U.S. patent number RE48,347 [Application Number 16/195,079] was granted by the patent office on 2020-12-08 for method and apparatus for spin-echo-train mr imaging using prescribed signal evolutions.
This patent grant is currently assigned to University of Virginia Patent Foundation. The grantee listed for this patent is University of Virginia Patent Foundation. Invention is credited to James R. Brookeman, John P. Mugler, III.
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United States Patent |
RE48,347 |
Mugler, III , et
al. |
December 8, 2020 |
Method and apparatus for spin-echo-train MR imaging using
prescribed signal evolutions
Abstract
A magnetic resonance imaging "MRI" method and apparatus for
lengthening the usable echo-train duration and reducing the power
deposition for imaging is provided. The method explicitly considers
the t1 and t2 relaxation times for the tissues of interest, and
permits the desired image contrast to be incorporated into the
tissue signal evolutions corresponding to the long echo train. The
method provides a means to shorten image acquisition times and/or
increase spatial resolution for widely-used spin-echo train
magnetic resonance techniques, and enables high-field imaging
within the safety guidelines established by the Food and Drug
Administration for power deposition in human MRI.
Inventors: |
Mugler, III; John P.
(Charlottesville, VA), Brookeman; James R. (Charlottesville,
VA) |
Applicant: |
Name |
City |
State |
Country |
Type |
University of Virginia Patent Foundation |
Charlottesville |
VA |
US |
|
|
Assignee: |
University of Virginia Patent
Foundation (Charlottesville, VA)
|
Family
ID: |
1000005060038 |
Appl.
No.: |
16/195,079 |
Filed: |
November 19, 2018 |
PCT
Filed: |
December 21, 2001 |
PCT No.: |
PCT/US01/50551 |
371(c)(1),(2),(4) Date: |
June 19, 2003 |
PCT
Pub. No.: |
WO02/50574 |
PCT
Pub. Date: |
June 27, 2002 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
Issue Date |
|
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14708875 |
May 11, 2015 |
RE47178 |
|
|
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14053190 |
Oct 14, 2013 |
RE45725 |
|
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|
12354471 |
Jan 15, 2009 |
RE44644 |
|
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60257182 |
Dec 21, 2000 |
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Reissue of: |
10451124 |
Dec 21, 2001 |
7164268 |
Jan 16, 2007 |
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Reissue of: |
10451124 |
Dec 21, 2001 |
7164268 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
G01R
33/5615 (20130101); G01R 33/5615 (20130101); G01R
33/50 (20130101); G01R 33/50 (20130101); G01R
33/5617 (20130101); G01R 33/586 (20130101); G01R
33/5617 (20130101); G01R 33/586 (20130101) |
Current International
Class: |
G01R
33/561 (20060101); G01R 33/50 (20060101); G01R
33/58 (20060101) |
Field of
Search: |
;324/300-322
;600/410-423 |
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applicant.
|
Primary Examiner: Whittington; Kenneth
Attorney, Agent or Firm: Panitch Schwarze Belisario &
Nadel LLP
Government Interests
GOVERNMENT SUPPORT
Work described herein was supported by Federal Grant Number
NS-35142, awarded by the National Institutes of Health. The United
States Government possesses certain rights in and to this
invention.
Parent Case Text
.Iadd.Notice: More than one reissue application has been filed for
the reissue of U.S. Pat. No. 7,164,268. The reissue applications
are Ser. No. 16/195,079 (the present application), application Ser.
No. 14/708,875 (now U.S. Pat. No. RE47,178), filed May 11, 2015,
application Ser. No. 14/053,190 (now U.S. Pat. No. RE45,725), filed
Oct. 14, 2013, and application Ser. No. 12/354,471 (now U.S. Pat.
No. RE44,644), filed Jan. 15, 2009. The present application is a
reissue continuation of application Ser. No. 14/708,875.
.Iaddend.
RELATED APPLICATIONS
This application is a .[.national stage.]. .Iadd.reissue
continuation of U.S. patent application Ser. No. 14/708,875, filed
on May 11, 2015, which is a reissue continuation of U.S. patent
application Ser. No. 14/053,190, filed on Oct. 14, 2013 (now, U.S.
Pat. No. RE45,725), which was a reissue continuation of U.S. patent
application Ser. No. 12/354,472, filed on Jan. 15, 2009 (now, U.S.
Pat. No. RE44,644), which was a reissue of U.S. Pat. No. 7,164,268,
which issued from U.S. patent application Ser. No. 10/451,124,
filed on Jun. 19, 2003 as a U.S. National Stage .Iaddend.filing of
International Application No. PCT/US01/50551, filed 21 Dec. 2001,
which claims .[.benefit.]. .Iadd.priority .Iaddend.under 35 U.S.C.
Section 119(e) from U.S. Provisional .Iadd.Patent
.Iaddend.Application .[.Ser..]. No. 60/257,182, filed on Dec. 21,
2000, entitled "Spin-Echo-Train MR Imaging Using Prescribed Signal
Evolutions," the entire .[.disclosure.]. .Iadd.disclosures
.Iaddend.of which .[.is hereby.]. .Iadd.are .Iaddend.incorporated
by reference herein. The present application is related to U.S.
Pat. No. 5,245,282, filed on Jun. 28, 1991, entitled
"Three-dimensional Magnetic Resonance Imaging," the entire
disclosure of which is hereby incorporated by reference herein.
Claims
We claim:
.[.1. A method for generating a spin echo pulse sequence for
operating a magnetic resonance imaging apparatus for imaging an
object that permits at least one of lengthening usable echo-train
duration, reducing power deposition and incorporating desired image
contrast into the tissue signal evolutions, said method comprising:
a) providing contrast-preparation, said contrast-preparation
comprising generating at least one of at least one radio-frequency
pulse, at least one magnetic-field gradient pulse, and at least one
time delay, whereby said contrast preparation encodes the
magnetization with at least one desired image contrast; b)
calculating flip angles and phases of refocusing radio-frequency
pulses that are applied in a data-acquisition step, wherein said
calculation provides desired prescribed signal evolution and
desired overall signal level, said calculation comprises: i)
selecting values of T1 and T2 relaxation times and selecting proton
density; ii) selecting a prescribed time course of the amplitudes
and phases of the radio-frequency magnetic resonance signals that
are generated by said refocusing radio-frequency pulses; and iii)
selecting characteristics of said contrast-preparation step, said
data-acquisition step and a magnetization-recovery step, with the
exception of the flip angles and phases of the refocusing
radio-frequency pulses that are to be calculated; and c) providing
said-data acquisition step based on a spin echo train acquisition,
said data-acquisition step comprises: i) an excitation
radio-frequency pulse having a flip angle and phase; ii) at least
two refocusing radio-frequency pulses, each having a flip angle and
phase as determined by said calculation step; and iii)
magnetic-field gradient pulses that encode spatial information into
at least one of said radio-frequency magnetic resonance signals
that follow at least one of said refocusing radio-frequency pulses;
d) providing magnetization-recovery, said magnetization-recovery
comprises a time delay to allow magnetization to relax; and e)
repeating steps (a) through (d) until a predetermined extent of
spatial frequency space has been sampled..].
.[.2. The method of claim 1, wherein said calculation of the flip
angles and phases is generated using an appropriate analytical or
computer-based algorithm..].
.[.3. The method of claim 1, wherein said calculation of the flip
angles and phases is generated to account for, the effects of
multiple applications of: said contrast-preparation, said
data-acquisition and said magnetization-recovery steps, which are
required to sample the desired extent of spatial-frequency
space..].
.[.4. The method of claim 1, wherein a two-dimensional plane of
spatial-frequency space is sampled..].
.[.5. The method of claim 1, wherein a three-dimensional volume of
spatial-frequency space is sampled..].
.[.6. The method of claim 1, wherein at least one of said
contrast-preparation and magnetization-recovery steps is
omitted..].
.[.7. The method of claim 1, wherein said calculation step is
performed once before one of said first contrast-preparation step
and said first data-acquisition step..].
.[.8. The method of claim 1, wherein at least one of at least one
said contrast-preparation step, at least one said data-acquisition
step and at least one said magnetization-recovery step is initiated
by a trigger signal to synchronizes the pulse sequence with at
least one of at least one external temporal event and at least one
internal temporal event..].
.[.9. The method of claim 8, wherein said external and internal
events comprise at least one of at least one voluntary action, at
least one involuntary action, at least one respiratory cycle and at
least one cardiac cycle..].
.[.10. The method of claim 1, wherein at least one of at least one
radio-frequency pulse and at least one magnetic-field gradient
pulse is applied as part of at least one of at least one said
magnetization-preparation step and at least one said
data-acquisition step is for the purpose of stabilizing the
response of at least one of magnetization related system and said
apparatus related hardware system..].
.[.11. The method of claim 1, wherein time duration varies between
repetitions for at least one of at least one said
contrast-preparation step, at least one said data-acquisition step
and at least one said magnetization-recovery step..].
.[.12. The method of claim 1, wherein the time periods between
consecutive refocusing radio-frequency pulses applied during said
data-acquisition steps are all of equal duration..].
.[.13. The method of claim 1, wherein time periods between
consecutive refocusing radio-frequency pulses applied during said
data-acquisition steps vary in duration amongst pairs of refocusing
radio-frequency pulses during at least one said data-acquisition
step..].
.[.14. The method of claim 1 wherein all the radio-frequency pulses
are at least one of non-spatially selective and non-chemically
selective..].
.[.15. The method of claim 1, wherein at least one of the
radio-frequency pulses is at least one of spatially selective in
one of one, two and three dimensions, chemically selective, and
adiabatic..].
.[.16. The method of claim 1, wherein during each said
data-acquisition step, the phase difference between the phase for
the excitation radio-frequency pulse and the phases for all
refocusing radio-frequency pulses is about 90 degrees..].
.[.17. The method of claim 1, wherein during each data-acquisition
step, the phase difference between the phase for any refocusing
radio-frequency pulse and the phase for the immediately subsequent
refocusing radio-frequency pulses is about 180 degrees, and the
phase difference between the phase for the excitation
radio-frequency pulse and the phase for the first refocusing pulse
is one of about 0 degrees and about 180 degrees..].
.[.18. The method of claim 17, wherein the flip angle for the
excitation radio-frequency pulse is about one-half of the flip
angle for the first refocusing radio-frequency pulse..].
.[.19. The method of claim 1, wherein the spatial-encoding
magnetic-field gradient pulses applied during each said
data-acquisition step are configured so as to collect data,
following each of at least one of the refocusing radio-frequency
pulses, for one line in spatial-frequency space which is parallel
to all other lines of data so collected, so as to collect the data
using a magnetic resonance imaging technique selected from the
group consisting of rapid acquisition with relaxation enhancement
(RARE), fast spin echo (FSE), and turbo spin echo (TSE or
TurboSE)..].
.[.20. The method of claim 1, wherein the spatial-encoding
magnetic-field gradient pulses applied during each said
data-acquisition step are configured so as to collect data,
following each of at least one of the refocusing radio-frequency
pulses, for two or more lines in spatial-frequency space which are
parallel to all other lines of data so collected, so as to collect
the data using a magnetic resonance imaging technique selected from
the group consisting of gradient and spin echo (GRASE) and turbo
gradient spin echo (TGSE or TurboGSE)..].
.[.21. The method of claim 1, wherein the spatial-encoding
magnetic-field gradient pulses applied during each said
data-acquisition step are configured so as to collect data,
following each of at least one of the refocusing radio-frequency
pulses, for one or more lines in spatial-frequency space, each of
which pass through one of a single point in spatial-frequency space
and a single line in spatial-frequency space, so as to collect the
data using a magnetic resonance imaging technique selected from the
group consisting of radial sampling or projection-reconstruction
sampling..].
.[.22. The method of claim 21, wherein the single point in
spatial-frequency space is about zero spatial frequency..].
.[.23. The method of claim 21, wherein the single line in
spatial-frequency space includes zero spatial frequency..].
.[.24. The method of claim 1, wherein the spatial-encoding
magnetic-field gradient pulses applied during each said
data-acquisition step are configured so as to collect data,
following each of at least one of the refocusing radio-frequency
pulses, along a spiral trajectory in spatial-frequency space, each
trajectory of which is contained in one of two dimensions and three
dimensions, and each trajectory of which passes through one of a
single point in spatial-frequency space and a single line in
spatial-frequency space..].
.[.25. The method of claim 24, wherein the single point in
spatial-frequency space is about zero spatial frequency..].
.[.26. The method of claim 24, wherein the single line in
spatial-frequency space includes zero spatial frequency..].
.[.27. The method of claim 1, wherein the spatial-encoding
magnetic-field gradient pulses applied during at least one of said
data-acquisition steps are configured to collect sufficient
spatial-frequency data to reconstruct at least two image sets, each
of which exhibits contrast properties different from the other
image sets..].
.[.28. The method of claim 27, wherein at least some of the
spatial-frequency data collected during at least one of said
data-acquisition steps is used in the reconstruction of more than
one image set, whereby the data is shared between image
sets..].
.[.29. The method of claim 1, wherein the spatial-encoding
magnetic-field gradient pulses applied during at least one of said
data-acquisition steps are configured so that, for the echo
following at least one of the refocusing radio-frequency pulses, at
least one of the first moment, the second moment and the third
moment corresponding to at least one of the spatial-encoding
directions is approximately zero..].
.[.30. The method of claim 1, wherein the spatial-encoding
magnetic-field gradient pulses applied during at least one of said
data-acquisition steps are configured so that, following at least
one of the refocusing radio-frequency pulses, the zeroth moment
measured over the time period between said refocusing
radio-frequency pulse and the immediately consecutive refocusing
radio-frequency pulse is approximately zero for at least one of the
spatial-encoding directions..].
.[.31. The method of claim 1, wherein during all said
data-acquisition steps the duration of all data-sampling periods
are equal..].
.[.32. The method of claim 1, wherein during at least one of said
data-acquisition steps at least one of the data-sampling periods
has a duration that differs from the duration of at least one other
data-sampling period..].
.[.33. The method of claim 1, wherein the spatial-encoding
magnetic-field gradient pulses applied during said data-acquisition
steps are configured so that the extent of spatial-frequency space
sampled along at least one of the spatial-encoding directions is
not symmetric with respect to zero spatial frequency, whereby a
larger extent of spatial-frequency space is sampled to one side of
zero spatial frequency as compared to the opposite side of zero
spatial frequency..].
.[.34. The method of claim 33 wherein said spatial-frequency data
is reconstructed using a partial-Fourier reconstruction
algorithm..].
.[.35. The method of claim 1, wherein during at least one of said
data-acquisition steps the temporal order in which
spatial-frequency space data is collected for at least one of the
spatial-encoding directions is based on achieving at least one of
selected contrast properties in the image and selected properties
of the corresponding point spread function..].
.[.36. The method of claim 1, wherein during at least one of said
data-acquisition steps the temporal order in which
spatial-frequency space data is collected is different from that
for at least one other data-acquisition step..].
.[.37. The method of claim 1, wherein during at least one of said
data-acquisition steps the extent of spatial-frequency space data
that is collected is different from that for at least one other
data-acquisition step..].
.[.38. The method of claim 1, wherein during at least one of said
data-acquisition steps spatial encoding of the radio-frequency
magnetic resonance signal that follows at least one of the
refocusing radio-frequency pulse is performed using only phase
encoding so that said signal is received by the radio-frequency
transceiver in the absence of any applied magnetic-field gradient
pulses and hence contains chemical-shift information..].
.[.39. The method of claim 1, wherein at least one navigator
radio-frequency pulse is incorporated into the pulse sequence for
the purpose of determining the displacement of a portion of the
object..].
.[.40. A magnetic resonance imaging apparatus generating a spin
echo pulse sequence in order to operate the apparatus in imaging an
object that permits at least one of lengthening usable echo-train
duration, reducing power deposition and incorporating desired image
contrast into the tissue signal evolutions, the apparatus
comprising: a main magnet system generating a steady magnetic
field; a gradient magnet system generating temporary gradient
magnetic fields; a radio-frequency transmitter system generating
radio-frequency pulses; a radio-frequency receiver system receiving
magnetic resonance signals; a reconstruction unit reconstructing an
image of the object from the received magnetic resonance signals;
and a control unit generating signals controlling the gradient
magnet system, the radio-frequency transmitter system, the
radio-frequency receiver system, and the reconstruction unit,
wherein the control unit generates signals causing: a) providing
contrast-preparation, said contrast-preparation comprising
generating at least one of at least one radio-frequency pulse, at
least one magnetic-field gradient pulse, and at least one time
delay, whereby said contrast preparation encodes the magnetization
with at least one desired image contrast; b) calculating flip
angles and phases of refocusing radio-frequency pulses that are
applied in a data-acquisition step, wherein said calculation
provides desired prescribed signal evolution and desired over-all
signal level, said calculation comprises: i) selecting values of T1
and T2 relaxation times and selecting proton density; ii) selecting
a prescribed time course of the amplitudes and phases of the
radio-frequency magnetic resonance signals that are generated by
said refocusing radio-frequency pulses; and iii) selecting
characteristics of said contrast-preparation step, said
data-acquisition step and a magnetization-recovery step, with the
exception of the flip angles and phases of the refocusing
radio-frequency pulses that are to be calculated; and c) providing
said-data acquisition step based on a spin echo train acquisition,
said data-acquisition step comprises: i) an excitation
radio-frequency pulse having a flip angle and phase, ii) at least
two refocusing radio-frequency pulses, each having a flip angle and
phase as determined by said calculation step, and iii)
magnetic-field gradient pulses that encode spatial information into
at least one of said radio-frequency magnetic resonance signals
that follow at least one of said refocusing radio-frequency pulses;
d) providing magnetization-recovery, said magnetization-recovery
comprises a time delay to allow magnetization to relax; and e)
repeating steps (a) through (d) until a predetermined extent of
spatial frequency space has been sampled..].
.[.41. A magnetic resonance imaging apparatus generating a spin
echo pulse sequence in order to operate the apparatus in imaging an
object that permits at least one of lengthening usable echo-train
duration, reducing power deposition and incorporating desired image
contrast into the tissue signal evolutions, the apparatus
comprising: main magnet means generating a steady magnetic field;
gradient magnet means generating temporary gradient magnetic
fields; radio-frequency transmitter means generating
radio-frequency pulses; radio-frequency receiver means receiving
magnetic resonance signals;. reconstruction means reconstructing an
image of the object from the received magnetic resonance signals;
and control means generating signals controlling the gradient
magnet means, the radio-frequency transmitter means, the
radio-frequency receiver means, and the reconstruction means,
wherein the control means generates signals causing: a) providing
contrast-preparation, said contrast-preparation comprising
generating at least one of at least one radio-frequency pulse, at
least one magnetic-field gradient pulse, and at least one time
delay, whereby said contrast preparation encodes the magnetization
with at least one desired image contrast; b) calculating flip
angles and phases of refocusing radio-frequency pulses that are
applied in a data-acquisition step, wherein said calculation
provides desired prescribed signal evolution and desired over-all
signal level, said calculation comprises: i) selecting values of T1
and T2 relaxation times and selecting proton density; ii) selecting
a prescribed time course of the amplitudes and phases of the
radio-frequency magnetic resonance signals that are generated by
said refocusing radio-frequency pulses; and iii) selecting
characteristics of said contrast-preparation step, said
data-acquisition step and a magnetization-recovery step, with the
exception of the flip angles and phases of the refocusing
radio-frequency pulses that are to be calculated; c) providing
said-data acquisition step based on a spin echo train acquisition,
said data-acquisition step comprises: i) an excitation
radio-frequency pulse having a flip angle and phase, ii) at least
two refocusing radio-frequency pulses, each having a flip angle and
phase as determined by said calculation step, and iii)
magnetic-field gradient pulses that encode spatial information into
at least one of said radio-frequency magnetic resonance signals
that follow at least one of said refocusing radio-frequency pulses;
d) providing magnetization-recovery, said magnetization-recovery
comprises a time delay to allow magnetization to relax; and e)
repeating steps (a) through (d) until a predetermined extent of
spatial frequency space has been sampled..].
.[.42. A computer readable media carrying encoded program
instructions for causing a programmable magnetic resonance imaging
apparatus to perform the method of claim 1..].
.[.43. A computer program provided on a computer useable readable
medium having computer program logic enabling at least one
processor in a magnetic resonance imaging apparatus to generate a
spin echo pulse sequence that permits at least one of lengthening
usable echo-train duration, reducing power deposition and
incorporating desired image contrast into the tissue signal
evolutions, said computer program logic comprising: a) providing
contrast-preparation, said contrast-preparation comprising
generating at least one of at least one radio-frequency pulse, at
least one magnetic-field gradient pulse, and at least one time
delay, whereby said contrast preparation encodes the magnetization
with at least one desired image contrast; b) calculating flip
angles and phases of refocusing radio-frequency pulses that are
applied in a data-acquisition step, wherein said calculation
provides desired prescribed signal evolution and desired overall
signal level, said calculation comprises: i) selecting values of T1
and T2 relaxation times and selecting proton density; ii) selecting
a prescribed time course of the amplitudes and phases of the
radio-frequency magnetic resonance signals that are generated by
said refocusing radio-frequency pulses; and iii) selecting
characteristics of said contrast-preparation step, said
data-acquisition step and a magnetization-recovery step, with the
exception of the flip angles and phases of the refocusing
radio-frequency pulses that are to be calculated; and c) providing
said-data acquisition step based on a spin echo train acquisition,
said data-acquisition step comprises: i) an excitation
radio-frequency pulse having a flip angle and phase; ii) at least
two refocusing radio-frequency pulses, each having a flip angle and
phase as determined by said calculation step; and iii)
magnetic-field gradient pulses that encode spatial information into
at least one of said radio-frequency magnetic resonance signals
that follow at least one of said refocusing radio-frequency pulses;
d) providing magnetization-recovery, said magnetization-recovery
comprises a time delay to allow magnetization to relax; and e)
repeating steps (a) through (d) until a predetermined extent of
spatial frequency space has been sampled..].
.[.44. The method of claim 40, wherein at least one of said
contrast-preparation and magnetization-recovery steps is
omitted..].
.[.45. The method of claim 41, wherein at least one of said
contrast-preparation and magnetization-recovery steps is
omitted..].
.[.46. The method of claim 43, wherein at least one of said
contrast-preparation and magnetization-recovery steps is
omitted..].
.Iadd.47. A method of generating a T2-weighted fast-spin-echo or
turbo-spin-echo pulse sequence having refocusing radio-frequency
pulses with varying flip angles, said method comprising:
generating, via a control unit, a three-dimensional T2-weighted
fast-spin-echo or turbo-spin-echo pulse sequence used in operating
a magnetic resonance imaging apparatus that images tissues of a
human subject, the generated pulse sequence having varying flip
angles that vary among a majority of refocusing radio-frequency
pulses of an echo train by decreasing to a minimum value and later
increasing, and wherein the varying flip angles result in a reduced
power deposition compared to the power deposition that is obtained
using refocusing radio-frequency pulses with constant flip angles
of approximately 180 degrees; applying the pulse sequence to a
radio-frequency transmitter coil of the magnetic resonance imaging
apparatus to generate radio-frequency pulses in an examination zone
that includes tissues of the human subject and receiving resulting
magnetic resonance signals from tissues of the human subject, using
a radio-frequency receiver coil of the magnetic resonance imaging
apparatus; and reconstructing magnetic resonance images from the
resulting magnetic resonance signals from the tissues of the human
subject, wherein the reconstructed magnetic resonance images have a
T2-weighted contrast, and wherein the T2-weighted contrast is
substantially the same as contrast in T2-weighted magnetic
resonance images generated from a fast-spin-echo or turbo-spin-echo
pulse sequence using refocusing radio-frequency pulses with
constant flip angles of approximately 180 degrees..Iaddend.
.Iadd.48. The method of claim 47, wherein the pulse sequence has a
usable echo-train duration for spin-echo train imaging that is
lengthened substantially beyond that achievable with constant,
low-flip-angle or pseudosteady-state approaches..Iaddend.
.Iadd.49. The method of claim 47, wherein the varying flip angles
are calculated to provide a prescribed signal
evolution..Iaddend.
.Iadd.50. The method of claim 49, wherein the prescribed signal
evolution is associated with T1 and T2 relaxation times that are
arbitrarily chosen..Iaddend.
.Iadd.51. The method of claim 50, wherein the pulse sequence has a
usable echo-train duration for spin-echo train imaging that is
lengthened substantially beyond that achievable with constant,
low-flip-angle or pseudosteady-state approaches..Iaddend.
.Iadd.52. A magnetic resonance imaging (MRI) apparatus that images
tissues of a human subject and is configured to generate a
T2-weighted fast-spin-echo or turbo-spin-echo pulse sequence having
refocusing radio-frequency pulses with varying flip angles, the
apparatus comprising: a main magnet system that generates a steady
magnetic field; a gradient magnet system that generates temporary
gradient magnetic fields; a radio-frequency transmitter system that
generates radio-frequency pulses; a radio-frequency receiver system
that receives magnetic resonance signals; a reconstruction unit
that reconstructs magnetic resonance images of the subject from the
received magnetic resonance signals from the tissues of the human
subject; and a control unit that generates signals controlling the
gradient magnet system, the radio-frequency transmitter system, the
radio-frequency receiver system, and the reconstruction unit,
wherein the control unit further provides signals that generate: a
three-dimensional T2-weighted fast-spin-echo or turbo-spin-echo
pulse sequence used in operating the MRI apparatus, the generated
pulse sequence having varying flip angles that vary among a
majority of refocusing radio-frequency pulses of an echo train by
decreasing to a minimum value and later increasing, and wherein the
varying flip angles result in a reduced power deposition compared
to the power deposition that is obtained using refocusing
radio-frequency pulses with constant flip angles of approximately
180 degrees, wherein the reconstructed magnetic resonance images
have a T2-weighted contrast, and wherein the T2-weighted contrast
is substantially the same as contrast in T2-weighted magnetic
resonance images generated from a fast-spin-echo or turbo-spin-echo
pulse sequence using refocusing radio-frequency pulses with
constant flip angles of approximately 180 degrees..Iaddend.
.Iadd.53. The apparatus of claim 52, wherein the pulse sequence
that is generated has a usable echo-train duration for spin-echo
train imaging that is lengthened substantially beyond that
achievable with constant, low-flip-angle or pseudosteady-state
approaches..Iaddend.
.Iadd.54. The apparatus of claim 52, wherein a control unit
executes a software program that performs calculations and is
configured to calculate the varying flip angles to provide a
prescribed signal evolution..Iaddend.
.Iadd.55. The apparatus of claim 54, wherein the prescribed signal
evolution is associated with T1 and T2 relaxation times that are
arbitrarily chosen..Iaddend.
.Iadd.56. The apparatus of claim 55, wherein the pulse sequence
that is generated has a usable echo-train duration for spin-echo
train imaging that is lengthened substantially beyond that
achievable with constant, low-flip-angle or pseudosteady-state
approaches..Iaddend.
.Iadd.57. A non-transitory computer readable medium having computer
program logic that when implemented enables one or more processors
in a magnetic resonance imaging apparatus that images tissues of a
human subject to generate a T2-weighted fast-spin-echo or
turbo-spin-echo pulse sequence having refocusing radio-frequency
pulses with varying flip angles, said computer program logic
comprising: logic for generating a three-dimensional T2-weighted
fast-spin-echo or turbo-spin-echo pulse sequence used in operating
the magnetic resonance imaging apparatus, the generated pulse
sequence having varying flip angles that vary among a majority of
refocusing radio-frequency pulses of an echo train by decreasing to
a minimum value and later increasing, and wherein the varying flip
angles result in a reduced power deposition compared to the power
deposition that is obtained using refocusing radio-frequency pulses
with constant flip angles of approximately 180 degrees; and logic
for reconstructing magnetic resonance images from magnetic
resonance signals received from tissues of the human subject as a
result of applying the generated pulse sequence, wherein the
reconstructed magnetic resonance images have a T2-weighted
contrast, and wherein the T2-weighted contrast is substantially the
same as contrast in T2-weighted magnetic resonance images generated
from a fast-spin-echo or turbo-spin-echo pulse sequence using
refocusing radio-frequency pulses with constant flip angles of
approximately 180 degrees..Iaddend.
.Iadd.58. The non-transitory computer readable medium having
computer program logic as defined in claim 57, wherein the pulse
sequence that is generated has a usable echo-train duration for
spin-echo train imaging that is lengthened substantially beyond
that achievable with constant, low-flip-angle or pseudosteady-state
approaches..Iaddend.
.Iadd.59. The non-transitory computer readable medium having
computer program logic as defined in claim 57, wherein the computer
program logic also calculates the varying flip angles to provide a
prescribed signal evolution..Iaddend.
.Iadd.60. The non-transitory computer readable medium having
computer program logic as defined in claim 59, wherein the
prescribed signal evolution is associated with T1 and T2 relaxation
times that are arbitrarily chosen..Iaddend.
.Iadd.61. The non-transitory computer readable medium having
computer program logic as defined in claim 60, wherein the pulse
sequence that is generated has a usable echo-train duration for
spin-echo train imaging that is lengthened substantially beyond
that achievable with constant, low-flip-angle or pseudosteady-state
approaches..Iaddend.
Description
FIELD OF INVENTION
The present invention relates to a pulse sequence for use in
operating a magnetic resonance imaging apparatus, and in particular
for lengthening the usable echo-train duration and reducing the
power deposition for spin-echo-train magnetic resonance
imaging.
BACKGROUND OF INVENTION
Over the past twenty years, nuclear magnetic resonance imaging
(MRI) has developed into an important modality for both clinical
and basic-science imaging applications. A large portion of MRI
techniques are based on spin-echo (SE) acquisitions because they
provide a wide range of useful image contrast properties that
highlight pathological changes and are resistant to image artifacts
from a variety of sources such as radio-frequency or static-field
inhomogeneities.
Spin-echo-based methods can be subdivided into two categories,
including those that generate one spin echo for each desired image
contrast following each excitation radio-frequency (RF) pulse, and
those that generate more than one spin echo for each desired image
contrast following each excitation RF pulse. The first category
includes, but is not limited thereto, the techniques commonly
referred to as "conventional SE" imaging. The second category
includes, but is not limited thereto, a method called "RARE" (See
Hennig J., Nauerth A., Friedburg H., "RARE Imaging: A Fast Imaging
Method for Clinical MR", Magn. Reson. Med. 1986, 3:823-833; and
Mulkern R. V., Wong S. T. S., Winalski C., Jolesz F. A., "Contrast
Manipulation and Artifact Assessment of 2D and 3D RARE Sequences",
Magn. Reson. Imaging 1990, 8:557-566, of which are hereby
incorporated by reference in their entirety) and its derivatives,
commonly referred to as "turbo-SE" or "fast-SE" imaging (See Melki
P. S., Jolesz F. A., Mulkern R. V., "Partial RF Echo Planar Imaging
with the FALSE Method. I Experimental and Theoretical Assessment of
Artifact", Magn. Reson. Med. 1992, 26:328-341 and Jones K. M.,
Mulkern R. V., Schwartz R. B., Oshio K., Barnes P. D., Jolesz F.
A., "Fast Spin-Echo MR Imaging of the Brain and Spine: Current
Concepts", AJR 1992, 158:1313-1320, of which are hereby
incorporated by reference in their entirety). For the purposes of
this disclosure, we are primarily interested in the generalized
form of techniques in the second category; however the present
invention is applicable to the first category as well. The term
"generalized" refers to the form of the spatial-encoding gradients
that are applied following any given refocusing RF pulse. For
example, RARE imaging encodes one line of spatial-frequency space
(k-space) data following each refocusing RF pulse using a constant,
frequency-encoding magnetic field gradient. In contrast, "GRASE"
imaging (See Feinberg D. A., Oshio K. "GRASE (Gradient- And
Spin-Echo) MR Imaging: A New Fast Clinical Imaging Technique",
Radiology 1991, 181: 597-602; and Oshio K., Feinberg D. A. "GRASE
(Gradient- And Spin-Echo) Imaging: A Novel Fast MRI Technique",
Magn. Reson. Med. 1991, 20:344-349, of which are hereby
incorporated by reference in their entirety) encodes three or more
lines of k-space data following each refocusing RF pulse using an
oscillating, frequency-encoding gradient waveform. This oscillating
gradient waveform collects one line of k-space data that includes
the spin echo, and one or more additional lines of k-space data
before the spin echo and after the spin echo. One skilled in the
art would appreciate that there exist an infinite number of
possibilities for spatially encoding the MR signal following each
refocusing RF pulse. For the purpose of this disclosure, we define
the term "spin-echo-train" imaging to encompass all of these
possibilities, including, but not limited thereto, RARE, turbo-SE,
fast-SE and GRASE imaging, because the present invention deals
with, among other things, the RF-pulse history during the echo
train, not the details of the spatial encoding.
In general, one of the major goals of technique development for MRI
has been to increase the amount of k-space data sampled per unit
time, under the constraints of obtaining the desired image contrast
and maintaining image artifacts at a tolerable level. Increases in
the data rate are typically traded for a decrease in the image
acquisition time and/or an increase in the spatial resolution. In
this respect, spin-echo-train methods have played an important
role; fast-SE imaging is routinely and widely used in clinical
MRI.
For instance, the echo trains used in clinical fast-SE imaging
generally employ high flip angles (>100.degree.) for the
refocusing RF pulses, and their durations are typically less than
the T2 relaxation times of interest for short effective echo times
(e.g., T1 or proton-density weighting) or less than two to three
times these T2 values for long effective echo times (e.g., T2
weighting or "FLAIR"; see Hajnal J. V., Bryant D. J., Kasuboski L.,
Pattany P. M., De Coene B., Lewis P. D., Pennock J. M., Oatridge
A., Young I. R., Bydder G. M., "Use of Fluid Attenuated Inversion
Recovery (FLAIR) Pulse Sequences in MRI of the Brain", J. Comput.
Assist. Tomogr. 1992, 16:841-844, of which is hereby incorporated
by reference in its entirety). For example, considering brain
imaging at 1.5 Tesla, these limits translate to echo-train
durations of <100 ms and <300 ms for short and long effective
echo times, respectively. When high flip angles are used for the
refocusing RF pulses, echo-train durations that are longer than
these limits can substantially degrade image contrast and introduce
artifacts such as blurring (See Mulkern et al.; Melki et al.;
Constable R. T., Gore J. C., "The Loss of Small Objects in Variable
TE Imaging: Implications for FSE, RARE and EPI", Magn. Reson. Med.
1992, 28:9-24; and Ortendahl D. A., Kaufman L., Kramer D. M.,
"Analysis of Hybrid Imaging Techniques", Magn. Reson. Med. 1992,
26:155-173, of which are hereby incorporated by reference in their
entirety).
Nonetheless, if it were possible to substantially lengthen
echo-train durations beyond these limits, while achieving the
desired image contrast and limiting artifacts, it would represent a
useful and widely applicable advance.
Preliminary studies with the goal of lengthening the echo-train
duration in spin-echo-train-based acquisitions have been performed
by other researchers. Over a decade ago, Hennig (See Hennig J.,
"Multiecho Imaging Sequences with Low Refocusing Flip Angles", J.
Magn. Reson. 1988, 78:397-407, of which is hereby incorporated by
reference in its entirety) proposed the use of constant,
low-flip-angle refocusing RF pulses to introduce a T1 dependence to
the evolution of the echo train and thereby lengthen its usable
duration. More recently, this concept was extended by Alsop, who
derived variable flip-angle series based on the
"pseudosteady-state" condition of a constant signal level when T1
and T2 relaxation are neglected (See Alsop D. C., "The Sensitivity
of Low Flip Angle RARE Imaging", Magn. Reson. Med. 1997;
37:176-184, of which is hereby incorporated by reference in its
entirety). Alsop also found that the echo-train performance was
improved by using a signal evolution that decreased for the first
few echoes and was then constant, instead of being constant for the
complete echo train. Using these evolutions, artifact-free human
brain images with T2-weighting were acquired by Alsop. An 80-echo
train with a duration of 400 ms and asymptotic flip angles ranging
from 17.degree. to 90.degree. were used.
Turning to the present invention, a method and related apparatus is
provided for lengthening the usable echo-train duration for
spin-echo-train imaging substantially beyond that achievable with
the constant, low-flip-angle or pseudosteady-state approaches. The
present invention method and apparatus explicitly consider the T1
and T2 relaxation times for the tissues of interest and thereby
permit the desired image contrast to be incorporated into the
tissue signal evolutions corresponding to the long echo train.
Given the considerable role that spin-echo-train methods already
play in MR imaging, the present invention methodology will be of
significant importance.
SUMMARY OF THE INVENTION
This present invention comprises the methodology, related
apparatus, and computer useable medium (readable media) for using a
series of refocusing RF pulses with variable flip angles and,
optionally, variable phase angles, in a spin-echo-train MRI pulse
sequence wherein the flip-angle series is specifically designed to
achieve a prescribed signal evolution during the echo train for
selected T1 and T2 relaxation times. By employing such a series of
refocusing RF pulses, the usable duration of the echo train can be
extended substantially beyond that obtainable with conventional
methods. This increase in the echo-train duration can be used to
decrease the image acquisition time and/or increase the spatial
resolution.
In one aspect, the present invention features a method for
generating a pulse sequence for operating a magnetic resonance
imaging apparatus for imaging an object, the method comprising: a)
providing contrast-preparation, the contrast-preparation comprising
generating at least one of at least one radio-frequency pulse, at
least one magnetic-field gradient pulse, and at least one time
delay, whereby the contrast preparation encodes the magnetization
with at least one desired image contrast; b) calculating flip
angles and phases of refocusing radio-frequency pulses that are
applied in a data-acquisition step, wherein the calculation
provides desired prescribed signal evolution and desired overall
signal level, the calculation comprises: i) selecting values of T1
and T2 relaxation times and selecting proton density; ii) selecting
a prescribed time course of the amplitudes and phases of the
radio-frequency magnetic resonance signals that are generated by
the refocusing radio-frequency pulses; and ii) selecting
characteristics of the contrast-preparation step, the
data-acquisition step and a magnetization-recovery step, with the
exception of the flip angles and phases of the refocusing
radio-frequency pulses that are to be calculated; and c) providing
the data acquisition step based on a spin echo train acquisition,
the data-acquisition step comprises: i) an excitation
radio-frequency pulse having a flip angle and phase; ii) at least
two refocusing radio-frequency pulses, each having a flip angle and
phase as determined by the calculation step; and iii)
magnetic-field gradient pulses that encode spatial information into
at least one of the radio-frequency magnetic resonance signals that
follow at least one of the refocusing radio-frequency pulses; d)
providing magnetization-recovery, the magnetization-recovery
comprises a time delay to allow magnetization to relax; and e)
repeating steps (a) through (d) until a predetermined extent of
spatial frequency space has been sampled.
In a second aspect, the present invention features a magnetic
resonance imaging apparatus for generating a pulse sequence for
operating the apparatus for imaging an object, the apparatus
comprising a main magnet system for generating a steady magnetic
field; a gradient magnet system for generating temporary gradient
magnetic fields; a radio-frequency transmitter system for
generating radio-frequency pulses; a radio-frequency receiver
system for receiving magnetic resonance signals; a reconstruction
unit for reconstructing an image of the object from the received
magnetic resonance signals; and a control unit for generating
signals controlling the gradient magnet system, the radio-frequency
transmitter system, the radio-frequency receiver system, and the
reconstruction unit, wherein the control unit generates signals
causing: a) providing contrast-preparation, the
contrast-preparation comprising generating at least one of at least
one radio-frequency pulse, at least one magnetic-field gradient
pulse, and at least one time delay, whereby the contrast
preparation encodes the magnetization with at least one desired
image contrast; b) calculating flip angles and phases of refocusing
radio-frequency pulses that are applied in a data-acquisition step,
wherein the calculation provides desired prescribed signal
evolution and desired overall signal level, the calculation
comprises: i) selecting values of T1 and T2 relaxation times and
selecting proton density; ii) selecting a prescribed time course of
the amplitudes and phases of the radio-frequency magnetic resonance
signals that are generated by the refocusing radio-frequency
pulses; and ii) selecting characteristics of the
contrast-preparation step, the data-acquisition step and a
magnetization-recovery step, with the exception of the flip angles
and phases of the refocusing radio-frequency pulses that are to be
calculated; and c) providing the data acquisition step based on a
spin echo train acquisition, the data-acquisition step comprises:
i) an excitation radio-frequency pulse having a flip angle and
phase, ii) at least two refocusing radio-frequency pulses, each
having a flip angle and phase as determined by the calculation
step, and iii) magnetic-field gradient pulses that encode spatial
information into at least one of the radio-frequency magnetic
resonance signals that follow at least one of the refocusing
radio-frequency pulses; d) providing magnetization-recovery, the
magnetization-recovery comprises a time delay to allow
magnetization to relax; and e) repeating steps (a) through (d)
until a predetermined extent of spatial frequency space has been
sampled.
In a third aspect, the present invention features a computer
readable media carrying encoded program instructions for causing a
programmable magnetic resonance imaging apparatus to perform the
method discussed above in the first aspect of the invention.
Similarly, the invention features a computer program product
comprising a computer useable medium having computer program logic
for enabling at least one processor in a magnetic resonance imaging
apparatus to generate a pulse sequence, the computer program logic
comprising the method discussed above in the first aspect of the
invention.
Because the flip angles for the refocusing RF pulses that are
derived with this method are typically much less than 180.degree.
for a substantial portion of the total number of RF pulses, the
power deposition is much less than that corresponding to
180.degree. RF pulses, which are commonly used in conventional
spin-echo-train pulse sequences. This feature is particularly
important for high field MRI (>1.5 Tesla), wherein power
deposition is a critical pulse-sequence design factor for human
applications. The present invention permits long, closely-spaced
echo trains to be used for high-field imaging that would not
otherwise meet the safety guidelines established by the Food and
Drug Administration for power deposition in human MRI.
Another potentially useful feature of the present invention is
that, for specific forms of the encoding-gradient waveforms,
signals from moving or flowing materials are strongly attenuated,
even when the velocities are relatively low. A specific example of
this behavior is the attenuation of the signal from cerebrospinal
fluid (CSF) surrounding the cervical spinal cord due to its
oscillatory motion, which can be used to generate CSF-suppressed
T2-weighted MR images of the spinal cord without requiring
inversion-nulling of the CSF signal. Studies have indicated that
the full range of clinically-relevant cord lesions may not be
adequately detected using inversion-nulling of the CSF signal
(i.e., FLAIR) (See Hittmair K., Mallek R., Prayer D., Schindler E.
G., Kollegger H., "Spinal Cord Lesions in Patients with Multiple
Sclerosis: Comparison of MR Pulse Sequences", AJNR 1996,
17:1555-1565; and Keiper M. D., Grossman R. I., Brunson J. C.,
Schnall M. D., "The Low Sensitivity of Fluid-Attenuated
Inversion-Recovery MR in the Detection of Multiple Sclerosis of the
Spinal Cord", AJNR 1997, 18:1035-1039, of which are hereby
incorporated by reference in their entirety).
These and other objects, along with advantages and features of the
invention disclosed herein, will be made more apparent from the
description, drawings and claims that follow.
BRIEF DESCRIPTION OF THE DRAWINGS
The foregoing and other objects, features and advantages of the
present invention, as well as the invention itself, will be more
fully understood from the following description of preferred
embodiments, when read together with the accompanying drawings, in
which:
FIG. 1 is a schematic representation of a general spin-echo-train
MRI pulse sequence. This is an exemplary type of MRI pulse sequence
to which the invention applies. The present invention method can be
applied to various types of pulse sequences.
FIG. 2 shows an example of a prescribed signal evolution that can
be used to generate T2-weighted MR images of the brain or
spine.
FIG. 3 shows the variable-flip-angle series corresponding to FIG. 2
that was derived using the present invention methods as described
herein.
FIGS. 4-6 show example MR images obtained using the
variable-flip-angle series of FIG. 3 in a "turbo-SE" type
spin-echo-train pulse sequence; collectively, FIGS. 4-6 provide
examples of the potential utility of the present invention. In
particular, showing brain images obtained at 1.5 Tesla, FIGS. 4(A)
and 4(B)-4(C) compare T2-weighted two-dimensional and
three-dimensional SE images, respectively. Further, showing brain
images obtained at 3 Tesla, FIGS. 5(A)-5(C) show T2-weighted
sagittal, coronal, and axial images, respectively, reconstructed
from the same three-dimensional acquisition. Finally, FIG. 6 shows
a sagittal image of the cervical spinal cord obtained at 1.5
Tesla.
FIG. 7 illustrates a simplified exemplary embodiment of a MRI
apparatus for practicing the present invention. The present
invention method can be applied to various commercially available
MRI apparatuses.
FIG. 8 is an exemplary flowchart for a simplified preferred
implementation of the methods of the present invention.
FIGS. 9A-9B is an exemplary flowchart for a simplified preferred
implementation of the calculation methods of the present invention,
step 200.
FIG. 10 is an exemplary flowchart for a simplified preferred
implementation of the contrast-preparation methods of the present
invention.
FIG. 11 is an exemplary flowchart for a simplified preferred
implementation of the data-acquisition methods of the present
invention.
DETAILED DESCRIPTION OF THE INVENTION
In the following, first presented is an exemplary embodiment of a
MR apparatus for practicing the MR methods of the present invention
for imaging an object, moving or stationary. Following are
descriptions of preferred and alternative embodiments of the
methods of the present invention, including their exemplary
implementation as computer hardware, firmware, and/or software.
An Exemplary MR-Apparatus of the Present Invention
FIG. 7 illustrates a simplified schematic of a MR apparatus 1 for
practicing the present invention. The MR apparatus 1 includes a
main magnet system 2 for generating a steady magnetic field in an
examination zone(s) of the MR apparatus. The z-direction of the
coordinate system illustrated corresponds to the direction of the
steady magnetic field generated by the magnet system 2.
The MR apparatus also includes a gradient magnet system 3 for
generating temporary magnetic fields G.sub.x, G.sub.y and G.sub.z
directed in the z-direction but having gradients in the x, y or z
directions, respectively. With this magnetic gradient system,
magnetic-field gradients can also be generated that do not have
directions coinciding with the main directions of the above
coordinate system, but that can be inclined thereto, as is known in
the art. Accordingly, the present invention is not limited to
directions fixed with respect to the MR apparatus. In this
application, for ease of description, the directions x, y and z
(and the gradients along these directions) are used for the read
direction, the phase-encode direction and slice-selection direction
(or second phase-encode direction for 3D imaging),
respectively.
Also, while traditional commercial methods provide linear gradients
in the x, y, or z directions it is also possible not to utilize all
three of these linear gradients. For example, rather than using a
linear z gradient, one skilled in the art can use a z-squared
dependence or some other spatial dependence to provide desired
results.
The magnet systems 2 and 3 enclose an examination zone(s) which is
large enough to accommodate a part of an object 7 to be examined,
for example a part of a human patient. A power supply means 4 feed
the gradient magnet system 3.
The MR apparatus also includes an RF transmitter system including
RF transmitter coil 5, which generates RF pulses in the examination
zone and is connected via transmitter/receiver circuit 9 to a RF
source and modulator 6. The RF transmitter coil 5 is arranged
around the part of body 7 in the examination zone. The MR apparatus
also comprises an RF receiver system including an RF receiver coil
which is connected via transmitter/receiver circuit 9 to signal
amplification and demodulation unit 10. The receiver coil and the
RF transmitter coil 5 may be one and the same coil. The MR
apparatus also includes an amplification and demodulation unit 10,
which, after excitation of nuclear spins in a part of the body
placed within the examination space by RF pulses, after encoding by
the magnetic-field gradients and after reception of the resulting
MR signals by the receiver coil, derives sampled phases and
amplitudes from the received MR signals. An image reconstruction
unit 12 processes the received MR imaging signals to, inter alia,
reconstruct an image by methods well-known in the art, such as by
Fourier transformation. It should be appreciated by one skilled in
the art that various reconstruction methods may be employed besides
the Fourier Transform (FT) depending on factors such as the type of
signal being analyzed, the available processing capability, etc.
For example, but not limited thereto, the present invention may
employ Short-Time FT (STFT), Discrete Cosine Transforms (DCT), or
wavelet transforms (WT). By means of an image processing unit 13,
the reconstructed image is displayed, for example, on monitor 14.
Further, the image reconstruction unit can optionally process MR
navigator signals to determine the displacement of a portion of the
patient.
The MR apparatus also includes a control unit 11 that generates
signals for controlling the RF transmitter and receiver systems by
means of a modulator 6, the gradient magnetic field system by means
of the power supply means 4, an image reconstruction unit 12 and an
image processing unit 13. In a preferred embodiment, the control
unit 11 (and other control elements in the MR apparatus) are
implemented with programmable elements, such as one or more
programmable signal processors or microprocessors, communicating
over busses with supporting RAM, ROM, EPROM, EEPROM, analog signal
interfaces, control interfaces, interface to computer-readable
media and so forth. These programmable elements are commanded by
software or firmware modules loaded into RAM, EPROM, EEPROM or ROM,
written according to well-known methods to perform the real-time
processing required herein, and loaded from computer-readable media
(or computer useable medium), such as magnetic disks or tapes, or
optical disks, or network interconnections, removable storage
drives, or so forth. The present invention may be implemented using
hardware, software or a combination thereof and may be implemented
in one or more computer systems or processing systems, such as
personal digit assistants (PDAs), for various applications, e.g.,
remote care and portable care practices.
In a less preferred embodiment, the control unit that directs a MR
apparatus for practicing the present invention can be implemented
with dedicated electronic components in fixed circuit arrangements.
In this case, these dedicated components are arranged to carry out
the method described above. For example, the invention is
implemented primarily in hardware using, for example, hardware
components such as application specific integrated circuits(ASICs).
Implementation of the hardware state machine to perform the
functions described herein will be apparent to persons skilled in
the relevant art(s).
In particular, the control unit commanded by its loaded software
causes the generation of MR signals by controlling the application
of MR pulse sequences, which comprise RF-pulses, time delays and
temporary magnetic-field gradient pulses. These pulse sequences are
generated according to the methods of the present invention as
subsequently described, and generally include 2D and 3D imaging
pulse sequences and optionally navigator pulse sequences for
determining the displacement of the patient or material.
Furthermore, according to alternate embodiments of the present
invention, the MR apparatus also optionally includes various other
units (not illustrated) from which the state of motion of the part
of the patient being imaged can be measured. These can include
sensors directly indicating the instantaneous state of motion of
the part of the patient being imaged, such as a chest belt for
directly indicating chest displacement during respiration, or
MR-active micro-coils whose position can be tracked, or optical
means, or ultrasound means, or so forth. These units can also
include sensors indirectly indicating the instantaneous state of
motion of the part of the patient being imaged. For example,
electrocardiogram and peripheral pulse sensors measure the temporal
progress of the cardiac cycle, and permit inference of the actual
state of motion of the heart from knowledge of cardiac
displacements associated with each phase of the cardiac cycle. When
these sensors are present to measure the state of motion, the
control unit need not generate navigator pulse sequences.
Moreover, the control unit 11 may also include a communications
interface 24. The communications interface 24 allows software and
data to be transferred between and among, via communication path
(i.e. channel) 28, the control unit 11, reconstruction unit 12,
image processing unit 13, and monitor 14 and external devices.
Examples of the communications interface 24 may include a modem, a
network interface (such as an Ethernet card), a communications
port, a PCMCIA slot and card, etc. Software and data transferred
via communications interface 24 are in the form of signals which
may be electronic, electromagnetic, optical or other signals
capable of being received by communications interface 24. The
signals are provided to communications interface 24 via the
communications path (i.e., channel) 26. The channel 26 carries
signals and may be implemented using wire or cable, fiber optics, a
phone line, a cellular phone link, a RF link, IR link and other
communications channels.
The preferred embodiments of the present invention may be
implemented as software/firmware/hardware with various MR
apparatuses, and methods, as one skilled in the art would
appreciate. Other exemplary apparatuses and methods, but not
limited thereto, are disclosed in the following U.S. patents, of
which are hereby incorporated by reference in their entirety
herein: U.S. Pat. No. 6,230,039 B1--Staber et. al.; U.S. Pat. No.
5,749,834--Hushek; and U.S. Pat. No. 5,656,776--Kanazawa.
The Methods of the Present Invention
Turning now to FIG. 1, pertaining to the general methods of this
invention, first in a preferred embodiment, the present invention
applies to magnetic resonance imaging MRI) using a
"spin-echo-train" MRI pulse sequence, which is a pulse sequence
that generates more than one spin echo for each desired image
contrast following each excitation RF pulse. Any form of the
applied spatial-encoding gradient waveforms, variations in the
spacing between refocusing RF pulses, and/or any combination of
non-selective, spatially-selective, and spectrally-selective RF
pulses are applicable to the present invention methods as long as
their effects on the magnetization are appropriately considered in
the derivation of the variable-flip-angle series. A contrast
preparation phase, such as an inversion RF pulse followed by a time
delay, may precede the acquisition phase of the pulse sequence.
Still referring to FIG. 1, there is shown a schematic
representation of a general spin-echo-train MRI pulse sequence.
This is an exemplary type of MRI pulse sequence to which the
invention applies. The representation is of a general
spin-echo-train MRI pulse sequence showing the excitation RF pulse
(.alpha.) and the first three (.beta..sub.1, .beta..sub.2,
.beta..sub.3) of n refocusing RF pulses, where n>1. The RF pulse
waveforms are drawn as rectangular for simplicity, but they may be
amplitude and/or phase modulated as appropriate for the desired
application. The echo spacing (ESP) may be fixed or may vary
between echoes. The contrast preparation module 20 denotes the
optional use of additional RF pulses, gradient pulses and/or time
delays (e.g., an inversion pulse followed by a time delay) to
permit additional control over the image contrast. The boxes on the
G.sub.select axis, referenced as 31, 32, 33 and 34, symbolically
denote the optional use of magnetic-field gradient waveforms for
spatial and/or spatial-spectral selection. The boxes on the
G.sub.encode axis, referenced as 41, 42, and 43, symbolically
denote the magnetic-field gradient waveforms used for spatial
encoding. The contrast preparation (if any) and the echo train are
repeated as necessary to collect the desired k-space data. The
timing parameters and the number of echoes may vary between
repetitions.
For a spin-echo-train pulse sequence, an object of the present
invention is to derive a series of refocusing RF pulses with
variable flip angles, and, optionally, variable phase angles, that
yields a specifically prescribed signal evolution during the echo
train for selected T1 and T2 relaxation times. To achieve this, a
mathematical model of the pulse sequence, incorporating the
specific timing, gradient and RF parameters of choice, is used to
calculate the signal evolution during the echo train. This model
would typically be implemented in the form of a computer program
that is based on the established mathematical equations that
describe the behavior of the magnetization during a pulse sequence.
See Haacke E. M., Brown R. W., Thompson M. R., Venkatesan R.,
"Magnetic Resonance Imaging: Physical Principles and Sequence
Design", John Wiley & Sons, New York, 1999, of which is hereby
incorporated by reference in its entirety. Other exemplary
spin-echo-train MR imaging methods are disclosed in the following
U.S. patents, of which are hereby incorporated by reference in
their entirety herein: U.S. Pat. No. 5,680,045--Feinberg; U.S. Pat.
No. 5,612,619--Feinberg; U.S. Pat. No. 5,541,511--Henning; U.S.
Pat. No. 5,315,249--Le Roux et al.; U.S. Pat. No.
5,270,654--Feinberg et al.; U.S. Pat. No. 4,901,020--Ladebeck et
al. and U.S. Pat. No. 4,818,940--Henning et al.
Given such a computer-based calculation tool, the process for
deriving this flip-angle series can be generally summarized in the
following four steps (steps I-IV) briefly discussed below. Firstly,
STEP I, the pulse sequence timing parameters (e.g., repetition
time, echo spacing(s), other time delays), the pulse sequence
magnetic-field gradient configuration, the desired shape of the
prescribed signal evolution during the echo train, the T1 and T2
relaxation parameters and the proton density for the "target"
tissue, and a target signal intensity are chosen. The signal
evolution may assume any physically-realizable shape. Some
examples, but not limited thereto, include: a constant; a linear
decay; an exponential decay; a linear or exponential decay for the
initial portion and a constant for the remainder; and a linear or
exponential decay for the initial portion, a constant for the
second portion and a linear or exponential decay for the remainder.
The T1, T2 and proton density for the target tissue may equal those
for a specific biological tissue (e.g., brain gray matter) or
material, or they may be arbitrarily chosen. The target signal
intensity is the desired signal intensity corresponding to a
specific echo in the echo train (e.g., the first or the middle
echo).
Secondly, STEP II, the flip angle .beta..sub.i (see FIG. 1) which
yields the desired signal intensity for the i.sup.th echo interval
is determined, where i ranges from 1 to the number of refocusing RF
pulses in the echo train. This flip angle can be calculated using
any appropriate method such as a "brute-force" search or interval
bisection and interpolation. See Forsythe G. E., Malcolm M. A.,
Moler C. B., "Computer Methods for Mathematical Computations",
Prentice-Hall, Englewood Cliffs, 1977, of which is hereby
incorporated by reference in its entirety.
Thirdly, STEP III, the pulse number i is incremented and the second
step is repeated until all flip angles for a given echo train are
calculated. If, for any value of i, the desired signal intensity
for the i.sup.th echo interval cannot be achieved, the target
signal intensity is reduced and the calculation process is
restarted.
Fourthly, STEP IV, if the pulse sequence under consideration
requires more than one repetition of the echo train to acquire the
desired k-space data, the second and third steps are repeated as
necessary until a steady state of the magnetization is reached.
After a given series of variable flip angles are derived, the
target signal intensity can be incremented until the maximum value
for which the prescribed signal-evolution shape can be realized is
reached, thus allowing determination of the maximum signal and/or
contrast values that can be obtained for a specific pulse sequence
configuration and signal evolution.
Next, exemplary hardware, firmware and software implementations of
the methods of the present invention are discussed.
FIG. 8 illustrates a preferred method for practicing the invention
as implemented by, for example, software loaded into the control
unit of the MR apparatus. Once the process starts and initializes,
at step 200, the contrast-preparation is provided by generating at
least one of a RF pulse, magnetic-field gradient pulse, and/or time
delay. The contrast-preparation encodes the magnetization with at
least one desired image contrast.
During step 300, flip angles and phases are calculated for
refocusing RF pulses that are applied in subsequent
data-acquisition steps so as to yield--for selected values of T1
and T2 relaxation times and proton density--a prescribed time
course for the amplitudes and phases of the RF magnetic resonance
signals that are generated by the refocusing RF pulses.
During step 400, data-acquisition is achieved based on an
echo-train acquisition, comprising the following: i) an excitation
RF pulse having a flip angle and phase; ii) at least two refocusing
RF pulses, each having a flip angle and phase as determined by the
calculation step; and iii) magnetic-field gradient pulses that
encode spatial information into at least one of the RF magnetic
resonance signals that follow at least one of the at least two
refocusing RF pulses.
Also, in step 500, magnetization-recovery is provided whereby the
magnetization-recovery comprises a time delay to allow
magnetization to relax. Finally, as illustrated by step 550, the
aforementioned method is repeated until a predetermined extent of
spatial-frequency space has been sampled.
It is important to appreciate that the various steps discussed
herein need not be performed in the illustrated order, and in fact
it may be preferred to perform the steps, at least in part,
simultaneously or omit some of the illustrated steps, at least in
part.
Next, turning to FIGS. 9A-9B, an exemplary method for the
calculating step 300 is provided. In step 310, T1, T2, and proton
density are chosen, and in step 320, a desired prescribed signal
evolution which describes the time course of the signal amplitudes
and phases, is also chosen. Turning to steps 330 and 340, the
characteristics of the contrast-preparation and data-acquisition,
respectively, are chosen (additional details shall be discussed
with FIGS. 10-11). Provided in step 350, the characteristics of the
magnetization-recovery period are chosen. Accordingly, at step 360,
the process of calculating the individual flip angles starts and is
initialized with thermal equilibrium magnetization. At step 370,
the magnetization, M.sub.1, is calculated that exists immediately
after the contrast-preparation and excitation RF pulse are applied.
At step 380, starting with M.sub.1 which is the input magnetization
for the first refocusing RF pulse, the flip angle and phase are
calculated for the current refocusing RF pulse that yields the
desired corresponding signal amplitude and phase, and this process
is repeated until the last refocusing RF pulse is achieved, step
385. If the last pulse is achieved, then step 390 permits
relaxation during the magnetization-recovery period. In steps 392
and 394, the process checks for a single-shot pulse sequence method
and whether steady state has been achieved. This accounts for the
effects of multiple applications of the contrast-preparation,
data-acquisition and magnetization-recovery steps if required to
sample the desired extent of spatial-frequency space. As used
herein, the "steady state" of magnetization is a state created by
certain fast (with repeat times short compared to relaxation times)
imaging pulse sequences during which both the longitudinal and the
transverse components of the nuclear magnetization exhibit a steady
temporal state. Once steady state is satisfied the process checks
whether the target signal has been achieved, step 396, so as to
increment across the overall signal level.
Turning to the exemplary contrast-preparation process as shown in
FIG. 10, at step 331, the following are chosen: flip angle, phase,
waveform and the time of application of any RF pulses. In step 332,
the following are chosen: strength, duration, time-dependence, axis
and time of application of any magnetic-field gradient pulses.
Moreover, in step 333, the following are chosen: duration and time
of application of any time delays.
Turning to the exemplary data-acquisition process as shown in FIG.
11, at step 341, the following are chosen: the flip angle and phase
of the excitation RF pulse. Also, at steps 342, 343, and 344, the
times between all RF pulses; number of refocusing RF pulses; and
configuration of spatial-encoding magnetic-field gradient pulses
are chosen, respectively.
EXAMPLES
Specific implementations of the present invention methodology are
useful to illustrate its nature. These examples are non-limiting
and are offered as exemplary only. For this purpose, set forth
herein are experimental studies in which the present invention
method was used to generate variable-flip-angle series for
three-dimensional (3D) T2-weighted MR imaging of the human brain
and cervical spine using a "turbo-SE" type (i.e., RARE-as set forth
in Henning et al., Magn. Res. Med. 1986, 3:823-833) spin-echo-train
pulse sequence, of which is hereby incorporated by reference in its
entirety. Brain studies were performed at 1.5 Tesla and 3 Tesla;
spine studies were performed at 1.5 Tesla. MR images were obtained
using a 1.5-Tesla commercial whole-body imager (MAGNETOM SYMPHONY,
Siemens Medical Systems, Iselin, N.J.) or a 3-Tesla commercial
whole-body imager (MAGNETOM ALLEGRA, Siemens Medical Systems,
Iselin, N.J.). The standard head RF coil supplied with the imager
was used. Informed consent was obtained from all subjects prior to
imaging.
Turning to FIGS. 2-3, FIG. 2 shows an example of a prescribed
signal evolution for gray matter that can be used to generate
T2-weighted MR images of the brain. The evolution consists of the
following: exponential decay during the first 20 echoes with decay
constant of 114 ms, constant for 66 echoes, and exponential decay
during the remaining echoes with decay constant of 189 ms. FIG. 3
shows the corresponding variable-flip-angle series that was derived
using the present invention methods as described herein. Using an
interactive computer-based (Ultra-60 workstation; Sun Microsystems,
Inc.) theoretical model, and the prescribed signal evolution for
brain gray matter, at 1.5 Tesla (see FIG. 2), the four-step process
described above was used to derive the corresponding
variable-flip-angle series depicted in FIG. 3. The pulse-sequence
parameters included an echo train length of 160, an echo spacing of
4.1 ms (fixed), a total echo-train duration of 656 ms, a repetition
time of 2750 ms and an effective echo time of 328 ms.
Example No. 1
FIGS. 4B-4F show an example of MR brain images obtained at 1.5
Tesla using the variable-flip-angle series of FIG. 3 in a
"turbo-SE" type spin-echo-train pulse sequence; collectively. In
particular, the T2-weighted two-dimensional and three-dimensional
SE images of FIGS. 4(A) and 4(B)-4(C), respectively, were obtained
from a 59 year old volunteer for demonstrating age-related
non-specific white-matter lesions. As can be observed, arrows mark
several of these lesions. The adjacent 1-mm thick 3D images, as
shown in FIGS. 4B-4D, correspond to the single 3-mm thick 2D image
in FIG. 4A. In the 3D images, the phase-encoding direction
corresponding to the 160-echo train is left-to-right in FIGS. 4B-4D
and 4F. No image artifacts secondary to this very long spin-echo
train are apparent. Pulse sequence parameters for the 10 minute 3D
acquisition included the following: repetition time/effective echo
time, 2750/328 ms; matrix, 256.times.160.times.216; field of view,
25.6.times.16.0.times.21.6 cm; voxel size, 1.0.times.1.0.times.1.0
mm; echo spacing, 4.1 ms; echo train length, 160; and full-Fourier
acquisition. Pulse sequence parameters for the 14.8 minute 2D
acquisition included the following: repetition time/first echo
time/second echo time, 2750/20/80 ms; matrix, 256.times.160; field
of view, 25.6.times.16.0 cm; section thickness, 3.0 mm; number of
sections, 54; full-Fourier acquisition; first-order flow
compensation; and reduced bandwidth on second echo.
In summary, using the variable-flip-angle series of FIG. 3, the
T2-weighted 3D images were obtained at 1.5 Tesla from the brain of
a healthy volunteer, and were compared to images from a 2D
conventional-SE pulse sequence (see FIG. 4). The images in FIG. 4
exhibit two important features: (1) the very long spin-echo-train
images (FIGS. 4B-4F) display high contrast between the age-related
lesions in the brain of this volunteer and surrounding normal
appearing white matter, indicating that this echo train shall
provide clinically useful contrast characteristics that appear very
similar to those for conventional T2-weighed SE images (FIG. 4A);
and (2) the thin 1-mm sections provide an improved definition of
lesion location and extent; the lesions seen in the 2D image
appear, to varying degrees, in three adjacent 1-mm sections.
Furthermore, the overall image quality for the very long
spin-echo-train and conventional-SE images is similar, despite the
much thinner sections of the former.
Finally, referring to FIGS. 4E-4F, such figures depict the largest
lesion in sagittal and coronal orientations, respectively, this
demonstrates the capability of the 3D acquisition to provide
high-quality images in arbitrary orientations.
Example No. 2
Next, referring to FIGS. 5A-5C, using the same pulse-sequence
parameters as described above in FIGS. 2-4, T2-weighted images were
also obtained at 3 Tesla from the brain of a healthy volunteer. The
three 1-mm thick images were all reconstructed from the same 3D
acquisition. These images appeared similar to those obtained at 1.5
Tesla, but exhibited higher signal-to-noise ratios. Of particular
importance, the partial-body and local values for the specific
absorption rate (SAR) were 1.29 W/kg and 3.16 W/kg, respectively,
compared to the FDA limits for partial-body and local SAR of 3.0
and 8.0 W/kg, respectively. The SAR values at 3 Tesla were much
less than the FDA limits, indicating that there remains substantial
latitude in the pulse-sequence design from the perspective of power
deposition, including the possibility for even more refocusing RF
pulses per excitation. Thus, according to the present invention,
although the use of spin-echo-train methods has been restricted at
high fields, such as 3 Tesla, due to power deposition limits, very
long spin-echo trains based on prescribed signal evolutions permit
high-quality brain images to be acquired at 3 Tesla with power
deposition well below the FDA limits.
Example No. 3
Referring to FIG. 6, as the final example, FIG. 6 shows a
T2-weighted sagittal image of the cervical spinal cord obtained at
1.5 Tesla from a healthy volunteer, again using a 160-echo train.
The quality of cervical-spine images from T2-weighted MRI
techniques is often compromised by artifacts arising from the
pulsatile motion of the CSF surrounding the cord. One potential
solution to this problem is to use FLAIR imaging. See Hajnal et al.
While this technique can completely suppress the signal from CSF,
there remains some concern about its ability to depict the full
range of clinically-relevant lesions. See Hittmair et al. and
Keiper et al. As illustrated in FIG. 6, an alternative is to use a
T2-weighted technique with a very long spin-echo train based on a
prescribed signal evolution, as provided by the present invention.
The signal from CSF is uniformly suppressed without generating
motion artifacts. The combination of the long echo train and the
relatively low flip angles of the refocusing RF pulses results in
suppression of even slowly moving fluid. The "dark-CSF" image in
FIG. 6 differs from a FLAIR image, among other things, in an
important way. With FLAIR, the CSF is suppressed based on its long
TI. Hence, the signals from any other tissues with relatively long
T1s will be diminished. This is one potential explanation for the
problems in depicting certain lesions with FLAIR--these lesions may
have long T1 components. In contrast, turning to the present
invention, the CSF suppressed in FIG. 6 is solely due to its
motion; long T1 lesions in the cord will be unaffected.
An advantage of the present invention is that it provides a method,
apparatus, and computer useable medium (readable media) to extend
the usable duration of the echo train in magnetic resonance imaging
pulse sequences such as RARE, turbo-spin-echo, fast-spin-echo or
GRASE, substantially beyond that obtainable with conventional
methods. This increase in the echo-train duration can be used to
decrease the image acquisition time and/or increase the spatial
resolution. The power deposition achieved with this technique is
much less than that for conventional spin-echo-train pulse
sequences, and thus the invention shall be especially useful, among
other things, for human imaging applications at high magnetic field
strengths.
Another advantage of the present invention is that it improves the
imaging of various objects and zones, including the brain. The
present invention is also applicable to other regions of the body
such as the spinal cord or joints. In particular, the present
invention enables high-resolution 3D imaging of the brain with
clinically-reasonable acquisition times, which is useful for
quantitative imaging of disseminated diseases such as multiple
sclerosis. For these diseases, high-resolution 3D imaging provides
a valuable tool for monitoring disease progression and response to
therapy during treatment or drug trials. The present invention is
also useful for non-human applications of magnetic resonance, such
as imaging of materials (e.g., plants or food products) or animal
models of disease at high field.
Further yet, an advantage of the present invention is that it
provides a means to shorten image acquisition times and/or increase
spatial resolution for widely-used spin-echo-train magnetic
resonance imaging techniques. Such improvements will in turn make
it feasible to obtain images with certain valuable combinations of
resolution and image contrast which have not been practical
heretofore. In addition, the present invention permits
spin-echo-train methods to be used for high-field imaging that
would not otherwise meet the safety guidelines established by the
Food and Drug Administration for power deposition in human MRI.
Finally, another advantage of the present invention method and
apparatus is that it explicitly considers the T1 and T2 relaxation
times for the tissues of interest and thereby permits the desired
image contrast to be incorporated into the tissue signal evolutions
corresponding to the long echo train. Given the considerable role
that spin-echo-train methods already play in MR imaging, the
present invention methodology will be of significant
importance.
All US patents and US patent applications cited herein are
incorporated herein by reference in their entirety and for all
purposes to the same extent as if each individual patent or patent
application was specifically and individually indicated to be
incorporated by reference in its entirety for all purposes.
The invention may be embodied in other specific forms without
departing from the spirit or essential characteristics thereof. The
foregoing embodiments are therefore to be considered in all
respects illustrative rather than limiting of the invention
described herein. Scope of the invention is thus indicated by the
appended claims rather than by the foregoing description, and all
changes which come within the meaning and range of equivalency of
the claims are therefore intended to be embraced herein.
* * * * *
References