve of the drop shadow intensity relative to data point position is generated, and autocorrelation signal is relative to the curve of data point position.
In one embodiment, according to the drop shadow intensity's signal with Z-direction spatial positional information, the drop shadow intensity is determined
The autocorrelation signal of signal, asks for the maximum value position of autocorrelation signal to determine centre bit of the receiving coil array in Z-direction
Put.In another embodiment, according to the drop shadow intensity's signal with Y-direction spatial positional information, determine that the drop shadow intensity believes
Number autocorrelation signal, the maximum value position of autocorrelation signal is asked for determine receiving coil array centre bit in the Y direction
Put.In a further embodiment, according to the drop shadow intensity's signal with Z-direction and Y-direction spatial positional information, the projection is determined
The autocorrelation signal of strength signal, asks for the maximum value position of autocorrelation signal to determine receiving coil array in Z-direction and Y
The center in direction.
In step 384, the coil unit of receiving coil array is selected according to center.
The determination of center provides foundation to the selection of coil unit.Optionally at center coil unit and
The neighbouring coil unit of coil unit in center.Imaging region that can be in practical application selects to be close to imaging
The coil unit in region.So as to reject the coil unit for reducing signal noise ratio (snr) of image and/or influence picture quality.
In step 385, drop shadow intensity's signal reconstruction image that the echo-signal according to the coil unit selected is obtained.
The echo-signal that the coil unit selected is received carries out Fourier transformation, and modulus is worth to drop shadow intensity's signal,
Drop shadow intensity's signal is used for reconstruction image.The echo-signal of other coil units is shielded, and the signal to noise ratio of such image is higher.
The action of MR imaging method 38 is illustrated in modular form, the sequencing and module of the module shown in figure
In action division be not limited to diagram embodiment.For example, module can be carried out in a different order；In one module
Action or multiple modules can be split as with the combination of actions in another module.In certain embodiments, in figure magnetic is total to
Shake imaging method 38 the step of before, among or may include other steps afterwards.
MR imaging apparatus 10 shown in Fig. 1 can be used to perform MR imaging method 38.Receiving unit 22 be used for from
Echo-signal of the collection with position encoded information of receiving coil array 17.Processing unit 23 is used for processing echo-signal acquisition band
There is drop shadow intensity's signal of spatial positional information, receiving coil is determined by gravity model appoach or correlation method according to drop shadow intensity's signal
The center of array 17, and the coil unit of receiving coil array 17 is selected according to center.Image reconstruction unit 31 is used
Carry out the drop shadow intensity's signal reconstruction image obtained according to the echo-signal of the coil unit selected.
In one embodiment, processing unit 23 is used for determining the position of centre of gravity of drop shadow intensity's signal, and according to center of gravity position
Put the center for determining receiving coil array 17.In another embodiment, processing unit 23 is used for determining that drop shadow intensity believes
Number autocorrelation signal, the position where determining the maximum of autocorrelation signal, and position according to where maximum determines to connect
Receive the center of coil array 17.
In one embodiment, receiving unit 22 is used for gathering the echo-signal with the position encoded information of Z-direction, processes
Unit 23 is used for processing echo-signal projection of the acquisition with Z-direction spatial positional information with the position encoded information of Z-direction
Strength signal.In another embodiment, receiving unit 22 is used for gathering the echo-signal with the position encoded information of Y-direction,
Processing unit 23 is used for processing the echo-signal acquisition with the position encoded information of Y-direction and carries Y-direction spatial positional information
Drop shadow intensity's signal.In a further embodiment, receiving unit 22 is used for gathering with Z-direction and the position encoded information of Y-direction
Echo-signal, processing unit 23 is used for processing echo-signal with Z-direction and the position encoded information of Y-direction and obtains with Z
Direction and drop shadow intensity's signal of Y-direction spatial positional information.
Receiving unit 22 can be used to the step of performing MR imaging method 38 381, and processing unit 23 can be used to perform step
Rapid 382-384, image reconstruction unit 31 can be used to perform step 385.Receiving unit 22, processing unit 23 and image reconstruction unit
31 concrete function and the implementation process of effect specifically refer to the implementation process of correspondence step in above-mentioned MR imaging method 38.
The preferred embodiment of the application is the foregoing is only, is not used to limit the application, all essences in the application
Within god and principle, any modification, equivalent substitution and improvements done etc. should be included within the scope of the application protection.
Claims (10)
1. a kind of MR imaging method, it is characterised in that：It includes：
From echo-signal of the receiving coil array acquisition with position encoded information, the receiving coil array includes some coils
Unit；
Process the echo-signal and obtain the drop shadow intensity's signal with spatial positional information；
The center of the receiving coil array is determined by gravity model appoach or correlation method according to drop shadow intensity's signal；
The coil unit of the receiving coil array is selected according to the center；And
Drop shadow intensity's signal reconstruction image that echo-signal according to the coil unit selected is obtained.
2. MR imaging method as claimed in claim 1, it is characterised in that：The centre bit for determining receiving coil array
The step of putting includes：Determine the position of centre of gravity of drop shadow intensity's signal, and the reception line is determined according to the position of centre of gravity
Enclose the center of array.
3. MR imaging method as claimed in claim 1, it is characterised in that：The centre bit for determining receiving coil array
The step of putting includes：Determine the autocorrelation signal of drop shadow intensity's signal, the position where determining the maximum of the autocorrelation signal
Put, and position according to where the maximum determines the center of the receiving coil array.
4. MR imaging method as claimed in claim 1, it is characterised in that：The step of collection echo-signal, includes adopting
The step of echo-signal of the collection with the position encoded information of Z-direction, acquisition drop shadow intensity signal, includes that treatment carries Z-direction
The echo-signal of position encoded information obtains the drop shadow intensity's signal with Z-direction spatial positional information.
5. the MR imaging method as described in claim 1 or 4, it is characterised in that：The step of collection echo-signal, wraps
The step of including echo-signal of the collection with the position encoded information of Y-direction, the acquisition drop shadow intensity signal includes that treatment carries Y
The echo-signal of the position encoded information in direction obtains the drop shadow intensity's signal with Y-direction spatial positional information.
6. a kind of MR imaging apparatus, it is characterised in that：It includes：
Receiving coil array, including some coil units；
Receiving unit, for carrying the echo-signal of position encoded information from the receiving coil array acquisition；
Processing unit, obtains the drop shadow intensity's signal with spatial positional information, according to described for processing the echo-signal
Drop shadow intensity's signal determines the center of the receiving coil array by gravity model appoach or correlation method, and according to the center
Position selects the coil unit of the receiving coil array；And
Image reconstruction unit, for drop shadow intensity's signal reconstruction that the echo-signal according to the coil unit selected is obtained
Image.
7. MR imaging apparatus as claimed in claim 6, it is characterised in that：The processing unit is used for determining the projection
The position of centre of gravity of strength signal, and the center of the receiving coil array is determined according to the position of centre of gravity.
8. MR imaging apparatus as claimed in claim 6, it is characterised in that：The processing unit is used for determining drop shadow intensity
The autocorrelation signal of signal, the position where determining the maximum of the autocorrelation signal, and according to where the maximum
Position determines the center of the receiving coil array.
9. MR imaging apparatus as claimed in claim 6, it is characterised in that：The receiving unit is used for gathering with Z side
To the echo-signal of position encoded information, the processing unit is used for processing the echo-signal with the position encoded information of Z-direction
Obtain the drop shadow intensity's signal with Z-direction spatial positional information.
10. MR imaging apparatus as described in claim 6 or 9, it is characterised in that：The receiving unit is used for gathering carrying
The echo-signal of the position encoded information of Y-direction, the processing unit is used for processing the echo letter with the position encoded information of Y-direction
Number obtain with Y-direction spatial positional information drop shadow intensity's signal.
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| CN108663640A (en) * | 2018-05-09 | 2018-10-16 | 上海东软医疗科技有限公司 | A kind of magnetic resonance coil method for determining position and device |
| CN108846843A (en) * | 2018-04-03 | 2018-11-20 | 南昌奇眸科技有限公司 | A kind of image characteristic extracting method |
| CN110095741A (en) * | 2019-04-30 | 2019-08-06 | 上海东软医疗科技有限公司 | Magnetic resonance coil method for determining position, device and magnetic resonance imaging system |
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| US20040135579A1 (en) * | 2001-02-23 | 2004-07-15 | Masahiro Takizawa | Magnetic resonance imaging apparatus and method |
| US20080007263A1 (en) * | 2006-07-06 | 2008-01-10 | Kabushiki Kaisha Toshiba | Magnetic resonance imaging apparatus |
| US20110006766A1 (en) * | 2008-03-14 | 2011-01-13 | Koninklijke Philips Electronics N.V. | Coil selection for parallel magnetic resonance imaging |
| CN101869478A (en) * | 2009-04-24 | 2010-10-27 | 株式会社东芝 | MR imaging apparatus and radio-frequency coil |
| CN102068254A (en) * | 2009-11-20 | 2011-05-25 | Ge医疗系统环球技术有限公司 | Magnetic resonance imaging apparatus |
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| CN108846843A (en) * | 2018-04-03 | 2018-11-20 | 南昌奇眸科技有限公司 | A kind of image characteristic extracting method |
| CN108663640A (en) * | 2018-05-09 | 2018-10-16 | 上海东软医疗科技有限公司 | A kind of magnetic resonance coil method for determining position and device |
| CN108663640B (en) * | 2018-05-09 | 2021-07-13 | 上海东软医疗科技有限公司 | Method and device for determining position of magnetic resonance coil |
| CN110095741A (en) * | 2019-04-30 | 2019-08-06 | 上海东软医疗科技有限公司 | Magnetic resonance coil method for determining position, device and magnetic resonance imaging system |
| CN110095741B (en) * | 2019-04-30 | 2021-09-28 | 上海东软医疗科技有限公司 | Magnetic resonance coil position determining method and device and magnetic resonance imaging system |
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