WO2016122810A1 - Specification of an echo train length in magnetic resonance - Google Patents

Specification of an echo train length in magnetic resonance Download PDF

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Publication number
WO2016122810A1
WO2016122810A1 PCT/US2015/067344 US2015067344W WO2016122810A1 WO 2016122810 A1 WO2016122810 A1 WO 2016122810A1 US 2015067344 W US2015067344 W US 2015067344W WO 2016122810 A1 WO2016122810 A1 WO 2016122810A1
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value
echo train
echo
magnetic resonance
train length
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PCT/US2015/067344
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French (fr)
Inventor
Yoshihiro Tomoda
Masanori Ozaki
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General Electric Co
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General Electric Co
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Priority to CN201580075080.XA priority Critical patent/CN107209239B/en
Priority to US15/546,952 priority patent/US10509088B2/en
Publication of WO2016122810A1 publication Critical patent/WO2016122810A1/en
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • 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]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/561—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution by reduction of the scanning time, i.e. fast acquiring systems, e.g. using echo-planar pulse sequences
    • G01R33/5615—Echo train techniques involving acquiring plural, differently encoded, echo signals after one RF excitation, e.g. using gradient refocusing in echo planar imaging [EPI], RF refocusing in rapid acquisition with relaxation enhancement [RARE] or using both RF and gradient refocusing in gradient and spin echo imaging [GRASE]
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • 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]
    • G01R33/48—NMR imaging systems
    • G01R33/4818—MR characterised by data acquisition along a specific k-space trajectory or by the temporal order of k-space coverage, e.g. centric or segmented coverage of k-space
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • 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]
    • G01R33/48—NMR imaging systems
    • G01R33/483—NMR imaging systems with selection of signals or spectra from particular regions of the volume, e.g. in vivo spectroscopy
    • G01R33/4833—NMR imaging systems with selection of signals or spectra from particular regions of the volume, e.g. in vivo spectroscopy using spatially selective excitation of the volume of interest, e.g. selecting non-orthogonal or inclined slices
    • G01R33/4835—NMR imaging systems with selection of signals or spectra from particular regions of the volume, e.g. in vivo spectroscopy using spatially selective excitation of the volume of interest, e.g. selecting non-orthogonal or inclined slices of multiple slices
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • 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]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/543—Control of the operation of the MR system, e.g. setting of acquisition parameters prior to or during MR data acquisition, dynamic shimming, use of one or more scout images for scan plane prescription
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • 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]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/565—Correction of image distortions, e.g. due to magnetic field inhomogeneities
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • 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]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/546—Interface between the MR system and the user, e.g. for controlling the operation of the MR system or for the design of pulse sequences
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • 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]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/561—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution by reduction of the scanning time, i.e. fast acquiring systems, e.g. using echo-planar pulse sequences
    • G01R33/5615—Echo train techniques involving acquiring plural, differently encoded, echo signals after one RF excitation, e.g. using gradient refocusing in echo planar imaging [EPI], RF refocusing in rapid acquisition with relaxation enhancement [RARE] or using both RF and gradient refocusing in gradient and spin echo imaging [GRASE]
    • G01R33/5617—Echo train techniques involving acquiring plural, differently encoded, echo signals after one RF excitation, e.g. using gradient refocusing in echo planar imaging [EPI], RF refocusing in rapid acquisition with relaxation enhancement [RARE] or using both RF and gradient refocusing in gradient and spin echo imaging [GRASE] using RF refocusing, e.g. RARE

Definitions

  • the present invention relates to a magnetic resonance apparatus for performing a sequence for acquiring an echo train from a subject, and a program applied to the magnetic resonance apparatus.
  • a fast spin echo (FSE) technique has been known as an imaging method using a magnetic resonance apparatus.
  • the FSE technique is a method suitable for reducing the scan time because it enables a plurality of echoes to be acquired by one excitation.
  • the operator inputs values for several kinds of parameters (resolution, echo train length, etc.). Once these parameter values have been input, a scan time is calculated based on the parameter values specified by the operator. The scan time is displayed in a display section. The operator observes the scan time displayed in the display section, and in the case that the scan time is too long, he/she modifies a value of the echo train length.
  • a scan time is recalculated based on the modified value of the echo train length, and the recalculated scan time is displayed in the display section.
  • the operator observes the scan time newly displayed in the display section.
  • the operator modifies the echo train length while observing how the scan time varies with the value of the echo train length, and determines a final value of the echo train length.
  • the echo train length affects image quality, so that it is desirable to define the echo train length that gives good image quality.
  • the present invention in its first aspect, is a magnetic resonance apparatus comprising: scanning section for performing a sequence for acquiring an echo train from a subject; upper-limit-value determining unit for determining an upper limit value for an echo train length of said echo train based on echo spacing in said echo train; and unit for obtaining an echo train length in performing said sequence based on said upper limit value for the echo train length and a number of views in which data acquisition is performed in k- space.
  • the present invention in its second aspect, is a program applied to a magnetic resonance apparatus that performs a sequence for acquiring an echo train from a subject, said program being for causing a computer to execute: upper-limit-value determining processing of determining an upper limit value for an echo train length of said echo train based on echo spacing in said echo train; and processing of obtaining an echo train length in performing said sequence based on said upper limit value for the echo train length and a number of views in which data acquisition is performed in k-space.
  • An echo train is obtained based on an upper limit value for the echo train length. Since the echo train length in performing a sequence may be thus determined so as not to exceed the upper limit value for the echo train length, the echo train length suitable for obtaining an image with high quality can be easily obtained.
  • FIG. 1 is a schematic diagram of a magnetic resonance apparatus in one embodiment of the present invention.
  • FIG. 2 is a diagram showing processing a processor 9 executes.
  • FIG. 3 is a diagram schematically showing a region to be imaged in the present embodiment.
  • FIG. 4 is a diagram showing an example of a scan performed for acquiring data in the region to be imaged.
  • FIG. 5 is a diagram showing the flow for obtaining a scan condition.
  • FIG. 6 is a diagram schematically showing a scan condition Al .
  • FIG. 7 is a diagram showing a scan time tl in the scan condition Al .
  • FIG. 8 is a diagram schematically showing an example of another scan condition A2 obtained by Step ST20.
  • FIG. 11 is a diagram schematically showing an exemplary screen of a display section for presenting each of the scan conditions Al and A2 to an operator.
  • FIG. 12 is an explanatory diagram of data acquisition divided over a plurality of times.
  • FIG. 13 is a diagram schematically showing an exemplary screen for presenting scan conditions to the operator.
  • FIG. 1 is a schematic diagram of a magnetic resonance apparatus in one embodiment of the present invention.
  • a magnetic resonance apparatus (referred to as “MR apparatus” hereinbelow) 100 comprises a magnet 2, a table 3, and an RF receive coil (referred to simply as “receive coil” hereinbelow) 4.
  • the magnet 2 has therein a reception space 21 inside of which a subj ect 13 is received.
  • a superconductive coil, a gradient coil, an RF coil, etc. (not shown) are incorporated.
  • the superconductive coil applies a static magnetic field
  • the gradient coil applies a gradient magnetic field
  • the RF coil applies an RF pulse.
  • the table 3 has a cradle 3 a.
  • the cradle 3 a is configured to be movable into the reception space 21 in the magnet 2.
  • the subject 13 is carried into the reception space 21 in the magnet 2 by the cradle 3 a.
  • the receive coil 4 is attached covering from the abdomen up to the chest of the subject 13.
  • the receive coil 4 receives magnetic resonance signals from the subject 13.
  • the MR apparatus 100 further comprises a transmitter 5, a gradient power supply 6, a receiver 7, a computer 8, an operating section 11, and a display section 12.
  • the transmitter 5 supplies electric current to the RF coil
  • the gradient power supply 6 supplies electric current to the gradient coil.
  • the receiver 7 applies signal processing such as demodulation/detection to signals received from the receive coil 4.
  • the magnet 2, receive coil 4, transmitter 5, gradient power supply 6, and receiver 7 together constitute the scanning section.
  • the computer 8 controls operation of several sections in the MR apparatus 100 to implement several kinds of operation of the MR apparatus 100, such as an operation of transmitting required information to the display section 11 , and an operation of reconstructing images.
  • the computer 8 comprises a processor 9 and a storage section 10.
  • the storage section 10 stores therein programs etc. executed by the processor 9.
  • the storage section 10 may be a computer-readable non-transitory recording medium.
  • a CD-ROM for example, may be employed.
  • the processor 9 loads thereon a program stored in the storage section 10, and executes processing written in the program.
  • FIG. 2 shows processing the processor 9 executes.
  • the processor 9 constitutes scan-time calculating unit 81 through TR determining unit 90, etc. by loading programs stored in the storage section 10.
  • the scan-time calculating unit 81 calculates a scan time.
  • the target-value defining unit 82 defines a target value for the scan time used for obtaining a scan condition.
  • the parameter-value defining unit 83 defines parameter values.
  • the echo-spacing calculating unit 84 calculates echo spacing.
  • the upper-limit-value determining unit 85 determines an upper limit value for the echo spacing.
  • the lower-limit-value determining unit 86 determines a lower limit value for the echo spacing.
  • the number-of- views calculating unit 87 calculates a number of views in which data acquisition is performed in k-space.
  • the number-of-repetitions calculating unit 88 calculates a number of repetitions of a sequence group.
  • the echo-train-length calculating unit 89 calculates an echo train length. [0042] The TR determining unit 90 determines a repetition time.
  • the processor 9 is an example for constituting the scan-time calculating unit 81 through TR determining unit 90, and it functions as these units by executing predefined programs.
  • the number- of-repetitions calculating unit 88 and echo-train-length calculating unit 89 together constitute the unit for obtaining an echo train length.
  • the operating section 11 is operated by an operator for inputting several kinds of information to the computer 8.
  • the display section 12 displays several kinds of information.
  • the MR apparatus 100 is constructed as described above.
  • FIG. 3 is a diagram schematically showing a region to be imaged in the present
  • FIG. 3 shows imaging coverage AR in an SI direction.
  • N slices SLi to SLN slice thickness TH are defined within the imaging coverage AR.
  • FIG. 4 is a diagram showing an example of a scan performed for acquiring data in the region to be imaged.
  • FIG. 4 shows a scan SC divided into a plurality of sequence groups Pi to Pm.
  • the scan SC one sequence group is performed during a repetition time TR.
  • Each sequence group includes sequences C i to CN for acquiring data from the slices SLi to SLN (see FIG. 3) according to a multi- slice technique.
  • FIG. 4 a plurality of sequences Ci to CN in a sequence group Pi among the sequence groups Pi through P m are shown.
  • the sequence C i has an excitation pulse (90-degree pulse) for exciting the slice SLi and a plurality of refocusing pulses (180-degree pulses) for refocusing the phase of spins.
  • the sequence Ci also has slice-selective gradient pulses applied in a slice-selective direction SS, phase-encoding gradient pulses applied in a phase-encoding direction PE, and frequency-encoding gradient pulses applied in a frequency-encoding direction FE.
  • an echo train ET consisting of a plurality of echoes El to Ev can be acquired
  • the echo spacing for the plurality of echoes El to Ev is represented by "ESP.”
  • the sequence is designed to have a varying magnitude of the gradient pulses in the phase-encoding direction.
  • sequences d to CN for obtaining images in the slices SL2 to SLN are successively performed.
  • the sequences C2 to CN may be represented by the same sequence chart as that for the sequence Ci, except the excitation frequency of the 90-degree pulse and 180-degree.
  • An echo train ET can thus be acquired each time a sequence Ci to CN is performed.
  • sequence group P i After performing the sequence group P i, a next sequence group P2 is performed. In the sequence group P2, again, the sequences Ci to CN are performed. Similarly thereafter, the sequence groups P3 to Pm are performed. Therefore, to acquire data for image reconstruction, the sequence group is repetitively performed m times in the scan SC.
  • the present embodiment obtains a scan condition that minimizes image degradation as much as possible before the scan SC is performed. Now a method of obtaining a scan condition that minimizes image degradation as much as possible will be described with reference to the flow shown in FIG. 5.
  • Step ST1 a scan condition for the subject is set.
  • FIG. 6 schematically shows a set scan condition Al.
  • FIG. 6 shows representative parameters including echo time TE, resolution Xres, resolution Yres, number of slices N, slice thickness TH, echo spacing ESP, number of repetitions m, echo train length ETL, and repetition time TR.
  • the echo time TE represents an echo time (effective echo time) since the excitation pulse (90-degree pulse) is applied until data in a ky view at the center of k-space is acquired. Therefore, in the case that the data in the ky view at the center of k-space is acquired by an i-th echo (i is an integer from 1 to v), a period of time from the excitation pulse (90-degree pulse) to the i-th echo is the (effective) echo time TE.
  • FIG. 4 shows a case in which the data in the ky view at the center of k-space is obtained by a first echo El. Therefore, a period of time from the excitation pulse (90- degree pulse) to the first echo El is the (effective) echo time TE. In the case that the data in the ky view at the center of k-space is obtained by the last echo Ev, a period of time from the excitation pulse (90-degree pulse) to the last echo Ev is the (effective) echo time TE.
  • the resolution Xres represents a resolution in the frequency-encoding direction FE (see FIG. 4), and the resolution Yres represents a resolution in the phase-encoding direction PE (see FIG. 4).
  • the number of repetitions m represents how many times a sequence group is repetitively performed in the scan SC.
  • the scan-time calculating unit 81 calculates a scan time tl taken to scan the subject with the scan condition Al.
  • FIG. 7 shows the scan time tl for the scan condition Al.
  • Step ST20 After calculating the scan time tl, the process goes to Step ST20.
  • Step ST20 aside from the scan condition Al, another scan condition capable of giving an image with good image quality is obtained. Now a method of obtaining another scan condition at Step ST20 will be described with reference to FIG. 8 hereinbelow.
  • FIG. 8 is a diagram schematically showing an example of another scan condition A2 obtained by Step ST20. Now a procedure in obtaining the scan condition A2 will be described hereinbelow. Step ST20 has Steps ST3 to ST11, which will be sequentially described.
  • the target-value defining unit 82 defines a target value Ttar for the scan time used for determining the another scan condition.
  • the target value Ttar is represented by EQ. (3) below:
  • Step ST4 parameter values for scanning the subject within the target value Ttar for the scan time are defined.
  • the storage section 10 stores therein a formula for obtaining parameter values suitable for scanning the subject within the target value Ttar for the scan time (or a value close to the target value Ttar) based on the scan time tl, target value Ttar for the scan time, and parameter values included in the scan condition Al .
  • the echo-spacing calculating unit 84 calculates echo spacing ESP based on the parameter values defined at Step ST4.
  • the upper-limit-value determining unit 85 determines an upper limit value etl max for the echo train length.
  • the upper limit value etl max for the echo train length is determined so that the following conditions for obtaining an image with high quality are satisfied:
  • the upper limit value XI for the echo train length such that image degradation caused by blurring may be prevented as much as possible from increasing may be represented using the upper limit value TEz max for the maximum echo time and the echo spacing ESP by EQ. (4) below:
  • an upper limit value X2 for the echo train length such that contrast variation due to the MT effect may be prevented as much as possible from increasing is stored in the storage section as a default value before imaging the subject.
  • the upper limit values XI and X2 for the echo train length are values usable as the upper limit value etl max for the echo train length.
  • etl max min(Xl , X2). ... (5)
  • etl max min(TEz_max/ESP, X2). ... (6)
  • TEz_max and X2 are set as default values.
  • TEz max/ESP is not an integer
  • the value for TEz max/ESP may be obtained as an integer value by round-off, round-down, round-up, or the like. After obtaining the upper limit value etl_max for the echo train length, the process goes to Step ST7.
  • the lower-limit-value determining unit 86 determines a lower limit value etl min for the echo train length.
  • ceil designates a function of rounding up the value of TE/ESP.
  • the value of ypoint is obtained taking account of the value of the time-reducing parameter in addition to the resolution Yres.
  • One time-reducing parameter is an acceleration factor, for example, which is defined when performing a sequence using a parallel imaging technique.
  • the acceleration factor Face may be set to a value of 1 , 2, 3, or 4, for example.
  • ypoint may be expressed by EQ. (9) below:
  • Face is set to a value of r acc- 3 or 4.
  • Facc 2
  • k-space is schematically shown, where data acquisition is performed in even-numbered ky views, while no data acquisition is performed in odd-numbered ky views.
  • FIG. 10 has the number of views in which data acquisition is actually performed reduced by half as compared with that in FIG. 9.
  • ypoint Yres / Face
  • Step ST9 when a value of the time-reducing parameter is set, ypoint is calculated taking account of the time-reducing parameter in addition to the resolution Yres. After calculating ypoint, the process goes to Step ST9.
  • ceil designates a function of rounding up the value of ypoint/etl max.
  • the number of repetitions m calculated by the number-of-repetitions calculating unit 88 is represented as "m2.”
  • the echo-train-length calculating unit 89 calculates an echo train length ETL required to acquire data for ypoint by the number of repetitions m calculated at Step ST9.
  • the echo train length ETL may be calculated by EQ. (14) below:
  • EQ. (14) gives the minimum value for the echo train length required to acquire data for ypoint by the number of repetitions m.
  • the echo train length ETL calculated by the echo-train-length calculating unit 89 is represented as "ETL2."
  • ETL obtained by EQ. (14) is smaller than the lower limit value etl rnin for the echo train length obtained at Step ST7, the echo train length ETL may be set to the lower limit value etl rnin.
  • the TR determining unit 90 determines a value for the repetition time TR2 that reduces the scan time.
  • TR determined by the TR determining unit 90 is represented as "TR2.” Once TR has been determined, the flow is terminated.
  • the upper limit value etl max for the echo train length is set so that Conditions 1 and 2 are satisfied (Step ST6).
  • the number of views ypoint in which data acquisition is performed is then calculated (Step ST8), the number of repetitions m is calculated based on the upper limit value etl max for the echo train length (Step ST9), and the echo train length ETL is calculated based on the number of views ypoint and number of repetitions m (Step ST 10).
  • the echo train length suitable for obtaining an image with reduced image degradation caused by contrast variation due to the MT effect and/or by blurring can be automatically calculated, thus eliminating the need for cumbersome operations that the operator would otherwise perform, such as an operation of manually modifying the echo train length, which mitigates stress in operation on the operator.
  • a scan condition A2 preventing the echo train length from exceeding the upper limit value etl may be obtained by performing Step ST20.
  • a period of time tl-At which is shorter than the scan time tl by At, is obtained as a target value T sca n for the scan time at Step ST3.
  • the display section may display a screen for presenting each of the scan conditions Al and A2 to the operator after obtaining the scan condition A2 (see FIG. 11).
  • FIG. 11 is a diagram schematically showing an exemplary screen of the display section for presenting each of the scan conditions Al and A2 to the operator.
  • buttons 11 1 and 11 2 are displayed in the display section.
  • the select button 11 1 is a button for presenting the scan condition Al to the operator, while the select button 11 2 is a button for presenting the scan condition A2 to the operator.
  • Step ST20 may be performed again to obtain a new scan condition.
  • the scan condition may be set so that data for a plurality of slices are acquired separately in a plurality of separate scans (see FIG. 12).
  • FIG. 12 is an explanatory diagram of data acquisition divided over a plurality of times.
  • FIG. 12 shows a case in which data in a plurality of slices are acquired separately in two scans SCI and SC2.
  • the scan time for each scan may be reduced and/or the repetition time TR may be reduced. Therefore, in the case that a breath-holding scan is to be performed and a subject has trouble with long time breath- holding, it is possible to scan the subject with an echo train length suitable for obtaining an image with reduced image degradation caused by contrast variation due to the MT effect or by blurring by performing a scan separately in a plurality of number of times.
  • the present invention is not limited to the breath-holding scan and may be applied to a scan for imaging a subject under free breathing.
  • a period of time shorter than the scan time tl by At is defined as the target value Tscan for the scan time in the present embodiment
  • a period of time longer than the scan time tl by At may be defined as the target value Tscan for the scan time.
  • the resolution Y re s2 in the scan condition A2 may be defined as a value greater than the resolution Yresl in the scan condition Al, it is possible to obtain a scan condition A2 suitable for obtaining an image with higher quality.
  • FIG. 13 is a diagram schematically showing an example of such a screen.
  • the display section shows five select buttons 11 1 to 11 5.
  • the select button 11 1 is a button for presenting the scan condition Al (scan time tl) to the operator.
  • the select button 11 2 is a button for presenting to the operator the scan condition A2 for scanning the subject in a scan time tl-At.
  • the select button 11 3 is a button for presenting to the operator a scan condition A3 for scanning the subject in a scan time tl-2At.
  • the select button 11 4 is a button for presenting to the operator a scan condition A4 for scanning the subject in a scan time tl+At.
  • the select button 11 5 is a button for presenting to the operator a scan condition A5 for scanning the subject in a scan time tl+2At.
  • a smaller one of two values XI and X2 usable as the upper limit value for the echo train length is determined as the upper limit value etl max for the echo train length.
  • the value XI usable as the upper limit value for the echo train length may be used as the upper limit value etl max for the echo train length.
  • the fast spin echo technique is described in the present embodiment, the present invention is applicable to imaging techniques that acquire an echo train.

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Abstract

To automatically obtain an optimal value for the echo train length. An MR apparatus (100) performs a sequence for acquiring an echo train from a subject. The MR apparatus (100) comprises upper-limit-value determining unit for determining an upper limit value etl_max for the echo train length based on a value X1 and a value X2, the value X1 including echo spacing ESP and a lower limit value TEz max for a maximum echo time. The MR apparatus (100) further comprises unit for obtaining an echo train length based on the upper limit value etl max for the echo train length and a number of views ypoint in which data acquisition is performed.

Description

SPECIFICATION OF AN ECHO TRAIN LENGTH IN MAGNETIC RESONANCE
TECHNICAL FIELD
[001] The present invention relates to a magnetic resonance apparatus for performing a sequence for acquiring an echo train from a subject, and a program applied to the magnetic resonance apparatus.
BACKGROUND ART
[002] In imaging a subject with a magnetic resonance apparatus, an operator is required to set a scan condition. In setting the scan condition, however, the operator must specify values for a wide variety of parameters, which poses a problem that the operator experiences much stress. Moreover, there is another problem that the operator may sometimes specify values leading to a lengthened scan time and/or deteriorated image quality. To address such problems, a technique is known to automatically define parameter values (see PTL 1).
PATENT LITERATURE
[003] PTL 1 : Japanese Patent Application KOKAI No. 2011-229546 SUMMARY OF INVENTION
[004] A fast spin echo (FSE) technique has been known as an imaging method using a magnetic resonance apparatus. The FSE technique is a method suitable for reducing the scan time because it enables a plurality of echoes to be acquired by one excitation. In setting a scan condition in the FSE technique, the operator inputs values for several kinds of parameters (resolution, echo train length, etc.). Once these parameter values have been input, a scan time is calculated based on the parameter values specified by the operator. The scan time is displayed in a display section. The operator observes the scan time displayed in the display section, and in the case that the scan time is too long, he/she modifies a value of the echo train length. As soon as the value of the echo train length has been modified, a scan time is recalculated based on the modified value of the echo train length, and the recalculated scan time is displayed in the display section. The operator observes the scan time newly displayed in the display section. Similarly thereafter, the operator modifies the echo train length while observing how the scan time varies with the value of the echo train length, and determines a final value of the echo train length. [005] On the other hand, the echo train length affects image quality, so that it is desirable to define the echo train length that gives good image quality. However, it is not easy for an operator to recognize how image quality varies with the echo train length. Here arises a problem that it is difficult for an operator to specify the echo train length that gives an image with good image quality.
[006] Accordingly, it would be desirable to provide a technique capable of automatically obtaining an optimal value for the echo train length.
Solution to Problem
[007] The present invention, in its first aspect, is a magnetic resonance apparatus comprising: scanning section for performing a sequence for acquiring an echo train from a subject; upper-limit-value determining unit for determining an upper limit value for an echo train length of said echo train based on echo spacing in said echo train; and unit for obtaining an echo train length in performing said sequence based on said upper limit value for the echo train length and a number of views in which data acquisition is performed in k- space.
[008] The present invention, in its second aspect, is a program applied to a magnetic resonance apparatus that performs a sequence for acquiring an echo train from a subject, said program being for causing a computer to execute: upper-limit-value determining processing of determining an upper limit value for an echo train length of said echo train based on echo spacing in said echo train; and processing of obtaining an echo train length in performing said sequence based on said upper limit value for the echo train length and a number of views in which data acquisition is performed in k-space.
[009] An echo train is obtained based on an upper limit value for the echo train length. Since the echo train length in performing a sequence may be thus determined so as not to exceed the upper limit value for the echo train length, the echo train length suitable for obtaining an image with high quality can be easily obtained. BRIEF DESCRIPTION OF DRAWINGS
[0010] FIG. 1 is a schematic diagram of a magnetic resonance apparatus in one embodiment of the present invention.
[0011] FIG. 2 is a diagram showing processing a processor 9 executes.
[0012] FIG. 3 is a diagram schematically showing a region to be imaged in the present embodiment.
[0013] FIG. 4 is a diagram showing an example of a scan performed for acquiring data in the region to be imaged.
[0014] FIG. 5 is a diagram showing the flow for obtaining a scan condition.
[0015] FIG. 6 is a diagram schematically showing a scan condition Al .
[0016] FIG. 7 is a diagram showing a scan time tl in the scan condition Al .
[0017] FIG. 8 is a diagram schematically showing an example of another scan condition A2 obtained by Step ST20.
[0018] FIG. 9 is a diagram schematically showing k-space for each slice when ypoint = 256.
[0019] FIG. 10 is a diagram schematically showing an example of k-space when ypoint = 128.
[0020] FIG. 11 is a diagram schematically showing an exemplary screen of a display section for presenting each of the scan conditions Al and A2 to an operator.
[0021] FIG. 12 is an explanatory diagram of data acquisition divided over a plurality of times.
[0022] FIG. 13 is a diagram schematically showing an exemplary screen for presenting scan conditions to the operator.
Description of Embodiments
[0023] Now an embodiment for practicing the invention will be described hereinbelow, although the present invention is not limited thereto.
[0024] FIG. 1 is a schematic diagram of a magnetic resonance apparatus in one embodiment of the present invention.
[0025] A magnetic resonance apparatus (referred to as "MR apparatus" hereinbelow) 100 comprises a magnet 2, a table 3, and an RF receive coil (referred to simply as "receive coil" hereinbelow) 4.
[0026] The magnet 2 has therein a reception space 21 inside of which a subj ect 13 is received. In the magnet 2, a superconductive coil, a gradient coil, an RF coil, etc. (not shown) are incorporated. The superconductive coil applies a static magnetic field, the gradient coil applies a gradient magnetic field, and the RF coil applies an RF pulse.
[0027] The table 3 has a cradle 3 a. The cradle 3 a is configured to be movable into the reception space 21 in the magnet 2. The subject 13 is carried into the reception space 21 in the magnet 2 by the cradle 3 a.
[0028] The receive coil 4 is attached covering from the abdomen up to the chest of the subject 13. The receive coil 4 receives magnetic resonance signals from the subject 13.
[0029] The MR apparatus 100 further comprises a transmitter 5, a gradient power supply 6, a receiver 7, a computer 8, an operating section 11, and a display section 12.
[0030] The transmitter 5 supplies electric current to the RF coil, and the gradient power supply 6 supplies electric current to the gradient coil. The receiver 7 applies signal processing such as demodulation/detection to signals received from the receive coil 4. The magnet 2, receive coil 4, transmitter 5, gradient power supply 6, and receiver 7 together constitute the scanning section.
[0031] The computer 8 controls operation of several sections in the MR apparatus 100 to implement several kinds of operation of the MR apparatus 100, such as an operation of transmitting required information to the display section 11 , and an operation of reconstructing images. The computer 8 comprises a processor 9 and a storage section 10.
[0032] The storage section 10 stores therein programs etc. executed by the processor 9. The storage section 10 may be a computer-readable non-transitory recording medium. For the non- transitory recording media, a CD-ROM, for example, may be employed. The processor 9 loads thereon a program stored in the storage section 10, and executes processing written in the program. FIG. 2 shows processing the processor 9 executes. The processor 9 constitutes scan-time calculating unit 81 through TR determining unit 90, etc. by loading programs stored in the storage section 10. [0033] The scan-time calculating unit 81 calculates a scan time.
[0034] The target-value defining unit 82 defines a target value for the scan time used for obtaining a scan condition.
[0035] The parameter-value defining unit 83 defines parameter values. [0036] The echo-spacing calculating unit 84 calculates echo spacing.
[0037] The upper-limit-value determining unit 85 determines an upper limit value for the echo spacing.
[0038] The lower-limit-value determining unit 86 determines a lower limit value for the echo spacing.
[0039] The number-of- views calculating unit 87 calculates a number of views in which data acquisition is performed in k-space.
[0040] The number-of-repetitions calculating unit 88 calculates a number of repetitions of a sequence group.
[0041] The echo-train-length calculating unit 89 calculates an echo train length. [0042] The TR determining unit 90 determines a repetition time.
[0043] The processor 9 is an example for constituting the scan-time calculating unit 81 through TR determining unit 90, and it functions as these units by executing predefined programs. The number- of-repetitions calculating unit 88 and echo-train-length calculating unit 89 together constitute the unit for obtaining an echo train length.
[0044] The operating section 11 is operated by an operator for inputting several kinds of information to the computer 8. The display section 12 displays several kinds of information.
[0045] The MR apparatus 100 is constructed as described above.
[0046] FIG. 3 is a diagram schematically showing a region to be imaged in the present
embodiment.
[0047] In the present embodiment, a liver of the subject is imaged. FIG. 3 shows imaging coverage AR in an SI direction. N slices SLi to SLN (slice thickness TH) are defined within the imaging coverage AR.
[0048] FIG. 4 is a diagram showing an example of a scan performed for acquiring data in the region to be imaged.
[0049] FIG. 4 shows a scan SC divided into a plurality of sequence groups Pi to Pm. In the scan SC, one sequence group is performed during a repetition time TR. Each sequence group includes sequences C i to CN for acquiring data from the slices SLi to SLN (see FIG. 3) according to a multi- slice technique. In FIG. 4, a plurality of sequences Ci to CN in a sequence group Pi among the sequence groups Pi through Pm are shown.
[0050] The sequence C i has an excitation pulse (90-degree pulse) for exciting the slice SLi and a plurality of refocusing pulses (180-degree pulses) for refocusing the phase of spins. The sequence Ci also has slice-selective gradient pulses applied in a slice-selective direction SS, phase-encoding gradient pulses applied in a phase-encoding direction PE, and frequency-encoding gradient pulses applied in a frequency-encoding direction FE. By performing the sequence Ci, an echo train ET consisting of a plurality of echoes El to Ev can be acquired The echo spacing for the plurality of echoes El to Ev is represented by "ESP." To acquire data in k-space required for image
reconstruction, the sequence is designed to have a varying magnitude of the gradient pulses in the phase-encoding direction.
[0051] After performing the sequence Ci, the sequences d to CN for obtaining images in the slices SL2 to SLN are successively performed. The sequences C2 to CN may be represented by the same sequence chart as that for the sequence Ci, except the excitation frequency of the 90-degree pulse and 180-degree. An echo train ET can thus be acquired each time a sequence Ci to CN is performed.
[0052] After performing the sequence group P i, a next sequence group P2 is performed. In the sequence group P2, again, the sequences Ci to CN are performed. Similarly thereafter, the sequence groups P3 to Pm are performed. Therefore, to acquire data for image reconstruction, the sequence group is repetitively performed m times in the scan SC.
[0053] In scanning a subject according to the FSE technique, there is a problem that too long a TEz, which is a period of time between the excitation pulse (90-degree pulse) and an echo Ev acquired last in the echo train ET (the period of time will be referred to as "maximum echo time" hereinbelow), exacerbates image degradation caused by blurring. There is also a problem that too large an echo train length ETL of the echo train ET exacerbates image degradation caused by contrast variation due to an MT (Magnetization Transfer) effect. Accordingly, the present embodiment obtains a scan condition that minimizes image degradation as much as possible before the scan SC is performed. Now a method of obtaining a scan condition that minimizes image degradation as much as possible will be described with reference to the flow shown in FIG. 5.
[0054] At Step ST1, a scan condition for the subject is set. FIG. 6 schematically shows a set scan condition Al.
[0055] FIG. 6 shows representative parameters including echo time TE, resolution Xres, resolution Yres, number of slices N, slice thickness TH, echo spacing ESP, number of repetitions m, echo train length ETL, and repetition time TR.
[0056] The echo time TE represents an echo time (effective echo time) since the excitation pulse (90-degree pulse) is applied until data in a ky view at the center of k-space is acquired. Therefore, in the case that the data in the ky view at the center of k-space is acquired by an i-th echo (i is an integer from 1 to v), a period of time from the excitation pulse (90-degree pulse) to the i-th echo is the (effective) echo time TE. FIG. 4 shows a case in which the data in the ky view at the center of k-space is obtained by a first echo El. Therefore, a period of time from the excitation pulse (90- degree pulse) to the first echo El is the (effective) echo time TE. In the case that the data in the ky view at the center of k-space is obtained by the last echo Ev, a period of time from the excitation pulse (90-degree pulse) to the last echo Ev is the (effective) echo time TE.
[0057] The resolution Xres represents a resolution in the frequency-encoding direction FE (see FIG. 4), and the resolution Yres represents a resolution in the phase-encoding direction PE (see FIG. 4). The number of repetitions m represents how many times a sequence group is repetitively performed in the scan SC.
[0058] The scan condition Al shown in FIG. 6 is represented to have TE=TE1, Xres=Xresl , Yres=Yresl, N=N1, TH=TH1, ESP=ESP1, m=ml, ETL=ETL1, and TR=TR1 for convenience of explanation. Values of the parameters in the scan condition Al may be manually input by the operator, or values typically employed in each hospital may be employed without modifications. Once the scan condition Al has been set, the process goes to Step ST2.
[0059] At Step ST2, the scan-time calculating unit 81 (see FIG. 2) calculates a scan time tl taken to scan the subject with the scan condition Al. FIG. 7 shows the scan time tl for the scan condition Al. The scan time tl may be calculated by EQ. (1) below: tl= m x TR. ... (1)
[0060] In the scan condition Al, m=ml and TR=TR1. Therefore, the scan time tl may be represented by EQ. (2) below: tl= m TR
= ml x TRl. ... (2)
[0061] After calculating the scan time tl, the process goes to Step ST20.
[0062] At Step ST20, aside from the scan condition Al, another scan condition capable of giving an image with good image quality is obtained. Now a method of obtaining another scan condition at Step ST20 will be described with reference to FIG. 8 hereinbelow.
[0063] FIG. 8 is a diagram schematically showing an example of another scan condition A2 obtained by Step ST20. Now a procedure in obtaining the scan condition A2 will be described hereinbelow. Step ST20 has Steps ST3 to ST11, which will be sequentially described.
[0064] At Step ST3, the target-value defining unit 82 (see FIG. 2) defines a target value Ttar for the scan time used for determining the another scan condition. The target value Ttar is represented by EQ. (3) below:
Figure imgf000010_0001
[0065] Since tl has been calculated at Step ST2 it has a known value. Moreover, At is a value defined beforehand, and is At=5 seconds, for example. Therefore, the target value Ttar for the scan time can be calculated because tl and At are known. For example, in the case that tl=25 seconds and At=5 seconds, then Ttar=20 seconds from EQ. (3). After obtaining the target value Ttar for the scan time, the process goes to Step ST4.
[0066] At Step ST4, parameter values for scanning the subject within the target value Ttar for the scan time are defined. In the present embodiment, the storage section 10 stores therein a formula for obtaining parameter values suitable for scanning the subject within the target value Ttar for the scan time (or a value close to the target value Ttar) based on the scan time tl, target value Ttar for the scan time, and parameter values included in the scan condition Al . The parameter-value defining unit 83 (see FIG. 2) defines parameter values suitable for scanning the subject within the target value Ttar for the scan time (or a value close to Ttar) based on the formula. Assume here that values for the resolution Xres, resolution Yres, number of slices N, and slice thickness TH are defined as the parameter values for convenience of explanation. In FIG. 8, it is assumed that Xres=Xres2,
Yres=Yres2, N=N2, and TH=TH2 are defined by the parameter-value defining unit 83. The echo time TE is assumed to be TE=TE1. After defining the parameter values, the process goes to Step ST5.
[0067] At Step ST5, the echo-spacing calculating unit 84 (see FIG. 2) calculates echo spacing ESP based on the parameter values defined at Step ST4. FIG. 8 shows the echo spacing ESP calculated by the echo-spacing calculating unit 84 as ESP=ESP2. After determining the echo spacing ESP, the process goes to Step ST6.
[0068] At Step ST6, the upper-limit-value determining unit 85 (see FIG. 2) determines an upper limit value etl max for the echo train length. In the present embodiment, the upper limit value etl max for the echo train length is determined so that the following conditions for obtaining an image with high quality are satisfied:
[0069] (Condition 1) image quality degradation caused by blurring should be minimized as much as possible; and
[0070] (Condition 2) image degradation caused by contrast variation due to the MT effect should be minimized as much as possible.
[0071] Now conditions required of the echo train length ETL in order to satisfy Conditions 1 and 2 will be described hereinbelow.
(For a condition required of the echo train length ETL in order to satisfy Condition 1)
[0072] In acquiring an echo train ET by the FSE technique, too long a maximum echo time TEz (see FIG. 4) poses a problem that an image surfers from image degradation caused by blurring. Therefore, the upper limit value TEz max for the maximum echo time TEz should be set so as to reduce blurring. Accordingly, in the present embodiment, an upper limit value TEz max for the maximum echo time such that image degradation caused by blurring may be prevented from increasing too much is stored in the storage section 10 as a default value before imaging the subject. In the case that the region to be imaged is the abdomen, the upper limit value TEz max for the maximum echo time is TEz_max=160 ms, for example.
[0073] Therefore, the upper limit value XI for the echo train length such that image degradation caused by blurring may be prevented as much as possible from increasing may be represented using the upper limit value TEz max for the maximum echo time and the echo spacing ESP by EQ. (4) below:
XI = TEz max / ESP. ... (4)
(For a condition required of the echo train length ETL in order to satisfy Condition 2)
[0074] In acquiring an echo train ET by the FSE technique, too great a value of the echo train length ETL poses a problem that image degradation caused by contrast variation due to the MT effect is exacerbated. Therefore, the upper limit value for the echo train length should be set so as to prevent contrast variation due to the MT effect from increasing too much. Accordingly, in the present embodiment, an upper limit value X2 for the echo train length such that contrast variation due to the MT effect may be prevented as much as possible from increasing is stored in the storage section as a default value before imaging the subject. In the case that the region to be imaged is the abdomen, the upper limit value X2 for the echo train length is X2=24, for example.
[0075] From the preceding description, it can be seen that the upper limit values XI and X2 for the echo train length are values usable as the upper limit value etl max for the echo train length. To satisfy both Conditions 1 and 2, however, a smaller one of the upper limit values XI and X2 should be used as the upper limit value etl max for the echo train length. Therefore, the upper limit value etl max for the echo train length may be represented by EQ. (5) below: etl_max = min(Xl , X2). ... (5)
[0076] In the equation, min is a function of taking a smaller one of XI and X2. Thus, etl max can be obtained from EQ. (5). Substituting EQ. (4) into EQ. (5) results in the following equation: etl max = min(TEz_max/ESP, X2). ... (6)
[0077] As described earlier, TEz_max and X2 are set as default values. The echo spacing ESP has been calculated at Step ST5. Therefore, by substituting the values into EQ. (6), the upper limit value etl max for the echo train length may be obtained. For example, when XI =24, TEz_max=160 (msec), and ESP=16 (msec), then the upper limit value etl max for the echo train length has a value as given below: etl max = min(Xl, TEz max/ESP)
= min (24, 160/16)
= 10.
[0078] In the case that TEz max/ESP is not an integer, the value for TEz max/ESP may be obtained as an integer value by round-off, round-down, round-up, or the like. After obtaining the upper limit value etl_max for the echo train length, the process goes to Step ST7.
[0079] At Step ST7, the lower-limit-value determining unit 86 (see FIG. 2) determines a lower limit value etl min for the echo train length. The lower limit value etl min for the echo train length is represented by EQ. (7) below: etl min = ceil(TE/ESP). ... (7)
[0080] In the equation, ceil designates a function of rounding up the value of TE/ESP. The echo time TE is TE=TE1 , and the echo spacing ESP is ESP=SEP2. Therefore, the lower limit value etl rnin for the echo train length may be obtained from EQ. (7). After obtaining the lower limit value etl_min for the echo train length, the process goes to Step ST8.
[0081] At Step ST8, the number of views ypoint in which data acquisition is actually performed among a plurality of ky views lined up in the ky direction in k-space is obtained based on the resolution Yres=Yres2 set at Step ST4. For example, when Yres2=256, then ypoint=256. FIG. 9 schematically shows k-space for each slice when ypoint=256. When ypoint=256, data acquisition is performed in views of ky=-127 to 128 for each slice.
[0082] In the case that a value of a time-reducing parameter for reducing the scan time is included in the scan condition, the value of ypoint is obtained taking account of the value of the time-reducing parameter in addition to the resolution Yres. One time-reducing parameter is an acceleration factor, for example, which is defined when performing a sequence using a parallel imaging technique. The acceleration factor Face is a factor representing that the number of phase encoding steps PN in the sequence is decreased from PN=Yres to PN=(1 /Face) Yres. When defining ypoint taking account of the acceleration factor Face in addition to Yres, the number-of-views calculating unit 87 (see FIG. 2) calculates the number of views ypoint in which data acquisition is performed using EQ. (8) below: ypoint= Yres / Face. ... (8)
[0083] The acceleration factor Face may be set to a value of 1 , 2, 3, or 4, for example. When performing a sequence in which the parallel imaging technique is not performed, for example, Face is set to Facc=l . When Facc=l , ypoint may be expressed by EQ. (9) below:
Ypoint = Yres / Face
= Yres. ... (9)
[0084] Therefore, when parallel imaging is not performed (Facc=l), ypoint is kept at Yres without change.
[0085] When the parallel imaging technique is performed, Face is set to a value of r acc- 3 or 4. When Facc=2, ypoint may be expressed by EQ. (10) below: ypoint = Yres / Face
= Yres / 2. ... (10)
[0086] Therefore, when Facc=2, ypoint is set to a half of Yres. Therefore, Facc=2 is able to halve the number of phase encoding steps in the sequence as compared with Facc=l, thus reducing by half the number of views in which data acquisition is actually performed. For example, when Yres=256 and Facc=2, then ypoint=128. FIG. 10 schematically shows an example of k-space when ypoint=128. In FIG. 10, k-space is schematically shown, where data acquisition is performed in even-numbered ky views, while no data acquisition is performed in odd-numbered ky views. The even-numbered ky views in which data acquisition is performed are indicated by solid lines, while odd-numbered ky views in which no data acquisition is performed are indicated by dashed lines. Therefore, it can be seen that FIG. 10 has the number of views in which data acquisition is actually performed reduced by half as compared with that in FIG. 9.
[0087] When Facc=3 is set, ypoint may be expressed by EQ. (11) below: ypoint = Yres / Face
= Yres / 3. (11) [0088] When FaCc=3, ypoint is set to 1/3 of Yres. Therefore, FaCc=3 causes a number of phase encoding steps in the sequence to be 1/3 as compared with FaCc=l.
[0089] Furthermore, when FaCc=4 is set, ypoint may be expressed by EQ. (12) below: ypoint = Yres / F; a<x
Yres / 4. ... (12)
[0090] When Facc=4, ypoint is set to 1/4 of Yres. Therefore, Facc=4 causes a number of phase encoding steps in the sequence to be 1/4 as compared with Facc=l.
As described above, when a value of the time-reducing parameter is set, ypoint is calculated taking account of the time-reducing parameter in addition to the resolution Yres. After calculating ypoint, the process goes to Step ST9.
[0091] At Step ST9, the number-of-repetitions calculating unit 88 (see FIG. 2) obtains how many times the sequence group should be repeated at minimum to acquire data for the number of views ypoint obtained at Step ST8. Representing a minimal number of repetitions for the sequence group required to acquire data for the number of views ypoint as "m," the number of repetitions m may be expressed by EQ. (13) below using the number of views ypoint and the upper limit value etl max for the echo train length: m = ceil(ypoint/etl_max). ... (13)
[0092] In the equation, ceil designates a function of rounding up the value of ypoint/etl max. The number of repetitions m may thus be obtained from EQ. (13). For example, when ypoint=256 and etl_max=23, the number of repetitions m has a value as follows: m = ceil(ypoint/etl_max)
= ceil(256/24)
= 11.
[0093] In FIG. 8, the number of repetitions m calculated by the number-of-repetitions calculating unit 88 is represented as "m2."
[0094] After obtaining the number of repetitions m, the process goes to Step ST10. [0095] At Step ST10, the echo-train-length calculating unit 89 (see FIG. 2) calculates an echo train length ETL required to acquire data for ypoint by the number of repetitions m calculated at Step ST9. The echo train length ETL may be calculated by EQ. (14) below:
ETL = ceil(ypoint/m). ... (14)
[0096] EQ. (14) gives the minimum value for the echo train length required to acquire data for ypoint by the number of repetitions m. When ypoint=256 and m=l 1, for example, the echo train length ETL has a value given by:
ETL = ceil(ypoint/m)
= ceil(256/l l)
= 24.
[0097] In FIG. 8, the echo train length ETL calculated by the echo-train-length calculating unit 89 is represented as "ETL2." In the case that ETL obtained by EQ. (14) is smaller than the lower limit value etl rnin for the echo train length obtained at Step ST7, the echo train length ETL may be set to the lower limit value etl rnin. Once the echo train length ETL has been obtained, the process goes to Step STll .
[0098] At Step ST11, the TR determining unit 90 (see FIG. 2) determines a value for the repetition time TR2 that reduces the scan time. In FIG. 8, TR determined by the TR determining unit 90 is represented as "TR2." Once TR has been determined, the flow is terminated.
[0099] In the present embodiment, the upper limit value etl max for the echo train length is set so that Conditions 1 and 2 are satisfied (Step ST6). The number of views ypoint in which data acquisition is performed is then calculated (Step ST8), the number of repetitions m is calculated based on the upper limit value etl max for the echo train length (Step ST9), and the echo train length ETL is calculated based on the number of views ypoint and number of repetitions m (Step ST 10). Therefore, the echo train length suitable for obtaining an image with reduced image degradation caused by contrast variation due to the MT effect and/or by blurring can be automatically calculated, thus eliminating the need for cumbersome operations that the operator would otherwise perform, such as an operation of manually modifying the echo train length, which mitigates stress in operation on the operator. [00100] Moreover, according to the present embodiment, even in the case that the echo train length ETLl defined in the scan condition Al exceeds the upper limit value for the echo train length, a scan condition A2 preventing the echo train length from exceeding the upper limit value etl may be obtained by performing Step ST20.
[00101] In the present embodiment, a period of time tl-At, which is shorter than the scan time tl by At, is obtained as a target value Tscan for the scan time at Step ST3. This gives a scan condition A2 that enables a scan on the subject to be achieved so that Conditions 1 and 2 are satisfied in a scan time shorter than the scan time tl .
[00102] The display section may display a screen for presenting each of the scan conditions Al and A2 to the operator after obtaining the scan condition A2 (see FIG. 11). FIG. 11 is a diagram schematically showing an exemplary screen of the display section for presenting each of the scan conditions Al and A2 to the operator.
[00103] Two select buttons 11 1 and 11 2 are displayed in the display section.
[00104] The select button 11 1 is a button for presenting the scan condition Al to the operator, while the select button 11 2 is a button for presenting the scan condition A2 to the operator.
[00105] Upon clicking on of a select button by the operator, specific parameter values, etc. in a scan condition corresponding to the select button are displayed. Therefore, the operator can observe the two scan conditions having different scan times, and select an optimal one from between the two scan conditions.
[00106] In the case that a scan time Tscan is calculated based on the scan condition A2 and a difference in time between the scan time TSCan and target value Ttar is greater than a predefined value, Step ST20 may be performed again to obtain a new scan condition. Moreover, in the case that the value of the repetition time TR=TR2 does not fall within an allowable range BR (for example, BR=2500 to 5000 msec) for the repetition time TR, Step ST20 may be performed again to obtain a new scan condition.
[00107] Moreover, in the case that the scan time Tscan is too much longer than the target value Ttar, or the repetition time TR exceeds the upper limit value (for example, 5000 msec) of the allowable range BR of the repetition time TR, the scan condition may be set so that data for a plurality of slices are acquired separately in a plurality of separate scans (see FIG. 12). [00108] FIG. 12 is an explanatory diagram of data acquisition divided over a plurality of times.
[00109] FIG. 12 shows a case in which data in a plurality of slices are acquired separately in two scans SCI and SC2. By thus acquiring data for slices separately in a plurality of scans, the scan time for each scan may be reduced and/or the repetition time TR may be reduced. Therefore, in the case that a breath-holding scan is to be performed and a subject has trouble with long time breath- holding, it is possible to scan the subject with an echo train length suitable for obtaining an image with reduced image degradation caused by contrast variation due to the MT effect or by blurring by performing a scan separately in a plurality of number of times. It should be noted that the present invention is not limited to the breath-holding scan and may be applied to a scan for imaging a subject under free breathing.
[00110] While a period of time shorter than the scan time tl by At is defined as the target value Tscan for the scan time in the present embodiment, a period of time longer than the scan time tl by At may be defined as the target value Tscan for the scan time. Since in this case, the resolution Yres2 in the scan condition A2 may be defined as a value greater than the resolution Yresl in the scan condition Al, it is possible to obtain a scan condition A2 suitable for obtaining an image with higher quality. Alternatively, it may be contemplated that both a value smaller than the scan time tl and a value greater than the scan time tl are determined as target values for the scan time, scan conditions corresponding to the respective target values for the scan time are obtained, and the display section is caused to display a screen for presenting these scan conditions to the operator (see FIG. 13). FIG. 13 is a diagram schematically showing an example of such a screen.
[00111] The display section shows five select buttons 11 1 to 11 5.
[00112] The select button 11 1 is a button for presenting the scan condition Al (scan time tl) to the operator.
[00113] The select button 11 2 is a button for presenting to the operator the scan condition A2 for scanning the subject in a scan time tl-At.
[00114] The select button 11 3 is a button for presenting to the operator a scan condition A3 for scanning the subject in a scan time tl-2At.
[00115] The select button 11 4 is a button for presenting to the operator a scan condition A4 for scanning the subject in a scan time tl+At. [00116] The select button 11 5 is a button for presenting to the operator a scan condition A5 for scanning the subject in a scan time tl+2At.
[00117] Upon clicking on of a select button by the operator, specific parameter values, etc. in a scan condition corresponding to the select button are displayed. Therefore, the operator can observe the five scan conditions having different scan times, and select an optimal one from among the five scan conditions.
[00118] In the present embodiment, a smaller one of two values XI and X2 usable as the upper limit value for the echo train length is determined as the upper limit value etl max for the echo train length. However, in the case that the contrast variation due to the MT effect is not very large, the value XI usable as the upper limit value for the echo train length may be used as the upper limit value etl max for the echo train length.
[00119] While the fast spin echo technique is described in the present embodiment, the present invention is applicable to imaging techniques that acquire an echo train.

Claims

1. A magnetic resonance apparatus comprising: scanning section for performing a sequence for acquiring an echo train from a subject; upper-limit-value determining unit for determining an upper limit value for an echo train length of said echo train based on echo spacing in said echo train; and unit for obtaining an echo train length in performing said sequence based on said upper limit value for the echo train length and a number of views in which data acquisition is performed in k- space.
2. The magnetic resonance apparatus as recited in claim 1 , wherein: said sequence has an excitation pulse for exciting a region to be imaged, and said upper-limit-value determining unit calculates a first value usable as said upper limit value for the echo train length based on a period of time between said excitation pulse and a last echo in said echo train and on said echo spacing, and determines said upper limit value for the echo train length based on said first value.
3. The magnetic resonance apparatus as recited in claim 2, wherein: said upper-limit-value determining unit determines said upper limit value for the echo train length based on said first value and a second value usable as said upper limit value for the echo train length.
4. The magnetic resonance apparatus as recited in claim 3, wherein: said second value is a value defined taking account of contrast variation caused by an MT effect.
5. The magnetic resonance apparatus as recited in claim 3 or 4, wherein: said upper- limit-value determining unit determines said upper limit value for the echo train based on a smaller one of said first and second values.
6. The magnetic resonance apparatus as recited in any one of claims 3 through 5, wherein: in the case that said first value is smaller than said second value, said upper-limit-value determining unit determines said first value as said upper limit value for the echo train.
7. The magnetic resonance apparatus as recited in claim 6, wherein: in the case that said first value is not an integer, said upper-limit-value determining unit converts said first value into an integer.
8. The magnetic resonance apparatus as recited in any one of claims 1 through 7, wherein: said scanning section performs a sequence group including a plurality of sequences within a repetition time, and said unit for obtaining an echo train length comprises: number-of-repetitions calculating unit for calculating a minimal number of repetitions for said sequence group required to acquire data in k-space based on said upper limit value for the echo train length; and echo-train-length calculating unit for calculating said echo train length based on said number of repetitions.
9. The magnetic resonance apparatus as recited in claim 8, comprising: unit for obtaining a number of views in which acquisition of data in k-space is performed, wherein said number-of-repetitions calculating unit calculates said number of repetitions based on said upper limit value for the echo train length and said number of views.
10. The magnetic resonance apparatus as recited in claim 9, wherein: said unit for obtaining a number of views obtains said number of views based on a resolution in a phase-encoding direction and a time-reducing parameter for reducing a scan time.
11. The magnetic resonance apparatus as recited in claim 10, wherein: said time- reducing parameter is a parameter for reducing the number of phase encoding steps.
The magnetic resonance apparatus as recited in any one of claims 8 through 11, comprising: TR determining unit for determining said repetition time.
13. The magnetic resonance apparatus as recited in any one of claims 1 through 12, comprising: lower-limit-value determining unit for determining a lower limit value for the echo train length based on said echo spacing.
14. The magnetic resonance apparatus as recited in claim 13, wherein: said lower-limit-value determining unit determines said lower limit value for the echo train based on said echo spacing and an effective echo time.
15. The magnetic resonance apparatus as recited in any one of claims 1 through 14, wherein: said apparatus sets a second scan condition for scanning the subject based on a first scan condition for scanning the subject.
16. The magnetic resonance apparatus as recited in claim 15, comprising: scan-time calculating unit for calculating a first scan time taken to scan the subject according to said first scan condition; and target-value defining unit for defining a target value for the scan time used for obtaining said second scan condition.
17. The magnetic resonance apparatus as recited in claim 16, comprising: parameter- value defining unit for defining parameter values in said second scan condition.
18. The magnetic resonance apparatus as recited in claim 17, wherein: said unit for obtaining an echo train length obtains an echo train length in said second scan condition.
19. The magnetic resonance apparatus as recited in claim 18, wherein: according to said second scan condition, data in a plurality of slices are acquired separately over a plurality of scans.
20. A program applied to a magnetic resonance apparatus that performs a sequence for acquiring an echo train from a subject, said program being for causing a computer to execute: upper-limit-value determining processing of determining an upper limit value for an echo train length of said echo train based on echo spacing in said echo train; and processing of obtaining an echo train length in performing said sequence based on said upper limit value for the echo train length and a number of views in which data acquisition is performed in k-space.
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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3760117A4 (en) * 2018-03-01 2021-05-19 Niigata University NUCLEAR MAGNETIC RESONANCE APPARATUS, MAGNETIC RESONANCE IMAGING APPARATUS, NUCLEAR MAGNETIC RESONANCE PROCESS, MAGNETIC RESONANCE IMAGING PROCESS, METHOD FOR DETERMINING MEASUREMENT CONDITIONS, AND PROGRAM

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR101844514B1 (en) * 2016-09-02 2018-04-02 삼성전자주식회사 Magnetic resonance imaging apparatus and method of obtaining magnetic resonance image
CN116643224B (en) * 2023-05-16 2025-12-30 浙江大学 Joint design method for spatial trajectories with variable acceleration factor k

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2011229546A (en) 2010-04-23 2011-11-17 Ge Medical Systems Global Technology Co Llc Scan condition determination device, magnetic resonance imaging device, scan condition determination method and program
US20130335082A1 (en) * 2012-06-19 2013-12-19 Dominik Paul Method and magnetic resonance system to acquire mr data in a predetermined volume segment
WO2014176428A1 (en) * 2013-04-25 2014-10-30 Ge Medical Systems Global Technology Company, Llc Scan condition determining apparatus, magnetic resonance imaging system and scan condition determining method

Family Cites Families (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP3940442B2 (en) * 1995-04-28 2007-07-04 株式会社東芝 Magnetic resonance imaging system
JP4129339B2 (en) * 1999-05-21 2008-08-06 株式会社東芝 MRI equipment
US8594767B2 (en) * 2007-02-09 2013-11-26 Hitachi Medical Corporation Magnetic resonance imaging apparatus and magnetic resonance imaging method
JP5164443B2 (en) * 2007-06-18 2013-03-21 株式会社日立メディコ Magnetic resonance imaging system
US8228060B2 (en) * 2007-06-25 2012-07-24 General Electric Company Method and apparatus for generating a flip angle schedule for a spin echo train pulse sequence
US8941381B2 (en) * 2010-05-28 2015-01-27 David Feinberg Multiplicative increase in MRI data acquisition with multi-band RF excitation pulses in a simultaneous image refocusing pulse sequence
JP5942271B2 (en) * 2011-01-17 2016-06-29 株式会社日立製作所 Magnetic resonance imaging apparatus and fluid weighted image acquisition method
US9612301B2 (en) * 2011-02-14 2017-04-04 Duke University High-throughput and motion insensitive MRI accelerated with multi-echo planar acquisition and related systems
DE102012204434B3 (en) * 2012-03-20 2013-07-11 Siemens Aktiengesellschaft Method for operating magnetic resonance imaging system for producing magnetic resonance image data of investigation object e.g. patient, involves selecting width of radio frequency (RF) refocusing pulses for generating echo signals

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2011229546A (en) 2010-04-23 2011-11-17 Ge Medical Systems Global Technology Co Llc Scan condition determination device, magnetic resonance imaging device, scan condition determination method and program
US20130335082A1 (en) * 2012-06-19 2013-12-19 Dominik Paul Method and magnetic resonance system to acquire mr data in a predetermined volume segment
WO2014176428A1 (en) * 2013-04-25 2014-10-30 Ge Medical Systems Global Technology Company, Llc Scan condition determining apparatus, magnetic resonance imaging system and scan condition determining method

Non-Patent Citations (5)

* Cited by examiner, † Cited by third party
Title
CONSTABLE R T ET AL: "Factors influencing contrast in fast spin-echo MR imaging", MAGNETIC RESONANCE IMAGING, ELSEVIER SCIENCE, TARRYTOWN, NY, US, vol. 10, no. 4, 1 January 1992 (1992-01-01), pages 497 - 511, XP026425127, ISSN: 0730-725X, [retrieved on 19920101] *
E M ESCOBEDO ET AL: "Usefulness of turbo spin-echo MR imaging in the evaluation of meniscal tears: comparison with a conventional spin-echo sequence.", AMERICAN JOURNAL OF ROENTGENOLOGY, vol. 167, no. 5, 1 November 1996 (1996-11-01), US, pages 1223 - 1227, XP055261652, ISSN: 0361-803X, DOI: 10.2214/ajr.167.5.8911185 *
FREDERICK H. EPSTEIN ET AL: "Optimization of fast cardiac imaging using an echo-train readout", JOURNAL OF MAGNETIC RESONANCE IMAGING, vol. 11, no. 2, 1 February 2000 (2000-02-01), US, pages 75 - 80, XP055261653, ISSN: 1053-1807, DOI: 10.1002/(SICI)1522-2586(200002)11:2<75::AID-JMRI1>3.0.CO;2-P *
REEDER S B ET AL: "Multi-echo segmented k-space imaging: An optimized hybrid sequence for ultrafast cardiac imaging", MAGNETIC RESONANCE IN MEDICINE 1999 US, vol. 41, no. 2, 1999, pages 375 - 385, XP055261648, ISSN: 0740-3194 *
SZE G ET AL: "Fast spin-echo MR imaging of the cervical spine: influence of echo train length and echo spacing on image contrast and quality.", AJNR. AMERICAN JOURNAL OF NEURORADIOLOGY 1993 SEP-OCT, vol. 14, no. 5, September 1993 (1993-09-01), pages 1203 - 1213, XP055261650, ISSN: 0195-6108 *

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3760117A4 (en) * 2018-03-01 2021-05-19 Niigata University NUCLEAR MAGNETIC RESONANCE APPARATUS, MAGNETIC RESONANCE IMAGING APPARATUS, NUCLEAR MAGNETIC RESONANCE PROCESS, MAGNETIC RESONANCE IMAGING PROCESS, METHOD FOR DETERMINING MEASUREMENT CONDITIONS, AND PROGRAM
US11320507B2 (en) 2018-03-01 2022-05-03 Niigata University Nuclear magnetic resonance apparatus, magnetic resonance imaging apparatus, nuclear magnetic resonance method, magnetic resonance imaging method, method for determining measurement conditions, and program

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