CN102188245B - System for fat suppression in obtaining of MR image - Google Patents
System for fat suppression in obtaining of MR image Download PDFInfo
- Publication number
- CN102188245B CN102188245B CN 201110064406 CN201110064406A CN102188245B CN 102188245 B CN102188245 B CN 102188245B CN 201110064406 CN201110064406 CN 201110064406 CN 201110064406 A CN201110064406 A CN 201110064406A CN 102188245 B CN102188245 B CN 102188245B
- Authority
- CN
- China
- Prior art keywords
- gradient
- magnetic field
- pulse
- section
- fat
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Landscapes
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
The invention relates to a system for fat suppression in obtaining of MR image, comprising: an RF signal generator for generating the RF pulses in an MR pulse sequence, including an RF excitation pulse and an RF re-focusing pulse after the RF excitation pulse, using one or more RF pulses for an echo signal structure. A magnetic field slice selection gradient generator generates two different slice selection magnetic field gradients to be used together with the RF excitation pulse and the RF re-focusing pulse correspondingly, wherein the first and second slice selection magnetic field gradients are substantially different in amplitude. An MR imaging control unit controls the obtaining of MR imaging data substantially suppressed in fat signal using the generated RF signals and the different slice selection magnetic field gradients.
Description
Cross reference
This is to be 61/314,653 non-provisional application by the provisional application sequence number that V. Deshpande submitted on March 17th, 2010.
Technical field
The present invention relates to be used for carrying out the system that fat signal suppresses in the MR imaging.
Background technology
Diffusion Imaging use spin echo EPI(echo-planar imaging in health and mammary gland MR application) pulse train is carried out.Can use dual reunion Jiao or standard Stejskal Tanner disperse scheme (single focusing) to obtain data.Often be desirably in and suppress fat signal in such obtaining, because the fat signal of Yi Zhiing does not cause space displacement and ghost image in the resulting image.The known method that is used for fat suppression is included in the EPI(echo-planar imaging) use before the driving pulse pulse of spectral selectivity fat suppression, spectral selectivity partial inversion to recover any of (SPIR) or frequency spectrum adiabatic inversion pulse (SPAIR).The water excitation is the another kind of option that suppresses fat signal.Known method relies on the field B0 of relative homogeneity to obtain good fat suppression.If there is change in B0, then above method can't obtain good fat suppression.System has solved fat suppression and the relevant issues of improving in the MR Image Acquisition in accordance with the principles of the present invention.
Summary of the invention
A kind of system has improved the fat suppression in the MR Image Acquisition of using MR pulse train, this MR pulse train uses one or more RF pulses to come RF pulse (lower bandwidth RF pulse) as EPI to form echo (for example spin echo or excite echo) and different section selection gradient amplitude, select the gradient counter-rotating together with section, improve the fat suppression in spin echo EPI Diffusion Imaging.A kind ofly be used for carrying out the system that fat signal suppresses and comprise the RF signal generator in the MR imaging, be used to generate the RF pulse of spin echo signal structure (formation) form, comprise RF driving pulse and the RF after the described RF driving pulse burnt pulse of meeting again.The magnetic field section is selected gradient generator to generate the first and second different sections and is selected magnetic field gradient, be used for respectively the corresponding together use of burnt pulse of meeting again with RF driving pulse and RF, this first and second different section selects magnetic field gradient to have different substantially amplitudes and/or polarity.Obtaining of the MR imaging data that MR imaging control unit uses the RF pulse generated and different sections to select magnetic field gradient to guide to have suppressed fat signal substantially.
Description of drawings
Fig. 1 illustrates and is used in accordance with the principles of the present invention carrying out the system that fat signal suppresses in the MR imaging.
Fig. 2 illustrates indication in accordance with the principles of the present invention, how use different sections to select gradient to obtain the diagram that fat signal suppresses for the excitation and the burnt pulse of meeting again.
Fig. 3 illustrates indication in accordance with the principles of the present invention, how use different sections to select gradient and use through the section of counter-rotating for the burnt pulse of meeting again to select gradient to obtain the diagram that fat signal suppresses for the excitation and the burnt pulse of meeting again.
Fig. 4 illustrates the pulse train that improved fat suppression is provided in accordance with the principles of the present invention.
The MRI image that Fig. 5 illustrates in accordance with the principles of the present invention, utilizes following (a)-(c) scheme to obtain: (a) standard fat suppression scheme; (b) fat suppression of the gradient counter-rotating of gradient is selected in the section of the burnt pulse of utilization reunion; And (c) fat suppression that the section of burnt pulse selects the gradient counter-rotating of gradient and use low bandwidth driving pulse (driving pulse of gradient is selected in just low section) of meeting again.
Fig. 6 illustrates in accordance with the principles of the present invention, by the flow chart that is used for carrying out the process that system that fat signal suppresses carries out in the MR imaging.
The specific embodiment
A kind of system improves the fat suppression in the MR Image Acquisition of using MR pulse train, and this MR pulse train uses one or more RF pulses to form echo and low bandwidth excitation RF pulse.This system advantageously uses different sections to select gradient amplitude to the RF pulse (being also referred to as the low bandwidth excitation) of EPI, selects the gradient counter-rotating together with section, improves the fat suppression in the spin echo EPI Diffusion Imaging.When proton spin turns back to that they are had after initial excitation RF pulse identical start-phase, use the RF burnt pulse of meeting again.Spin-echo sequence uses for example 180 ° of pulses to generate signal echo with the burnt proton spin of meeting again, and gradin-echo uses the burnt gradient of meeting again to maximize remaining cross magnetization.
Fig. 1 illustrates the system 10 that is used to carry out the MR imaging that fat signal suppresses.System 10 is used for signal with spin echo and generates the fat suppression of improving pulse train.In one embodiment, this system uses spin echo disperse EPI sequence.Have the excitation and the burnt pulse of meeting again that gradient is selected in different section by use, for example, improve fat suppression by using the burnt pulse of meeting again of low bandwidth EPI excitation RF pulse and high bandwidth.Alternately, can use the burnt pulse of meeting again of high bandwidth driving pulse and low bandwidth.The section of these two pulses selects gradient amplitude advantageously different.
Basic field magnet 1 generates constant in time high-intensity magnetic field, and with the polarization or the aligning of the nuclear spin of the inspection area that is used for object, the inspection area of described object is such as the part of the human body of for example examine.The high homogeneity of the required main field of magnetic resonance measurement is provided in spherical measurement volumes M, and this sphere measurement volumes M for example is that the part with the human body of examine is incorporated into volume wherein.In order to satisfy homogeneity needs and especially constant influence in order to eliminate, in position locate to install the shimming plate of making by ferromagnetic material.Become influence when eliminating by shim coil 2, this shim coil 2 is controlled by shim current source 15.
In main field 1, use by for example three cylindrical gradient coil system 3 that winding constitutes.Provide electric current by amplifier 14 to each winding, so that on the respective direction of cartesian coordinate system, generate the linear gradient field.First winding of gradient fields system 3 is created on the gradient G on the x direction
x, second winding is created on the gradient G on the y direction
y, and the tertiary winding is created on the gradient G on the z direction
zEach amplifier 14 comprises digital to analog converter, and this digital to analog converter generates gradient pulse by sequence controller 18 controls between in due course.
Location radio frequency (RF) coil 4 in gradient fields system 3, these radio frequencies (RF) coil 4 will be converted to alternating magnetic field by the radio-frequency pulse that radio-frequency power amplifier 16 is launched via multiplexer 6, so that the nuclear spin in the zone of the nuclear in the zone of excitation examine object or examine object and aligning examine object or examine object.In one embodiment, RF coil 4 comprises whole along the subclass of a plurality of RF coils of arranging corresponding to the length segmentation of the volume M of patient's length or a plurality of basically RF coils.In addition, each section RF coil of coil 4 comprises a plurality of RF coils, and described a plurality of RF coils provide by the parallel RF view data that is used to generate single MR image.Use the RF pulse signal to RF coil 4, RF coil 4 produces magnetic field pulse in response, described magnetic field pulse is with spin half-twist or Rotate 180 ° so-called to be used for " spin echo " imaging of the proton in the health of imaging, or rotation is less than or equal to 90 ° angle so-called to be used for " gtadient echo " imaging.In response to applied RF pulse signal, RF coil 4 receives the MR signals, just when the proton of health underexcitation turns back to equilibrium locations by static and gradient magnetic foundation from the signal of the proton of described excitation.To comprise that the nuclear spin echo signal that receives by RF coil 4 is a voltage as the MR conversion of signals of the alternating field that is produced by the precession nuclear spin, this voltage offers the radio frequency receiver processing unit 8 of radio system 22 via amplifier 7 and multiplexer 6.
This radio system 22 is operated under the RF signal transfer mode with the excitation proton, and operates to handle resulting RF echo-signal under receiving mode.Under transmission mode, the RF pulses are transmitted to be enabled in the nuclear magnetic resonance, NMR among the volume M via transmission channel 9 in system 22.Especially, system 22 handles the corresponding RF echo impulse that is associated with pulse train, and this pulse train is used so that the plural Serial No. of numeral to be provided together with sequence controller 18 by component computer 20.This Serial No. is provided as real part and imaginary part via the digital to analog converter in the radio frequency system 22 12, and is provided to transmission channel 9 from this digital to analog converter 12.In transmission channel 9, utilize radio-frequency carrier signal to modulate described pulse train, this radio-frequency carrier signal has the fundamental frequency corresponding to the resonant frequency of the nuclear spin in measurement volumes M.
Finish via multiplexer 6 from being transferred to the conversion that receives operation.The 4 transmitting RF pulses of RF coil are activated at nuclear proton spin among the measurement volumes M and the RF echo-signal that acquires.Correspondingly the magnetic resonance signal of Huo Deing is carrying out demodulation in the receptor processing unit 8 in RF system 22 under the phase sensitive mode, and converts the real part and the imaginary part of measuring-signal to via corresponding analog-digital converter 11, and handles by tomography computer 17.Tomography computer 17 comes reconstructed image according to the treated RF echo impulse data of obtaining.Under the control of component computer 20, carry out the processing of RF data, view data and control sequence.In response to predetermined pulse train control sequence, the generation and the spatial respective scanned of k-of sequence controller 18 control expectation pulse trains.The reception of the magnetic resonance signal of especially, the switching of sequence controller 18 control magnetic gradients between in due course, the transmission of RF pulse and RF echo data form with definite phase place and amplitude.Synthesizer 19 is determined the sequential of the operation of RF system 22 and sequence controller 18.Carry out the selection of the suitable control sequence that is used to generate the MR image via terminal (control station) 21 and the demonstration of the nuclear spin image that generated by the user, this terminal (control station) 21 comprises keyboard and one or more screen.System 10 uses magnetic field gradient and radio-frequency (RF) excited to create image.Component computer 20 is transformed into the k-spatial data that obtains on the cartesian grid, and three dimensional fourier transform (3DFT) method is used to deal with data to form final image.
Have the section selection magnetic field gradient that gradient intensity is selected in different sections if use, then chemical shift causes the different space displacement of fat signal and water signal in response to excitation with meeting again burnt pulse, thereby prevents reunion Jiao of fat signal.If gradient enough low (corresponding to the pulse long enough) is selected in the section of one of pulse, then there is advantageously improved (and may be basic perfect) fat suppression.Required, as the bandwidth of the function of the burnt pulse bandwidth of meeting again be:
System 10 advantageously adopts the gradient inverting method to select gradient amplitude together with the difference section of the excitation RF pulse that is used for EPI (being called the low bandwidth excitation), to reduce the required prolongation of RF pulse.This be since Spatial Mismatch be in now rightabout (as discuss after a while as shown in Fig. 3) obtain.Select in section under the situation of gradient counter-rotating,
For
(for
,
Have nothing to do), equation 4
Spend the bandwidth of pulses greater than 90 of equation 1.Therefore, advantageously reduced the required RF pulse duration with gradient counter-rotating.The section profile of more than analyzing each pulse of hypothesis is ideal substantially.In fact, because defective section profile, space displacement needs higher.Before the EPI excitation, except the excitation and the burnt pulse of meeting again, also use the fat suppression pulse, with the section profile defective of the explanation excitation and the burnt pulse of meeting again.
Fig. 2 illustrates indication mechanism 10(Fig. 1) how to use different sections to select gradient that the diagram of fat signal inhibition is provided for the excitation and the burnt pulse of meeting again.Fig. 2 illustrates the locus that the contrast time draws, this locus indication in response to the RF pulse of the MR imaging anatomical slice 225 that is used for comprising fat and water at the space displacement of fatty and hydromagneticization.System 10 uses low bandwidth (gradient intensity is selected in low section) the 90 degree RF driving pulses 210 that generated by RF system 22, these low bandwidth 90 degree RF driving pulses 210 make from the fat 220 of water 223 different spatial owing to chemical shift is energized.Similarly, by RF system 22 generate and have different sections select gradient intensity (the RF bandwidth different) with driving pulse 210 and section select the RF of the gradient counter-rotating burnt pulse 212 of meeting again, act on fat 230 from another different spatial.Especially, act on fat 230 RF pulse 212 have high section select gradient intensity (than the high RF bandwidth of driving pulse 210) and section select the gradient counter-rotating, described fatty 230 have aspect magnetization than by driving pulse 210 previous magnetized fatty 220 space displacements that lack.In addition, the 2nd RF that generates by RF system 22 meet again that burnt pulse 214 has that gradient intensity (than the high RF bandwidth of driving pulse 210) is selected in high section and section select the gradient counter-rotating, and only act on water, so fat be can't see the burnt pulse 214 of reunion and therefore the fat magnetization is damaged, and this has advantageously suppressed the MR fat signal.
Fig. 3 illustrates indication and how to use different sections to select gradient to obtain the diagram that fat signal suppresses to the excitation and the burnt pulse of meeting again, and the section of the burnt pulse of wherein meeting again selects gradient to be inverted.System 10 uses low bandwidth (gradient intensity is selected in low section) the 90 degree RF driving pulses 310 that generated by RF system 22, these low bandwidth 90 degree RF driving pulses 310 make in the section 325 from the fat 320 of water 323 different spatial owing to chemical shift is energized.Similarly, generate and have different sections by RF system 22 and select gradient intensity (the RF bandwidth different) and section to select the RF of the gradient counter-rotating burnt pulse 312 of meeting again, act on fat 330 from another different spatial with driving pulse 310.Especially, act on fat 330 RF pulse 312 and have high section and select gradient intensity (than the high RF bandwidth of driving pulse 310) and section to select the gradient counter-rotating, this fat 330 has aspect magnetization than by driving pulse 310 magnetized fatty 320 space displacements that lack.The fatty displacement because counter-rotating section selection gradient has been reversed, so the requirement to fatty displacement during encouraging reduces, therefore this cause higher admissible section to select gradient intensity, just higher RF bandwidth, and this higher RF bandwidth is corresponding to shorter RF pulse.In addition, the 2nd RF that generates by RF system 22 meet again that burnt pulse 314 has that gradient intensity (than the high RF bandwidth of driving pulse 310) is selected in high section and section select the gradient counter-rotating, and only act on water, so fat be can't see the burnt pulse 314 of reunion and therefore the fat magnetization is damaged, and this advantageously suppresses the MR fat signal.
Fig. 4 illustrates 10(Fig. 1 by system) the spin echo EPI pulse train that provides improved fat suppression to adopt is provided, this spin echo EPI pulse train comprises that RF pulse 403, magnetic section select gradient pulse 405, magnetic gradient pulses phase place 407 and magnetic gradient read pulse 409.Before EPI excitation RF pulse 423, use spectral selectivity fat suppression (FS) RF pulse 420.Pulse 423 is the sine pulses with the bandwidth that can be selected by the user.System 10 uses the burnt pulse 426 of meeting again of 180 degree, and the burnt pulse 426 of meeting again of this 180 degree comprises that having the polar section opposite with driving pulse 423 selects the burnt pulse of meeting again of the high bandwidth of gradient.System 10 uses burnt pulse 429, the 2 180 degree burnt pulse 429 of meeting again of meeting again of the 2 180 degree and comprises as select having with driving pulse 423 essentially identical polar sections as shown in the gradient pulse 405 to select the burnt pulse of meeting again of the high bandwidth of gradients in section.System 10 obtains the MR data with the echo time (TE) 430 in single-shot EPI reads.
Fig. 5 illustrates three MRI images that utilize following three kinds of fat suppression schemes to obtain from two patients: (a) standard fat suppression scheme; (b) fat suppression of the gradient counter-rotating of gradient is selected in the section of the burnt pulse of utilization reunion; And (c) fat suppression that the section of burnt pulse selects the gradient counter-rotating of gradient and use low bandwidth driving pulse (driving pulse of gradient is selected in just low section) of meeting again.These images are had a mind to amplify to emphasize fatty element.Especially, image 505 is to use the known fat suppression method of a fat suppression pulse of application before driving pulse to obtain, and the residual fat signal that causes image artifacts 520 is shown.Image 510 utilization has the section of the burnt pulse of meeting again and selects the fat suppression pulse train of the gradient counter-rotating of gradient to obtain, and so that the fat suppression better than image 505 to be provided, but this image 510 still presents the pseudo-shadow 525 of not repressed fat signal.The section that image 515 utilization has a burnt pulse of meeting again select gradient the gradient counter-rotating fat suppression pulse train and use low bandwidth driving pulse (driving pulse of gradient is selected in just low section) to obtain, to suppress the fat signal effect substantially fully.
Fig. 6 be shown in carry out in the MR imaging that fat signal suppresses and by the 10(Fig. 1 of system) flow chart of the process carried out.Step 612 after the beginning of step 611, RF signal generator 22 generates the RF pulse of spin echo signal versions, comprises RF driving pulse and the RF after this RF driving pulse burnt pulse of meeting again.In step 617, comprise that magnetic field section selects the magnetic gradient field system 3 of gradient generator, generate first section of together using and select magnetic field gradient with the RF driving pulse, and generation and the RF second section selection magnetic field gradient that burnt pulse together uses of meeting again.This first and second different section selects magnetic field gradient to have different substantially amplitudes.In one embodiment, magnetic field section selection gradient generator generates the first and second different sections with opposite polarity and selects magnetic field gradient.First section selects magnetic field gradient to have following amplitude: the Spatial Mismatch that this amplitude is selected as feasible fat is slice thickness and because the summation of the Spatial Mismatch that the second section selection gradient causes at least.Second section selects magnetic field gradient to have following amplitude: the Spatial Mismatch that this amplitude is selected as feasible fat is slice thickness and because the summation of the Spatial Mismatch that the first section selection gradient causes at least.
In one embodiment, RF signal generator 22 generates the burnt pulse of a succession of reunion in step 619, and the magnetic field section selects gradient generator to generate the section selection gradient amplitude different to the burnt pulse of alternative reunion.In step 623, component computer 20(MR imaging control unit) obtaining of MR imaging data that the RF pulse that generated and different section selection magnetic field gradients suppressed fat signal substantially used in guiding (control).In addition, RF signal generator 22 is ignored use spectral selectivity fat suppression RF pulse before the RF driving pulse, and still, in another embodiment, generator 22 is created on the spectral selectivity fat suppression RF pulse of using before the RF driving pulse.The process of Fig. 6 stops in step 631.
The processor of Shi Yonging is to be used to carry out the device that is stored in the machine readable instructions that is used to execute the task on the computer-readable medium herein, and can comprise any or combination in hardware and the firmware.Processor can also comprise the memorizer of the executable machine instructions that storage is used to execute the task.Processor acts on information as follows: by manipulation, analysis, modification, conversion or transmission information to use by executable program or massaging device; And/or by routing information to output device.Processor can use or comprise the performance of controller for example or microprocessor, and uses executable instruction to be adjusted the special function that can not be carried out by general purpose computer to carry out.Processor can with any other processor coupling (but electrically and/or for example comprising execution unit) to realize mutual between them and/or to communicate by letter.User interface processor or generator are the well known elements that is used to generate display image or its part that comprises electronic circuit or software or both combinations.User interface comprises makes the user to install mutual one or more display images with processor or other.
Comprise as executable application programs used herein being used to adjust processor implementing the code or the machine readable instructions of predetermined function that described predetermined function such as operating system, context data obtain system or for example in response to those functions of other information processing systems of user command or input.Executable program is code segment or the executable application programs part that one or more particular procedures are carried out in one section code or machine readable instructions, subroutine or other different being used to.These processes can comprise: receive input data and/or parameter, carry out function to the input data executable operations that received and/or in response to the input parameter that is received, and dateout and/or the parameter that obtains is provided.Comprise one or more display images as the user interface of using (UI) herein, these one or more display images are generated by user interface processor and make the user to carry out data mutual and that make it possible to be associated with processor or other devices and obtain and processing capacity.
UI also comprises executable program or executable application programs.This executable program or executable application programs are adjusted user interface processor to generate the signal of expression UI display image.These signals are provided for display device, and this display device display image is watched for the user.Executable program or executable application programs are also from the user input apparatus received signal, and described user input apparatus such as keyboard, mouse, light pen, touch screen or any other permission user provide the device of data to processor.This processor is handled the UI display image in response to the signal that receives from input equipment under the control of executable program or executable application programs.By this way, the user uses input equipment and display image mutual, makes that the user can be mutual with processor or other devices.Function herein and treatment step can automatically be carried out or completely or partially carry out in response to user command.The behavior that automatically performs (comprising step) is in response to executable instruction or device operation and carries out, and need not the user and directly starts the behavior.
The system of Fig. 1-6 and process are not exclusiveness.Can draw other system according to principle of the present invention and reach identical purpose with process.Though invention has been described with reference to specific embodiment, be appreciated that here shown in and described embodiment and variant only be for illustration purpose.Those skilled in the art can implement the modification to current design, and do not depart from scope of the present invention.System uses different sections to select gradient to the excitation in the spin echo signal EPI sequence with the burnt pulse of meeting again, for example to obtain fat suppression.In addition, in alternative embodiment, these processes and application program can be positioned on one or more (for example distributed) blood processor on the unitary network of connection layout 1.The function that provides among Fig. 1-6, image control and any of step can completely or partially be realized with hardware, software or both combinations.
Claims (20)
1. one kind is used for carrying out the system that fat signal suppresses in the MR imaging, comprising:
The RF signal generator is used for using the one or more RF pulses that are used for the echo structure to generate the RF pulse of MR pulse train, comprising:
The RF driving pulse and
RF after the described RF driving pulse burnt pulse of meeting again;
Gradient generator is selected in the magnetic field section, be used to generate the first and second different sections and select magnetic field gradient to be used for respectively the corresponding together use of burnt pulse of meeting again with described RF driving pulse and described RF, the described first and second different sections selection magnetic field gradients have different substantially amplitudes; And
MR imaging control unit is used to guide RF pulse that use generates and different sections to select magnetic field gradient to suppress the obtaining of MR imaging data of fat signal substantially.
2. system according to claim 1, wherein
Described RF signal generator, magnetic field section select gradient generator and MR imaging control unit in the MR imaging device.
3. system according to claim 1, wherein
Magnetic field gradient is selected in the first and second different sections that the section of described magnetic field selects the gradient generator generation to have opposite polarity, and
Described RF signal generator is created on the spectral selectivity fat suppression RF pulse of using before the described RF driving pulse.
4. system according to claim 1, wherein
The gradient generator generation first section selection magnetic field gradient is selected in the section of described magnetic field, and described first section selects magnetic field gradient to have following amplitude: the Spatial Mismatch that this amplitude is selected as feasible fat is slice thickness and because the summation of the Spatial Mismatch that the second section selection gradient causes at least.
5. system according to claim 4, wherein
The gradient generator generation second section selection magnetic field gradient is selected in the section of described magnetic field, and described second section selects magnetic field gradient to have following amplitude: the Spatial Mismatch that this amplitude is selected as feasible fat is slice thickness and because the summation of the Spatial Mismatch that the first section selection gradient causes at least.
6. system according to claim 1, wherein
Described RF signal generator generates the burnt pulse of a succession of reunion.
7. system according to claim 6, wherein
The section of described magnetic field is selected gradient generator to generate gradient amplitude is selected in the different section of the burnt pulse of alternative reunion.
8. system according to claim 1, wherein
The section of described magnetic field is selected gradient generator to generate first section and is selected magnetic field gradient, described first section selects magnetic field gradient to have following amplitude: the Spatial Mismatch that this amplitude is selected as feasible fat is slice thickness and because the summation of the Spatial Mismatch that the second section selection gradient causes at least
The section of described magnetic field is selected gradient generator to generate second section and is selected magnetic field gradient, described second section selects magnetic field gradient to have following amplitude: this amplitude be selected as making the Spatial Mismatch of fat be slice thickness at least with because the summation of the Spatial Mismatch that gradient causes is selected in first section, and
Use the burnt pulse of a succession of reunion rather than only two burnt pulses of meeting again, and section selection gradient amplitude is different to the burnt pulse of alternative reunion.
9. system according to claim 1, wherein
Described RF signal generator is created on the spectral selectivity fat suppression RF pulse before the described RF driving pulse.
10. system according to claim 1, wherein
Described RF signal generator is ignored the use of the spectral selectivity fat suppression RF pulse before described RF driving pulse.
11. one kind is used for carrying out the system that fat signal suppresses in the MR imaging, comprises:
The RF signal generator is used to generate the RF pulse of spin echo signal version, comprising:
The RF driving pulse and
RF after the described RF driving pulse burnt pulse of meeting again;
Gradient generator is selected in the magnetic field section, be used to generate first section of using with described RF driving pulse and select magnetic field gradient and be used to generate with described RF second section that burnt pulse uses of meeting again to select magnetic field gradient, the described first and second different sections select magnetic field gradients to have different substantially amplitudes and opposite polarity; And
MR imaging control unit is used to guide RF pulse that use generates and different sections to select magnetic field gradient to suppress the obtaining of MR imaging data of fat signal substantially.
12. system according to claim 11, wherein
The gradient generator generation first section selection magnetic field gradient is selected in the section of described magnetic field, and described first section selects magnetic field gradient to have following amplitude: the Spatial Mismatch that this amplitude is selected as feasible fat is slice thickness and because the summation of the Spatial Mismatch that the second section selection gradient causes at least.
13. system according to claim 12, wherein
The gradient generator generation second section selection magnetic field gradient is selected in the section of described magnetic field, and described second section selects magnetic field gradient to have following amplitude: the Spatial Mismatch that this amplitude is selected as feasible fat is slice thickness and because the summation of the Spatial Mismatch that the first section selection gradient causes at least.
14. system according to claim 11, wherein
Described RF signal generator generates the burnt pulse of a succession of reunion.
15. system according to claim 14, wherein
The section of described magnetic field is selected gradient generator to generate gradient amplitude is selected in the different section of the burnt pulse of alternative reunion.
16. system according to claim 11, wherein
The section of described magnetic field is selected gradient generator to generate first section and is selected magnetic field gradient, described first section selects magnetic field gradient to have following amplitude: the Spatial Mismatch that this amplitude is selected as feasible fat is slice thickness and because the summation of the Spatial Mismatch that the second section selection gradient causes at least
The section of described magnetic field is selected gradient generator to generate second section and is selected magnetic field gradient, described second section selects magnetic field gradient to have following amplitude: this amplitude be selected as making the Spatial Mismatch of fat be slice thickness at least with because the summation of the Spatial Mismatch that gradient causes is selected in first section, and
Use the burnt pulse of a succession of reunion rather than only two burnt pulses of meeting again, and section selection gradient amplitude is different to the burnt pulse of alternative reunion.
17. system according to claim 11, wherein
Described RF signal generator is created on the spectral selectivity fat suppression RF pulse of using before the described RF driving pulse.
18. system according to claim 11, wherein
Described RF signal generator is ignored the use of the spectral selectivity fat suppression RF pulse before described RF driving pulse.
19. one kind is used for carrying out the method that fat signal suppresses in the MR imaging, comprises following behavior:
The RF pulse that generation is arranged with spin echo signal comprises:
The RF driving pulse and
RF after the described RF driving pulse burnt pulse of meeting again;
Generate the first and second different sections and select magnetic field gradient to be used for respectively the corresponding together use of burnt pulse of meeting again with described RF driving pulse and described RF, the described first and second different sections selection magnetic field gradients have different substantially amplitudes; And
Control uses the RF pulse generated and different sections to select magnetic field gradient to suppress the obtaining of MR imaging data of fat signal substantially.
20. method according to claim 19 comprises following behavior:
Generation has the first and second different sections of opposite polarity and selects magnetic field gradient.
Applications Claiming Priority (6)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US31465310P | 2010-03-17 | 2010-03-17 | |
| US61/314,653 | 2010-03-17 | ||
| US61/314653 | 2010-03-17 | ||
| US12/861943 | 2010-08-24 | ||
| US12/861,943 | 2010-08-24 | ||
| US12/861,943 US8310234B2 (en) | 2010-03-17 | 2010-08-24 | System for fat suppression in MR image acquisition |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN102188245A CN102188245A (en) | 2011-09-21 |
| CN102188245B true CN102188245B (en) | 2013-07-31 |
Family
ID=44597720
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN 201110064406 Active CN102188245B (en) | 2010-03-17 | 2011-03-17 | System for fat suppression in obtaining of MR image |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN102188245B (en) |
Families Citing this family (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| KR101343029B1 (en) | 2011-11-08 | 2013-12-18 | 한국과학기술원 | Magnetic resonance imaging device and control method thereof |
| CN102565733B (en) * | 2011-12-12 | 2014-07-16 | 中国科学院深圳先进技术研究院 | Magnetic resonance multi-core array radio frequency device and magnetic resonance signal receiving method |
| US9687172B2 (en) | 2012-01-24 | 2017-06-27 | National Institute of Health (NIH), The United States of America, U.S. Dept. of Health and Human Services (DHHS) | System for motion corrected MR diffusion imaging |
| DE102012214660B4 (en) | 2012-08-17 | 2014-02-27 | Siemens Aktiengesellschaft | Automated spectral fat saturation |
| CN107643501A (en) * | 2017-03-13 | 2018-01-30 | 李茗 | Applications of the 3D_BTFE_SPAIR in the imaging of pancreatic duct water |
| DE102018201810A1 (en) * | 2018-02-06 | 2019-08-08 | Siemens Healthcare Gmbh | Multilayer imaging with binomial pulses |
| CN113970716B (en) * | 2021-10-18 | 2024-04-23 | 上海联影医疗科技股份有限公司 | Gradient echo sequence fat pressing method and magnetic resonance imaging method and equipment |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5757188A (en) * | 1995-01-19 | 1998-05-26 | Kabushiki Kaisha Toshiba | Magnetic resonance imaging apparatus with fat signal suppression |
| US6342786B1 (en) * | 1999-01-13 | 2002-01-29 | Siemens Aktiengesellschaft | Magnetic resonance tomography apparatus and method in the form of a frequency-selective and location-selective RF pulse sequence for operating same |
| CN101401723A (en) * | 2007-10-04 | 2009-04-08 | 株式会社东芝 | MRI apparatus |
-
2011
- 2011-03-17 CN CN 201110064406 patent/CN102188245B/en active Active
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5757188A (en) * | 1995-01-19 | 1998-05-26 | Kabushiki Kaisha Toshiba | Magnetic resonance imaging apparatus with fat signal suppression |
| US6342786B1 (en) * | 1999-01-13 | 2002-01-29 | Siemens Aktiengesellschaft | Magnetic resonance tomography apparatus and method in the form of a frequency-selective and location-selective RF pulse sequence for operating same |
| CN101401723A (en) * | 2007-10-04 | 2009-04-08 | 株式会社东芝 | MRI apparatus |
Non-Patent Citations (2)
| Title |
|---|
| 下肢磁共振成像技术的研究;刘新球 等;《医疗卫生装备》;20071231;第28卷(第2期);全文 * |
| 刘新球 等.下肢磁共振成像技术的研究.《医疗卫生装备》.2007,第28卷(第2期), |
Also Published As
| Publication number | Publication date |
|---|---|
| CN102188245A (en) | 2011-09-21 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US10955500B2 (en) | Pulse sequences for low field magnetic resonance | |
| CN102188245B (en) | System for fat suppression in obtaining of MR image | |
| CN113366330A (en) | Low field diffusion weighted magnetic resonance imaging | |
| US10534056B2 (en) | System for simultaneous dual-slab acquisition of MR images with asymmetric and time-reversed asymmetric, concatenated pulses | |
| CN102342833B (en) | For setting up the method for magnetic resonance image (MRI) and corresponding magnetic resonance equipment | |
| JP6480952B2 (en) | Low noise magnetic resonance imaging using low order harmonic pulse sequences | |
| US9291693B2 (en) | Magnetic resonance imaging apparatus and control method thereof | |
| JP2015503374A (en) | MRI with Dixon-type water / fat separation and prior knowledge on main field inhomogeneity | |
| JP2014057861A (en) | Method and apparatus for controlling magnetic resonance system | |
| US20070285090A1 (en) | Phase cycling method and magnetic resonance imaging apparatus | |
| KR20160035989A (en) | Method and magnetic resonance system for reconstructing an mr image taking into account the chemical shift | |
| US8310234B2 (en) | System for fat suppression in MR image acquisition | |
| US8456163B2 (en) | Variable image resolution MR imaging system | |
| JP2001112734A (en) | Mri apparatus | |
| KR101282124B1 (en) | Magnetic resonance imaging device and method for constructing mr image using the same | |
| CN108896940B (en) | System and method for compensating gradient pulses for MRI | |
| CN117008029A (en) | System and method for compensating chemical shift substitution in spatial saturation bands using dual spatial saturation pulses | |
| JP2021512678A (en) | MRI using fat / water separation | |
| US11360175B2 (en) | Magnetic resonance imaging apparatus | |
| JPH04246326A (en) | Mr imaging method | |
| JPH04200532A (en) | Mr device |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| TR01 | Transfer of patent right |
Effective date of registration: 20170713 Address after: Erlangen, Germany Patentee after: SIEMENS AG Address before: American Pennsylvania Patentee before: American Siemens Medical Solutions Inc. |
|
| TR01 | Transfer of patent right |