U.S. patent application number 13/569573 was filed with the patent office on 2012-11-29 for magnetic resonance imaging apparatus and magnetic resonance imaging method.
This patent application is currently assigned to TOSHIBA MEDICAL SYSTEMS CORPORATION. Invention is credited to Hitoshi KANAZAWA, Mitsue MIYAZAKI.
Application Number | 20120302872 13/569573 |
Document ID | / |
Family ID | 39584978 |
Filed Date | 2012-11-29 |
United States Patent
Application |
20120302872 |
Kind Code |
A1 |
MIYAZAKI; Mitsue ; et
al. |
November 29, 2012 |
MAGNETIC RESONANCE IMAGING APPARATUS AND MAGNETIC RESONANCE IMAGING
METHOD
Abstract
A magnetic resonance imaging apparatus includes an imaging
condition setting unit, a scan performing unit and a blood flow
image generating unit. The imaging condition setting unit sets a
sequence accompanying application of a motion probing gradient
pulse as an imaging condition. The scan performing unit performs an
imaging scan according to the sequence. The blood flow image
generating unit generates a blood flow image based on data acquired
by the imaging scan.
Inventors: |
MIYAZAKI; Mitsue; (Mount
Prospect, IL) ; KANAZAWA; Hitoshi; (Utsunomiya-Shi,
JP) |
Assignee: |
TOSHIBA MEDICAL SYSTEMS
CORPORATION
OTAWARA-SHI
JP
KABUSHIKI KAISHA TOSHIBA
TOKYO
JP
|
Family ID: |
39584978 |
Appl. No.: |
13/569573 |
Filed: |
August 8, 2012 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
11790484 |
Jul 3, 2007 |
|
|
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13569573 |
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Current U.S.
Class: |
600/419 |
Current CPC
Class: |
G01R 33/5635 20130101;
G01R 33/4818 20130101; G01R 33/5617 20130101; A61B 5/055 20130101;
G01R 33/5673 20130101; G01R 33/5614 20130101; G01R 33/5616
20130101; G01R 33/4824 20130101; G01R 33/56509 20130101; A61B
5/7285 20130101; A61B 5/0263 20130101; G01R 33/56341 20130101 |
Class at
Publication: |
600/419 |
International
Class: |
A61B 5/026 20060101
A61B005/026; A61B 5/055 20060101 A61B005/055 |
Foreign Application Data
Date |
Code |
Application Number |
Apr 25, 2006 |
JP |
120382/2006 |
Claims
1. A magnetic resonance imaging (MRI) apparatus comprising: an
imaging condition setting unit configured to set an MRI data
acquisition sequence accompanying application of a motion probing
gradient (MPG) pulse as an imaging condition; a scan performing
unit configured to perform an MRI data acquisition scan after
application of the MPG according to the set sequence; and a blood
flow image generating unit configured to generate a blood flow
image based on MRI data acquired by the MRI scan.
2. A magnetic resonance imaging apparatus as in claim 1 wherein:
the imaging condition setting unit is configured to set an imaging
condition using an MRI data acquisition sequence that is
independent from blood travel direction in a target blood
vessel.
3. A magnetic resonance imaging apparatus as in claim 2, wherein
said imaging condition setting unit is configured to set the
imaging condition by using one of (a) a balanced SSFP sequence and
(b) a PROPELLER type.
4. A magnetic resonance imaging apparatus as in claim 1 wherein the
imaging condition setting unit is configured to set an MRI data
acquisition preparation sequence with an imaging condition for
applying plural motion probing gradient (MPG) pulses, each MPG
pulse having a mutually different intensity and to acquire MRI data
using each different MPG pulse intensity, said MRI apparatus
further comprising: a preparation scan performing unit configured
to perform a preparation scan according to the set preparation
sequence; and a reference blood flow image generating unit
configured to generate blood flow images for a reference based on
MRI data corresponding to each MPG pulse intensity, the MRI data
for the reference being acquired by the preparation scan.
5. A magnetic resonance imaging apparatus as in claim 4, wherein
said scan performing unit is configured to perform an MRI scan
using an MRI data acquisition sequence accompanying application of
an MPG pulse having an intensity based on blood flow images for the
reference.
6. A magnetic resonance imaging apparatus as in claim 1 wherein:
said imaging condition setting unit is configured to set MRI data
acquisition timing as an imaging condition for acquiring data near
the center of k-space during a systole and during a diastole in a
heart beat cycle; said scan performing unit is configured to
perform an MRI scan according to the set imaging condition; and
said blood flow image generating unit is configured to generate a
blood flow image based on compiled MRI data acquired during the
systole and during the diastole.
7. A magnetic resonance imaging apparatus as in claim 1 wherein:
said imaging condition setting unit is configured to be able to
change intensities of the MPG pulse in three directions of (1) a
gradient magnetic field direction for slice encoding, (2) a
gradient magnetic field direction for phase encoding and (3) a
gradient magnetic field direction for readout.
8. A magnetic resonance imaging apparatus as in claim 1 wherein:
said imaging condition setting unit is configured to be able to set
intensities of the MPG pulse in three directions of (1) a gradient
magnetic field direction for slice encoding, (2) a gradient
magnetic field direction for phase encoding and (3) a gradient
magnetic field direction for readout in accordance with blood
travel direction of a target blood vessel.
9. A magnetic resonance imaging apparatus as in claim 1 wherein:
said imaging condition setting unit is configured to set the
imaging condition for a scroll acquisition of the MRI data.
10. A magnetic resonance imaging apparatus as in claim 1 wherein:
the scan performing unit is configured to apply the MPG pulse
between an excitation pulse and a recovery pulse.
11. A magnetic resonance imaging apparatus as in claim 10 wherein:
the scan performing unit is configured to apply another pulse
between the MPG pulse and the MRI scan.
12. A magnetic resonance imaging apparatus as in claim 11 wherein:
the scan performing unit is configured to apply a fat saturation
pulse as said another pulse.
13. A magnetic resonance imaging (MRI) apparatus comprising: an
imaging condition setting unit configured to set an MRI data
acquisition sequence accompanying application of a flow encode
pulse as an imaging condition: a scan performing unit configured to
perform an MRI scan after application of the flow encode pulse,
according to the set sequence; and a blood flow image generating
unit configured to generate a non-contrast-enhanced blood flow
image based on data acquired by the MRI scan.
14. A magnetic resonance imaging apparatus as in claim 13 wherein:
the scan performing unit is configured to apply the flow encode
pulse between an excitation pulse and a recovery pulse.
15. A magnetic resonance imaging apparatus as in claim 14 wherein:
the scan performing unit is configured to apply another pulse
between the flow encode pulse and the imaging scan.
16. A magnetic resonance imaging apparatus as in claim 15 wherein:
the scan performing unit is configured to apply a fat saturation
pulse as said another pulse.
17. A magnetic resonance imaging (MRI) method comprising: an
imaging condition setting unit configured to set an MRI data
acquisition sequence accompanying application of a motion probing
gradient (MPG) pulse as an imaging condition; a scan performing
unit configured to perform an MRI data acquisition scan after
application of the MPG according to the set sequence; and a blood
flow image generating unit configured to generate a blood flow
image based on MRI data acquired by the MRI scan.
18. A magnetic resonance imaging method as in claim 17 comprising:
the imaging condition setting unit is configured to set an imaging
condition using an MRI data acquisition sequence that is
independent from blood travel direction in a target blood
vessel.
19. A magnetic resonance imaging as in claim 17 wherein the imaging
condition setting unit is configured to set an MRI data acquisition
preparation sequence with an imaging condition for applying plural
motion probing gradient (MPG) pulses, each MPG pulse having a
mutually different intensity and to acquire MRI data using each
different MPG pulse intensity, said MRI apparatus further
comprising: a preparation scan performing unit configured to
perform a preparation scan according to the set preparation
sequence; and a reference blood flow image generating unit
configured to generate blood flow images for a reference based on
MRI data corresponding to each MPG pulse intensity, the MRI data
for the reference being acquired by the preparation scan.
20. A magnetic resonance imaging method as in claim 17 comprising:
said imaging condition setting unit is configured to set MRI data
acquisition timing as an imaging condition for acquiring data near
the center of k-space during a systole and during a diastole in a
heart beat cycle; said scan performing unit is configured to
perform an MRI scan according to the set imaging condition; and
said blood flow image generating unit is configured to generate a
blood flow image based on compiled MRI data acquired during the
systole and during the diastole.
21. A magnetic resonance imaging method comprising: an imaging
condition setting unit configured to set an MRI data acquisition
sequence accompanying application of a flow encode pulse as an
imaging condition: a scan performing unit configured to perform an
MRI scan after application of the flow encode pulse, according to
the set sequence; and a blood flow image generating unit configured
to generate a non-contrast-enhanced blood flow image based on data
acquired by the MRI scan.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a division of U.S. application Ser. No.
11/790,484 filed Jul. 3, 2007, pending, which application claims
priority based on Japanese Patent Application No. 2006-120382 filed
Apr. 25, 2006, the entire contents of both of which are hereby
incorporated by reference in this application.
BACKGROUND
[0002] 1. Technical Field
[0003] The present exemplary embodiments relate to an MRI (magnetic
resonance imaging) apparatus and a magnetic resonance imaging
method which magnetically excites nuclear spins of an object with
an RF (radio frequency) signal having the Larmor frequency and
reconstructs an image based on an MR (magnetic resonance) signal
generated due to the excitation and, more particularly, to a
magnetic resonance imaging apparatus and a magnetic resonance
imaging method, which perform a non-contrast-enhanced MRA (magnetic
resonance angiography) obtaining a blood flow image without using a
contrast medium.
[0004] 2. Related Art
[0005] Magnetic resonance imaging is an imaging method which
magnetically excites nuclear spins of an object set in a static
magnetic field with an RF signal having the Larmor frequency and
reconstructs an image based on an MR signal generated due to the
excitation.
[0006] In the field of magnetic resonance imaging, as a method of
obtaining an image of a blood flow, MRA is known. MRI that does not
use a contrast medium is referred to as non-contrast-enhanced MRA.
As non-contrast-enhanced MRA, an FBI (fresh blood imaging) method
which performs in synchronism with an ECG (electrocardiogram)
signal to capture a rapid blood flow ejected from the heart,
thereby satisfactorily representing a blood vessel, has been
devised (for example, refer to Japanese Patent Application
(Laid-Open) No. 2000-5144).
[0007] Such non-contrast-enhanced MRA using the FBI method creates
a difference between image data acquired with different delay times
of ECG synchronization so that an MRA image in which an artery and
a vein are distinguished from each other is obtained. In addition,
in the FBI method, a flow-spoiled FBI method in which an artery
signal is suppressed during systole by applying a spoiler pulse has
been devised. That is, according to the flow-spoiled FBI method,
the difference of artery signals during diastole and systole of the
cardiac muscle is used for imaging.
[0008] Further, in the FBI method, in order to extract a blood flow
of low flow velocity, a flow-dephasing method in which a gradient
pulse (Gspoil) is applied in a RO (readout) direction, and a
dephase pulse or refocusing pulse is applied to a gradient magnetic
field pulse has been designed (for example, refer to
JP-A-2003-135430). According to the flow-dephasing method, due to
the dephase pulse or the refocusing pulse, it is possible to
increase the relative signal difference between a signal value from
the blood flow of high velocity and a signal value from the blood
flow of low velocity. Therefore, it is possible to clearly
distinguish the artery and the vein from each other on the basis of
the relative signal difference.
[0009] That is, in order to distinguish the artery and the vein, it
is important to increase the difference between signals during
diastole with respect to signals during systole. In order to
increase the difference between signals in diastole and systole, it
is needed to make intensity of the signal from the blood flow in
systole small. However, especially in case of MRA for a lower limb,
since flow velocities of both venous blood and arterial blood are
slow, it is difficult to distinguish the artery and the vein due to
decrease of signal difference between diastole and systole.
Accordingly, a gradient pulse having a proper intensity in the RO
direction is set, and the blood flow signal from the artery in
systole is suppressed by the set gradient pulse. Thus, it is
possible to increase a difference of signals from the artery
between diastole and systole. In this state, the blood flow signal
in diastole is collected. Subtraction processing and/or NIP
(maximum intensity projection) processing are performed on the
blood flow signals collected in diastole, and only the artery is
represented.
[0010] Further ECG-prep as a related technology used with FBI
method has been devised to measure an appropriate delay time for
ECG synchronization (for example, refer to U.S. Pat. No.
6,144,201). The ECG-prep performs an ECG-prep scan which is a
preparation scan to decide an appropriate delay time for ECG
synchronization previous to an FBI scan for imaging, and
subsequently performs the FBI scan with the ECG delay time decided
by the ECG-prep scan. The ECG-prep scan obtains plural single shot
images at mutually different time phases by acquiring data at
gradually changed different delay times from an R wave of an ECG
signal. By selecting an image where a blood vessel is depicted
appropriately from among the plural images obtained from the
ECG-prep scan, an ECG delay time for the FBI scan can be
determined. This allows a high-velocity blood flow to be depicted
at a time phase corresponding to a lower flow velocity.
[0011] In the conventional Flow-Spoiled FBI method, an FASE (fast
advanced spin echo) sequence is used as an imaging sequence and a
gradient pulse is applied in an RO direction to suppress a
blood-flow signal from an artery systole. In a technology, called
Flow-Adjusted FBI, a gradient pulse is applied not only in an RO
direction but in a PE (phase encode) direction. A gradient pulse
application achieves good arteriovenous separation.
[0012] However, when a spoiler intensity of a gradient pulse is
increased in order to improve arteriovenous separation performance,
it is necessary to extend ETS (echo train spacing). As a result,
there are problems in that time resolution decreases with an
increase in ETS and arteriovenous separation of a high-velocity
blood vessel becomes difficult.
[0013] In the conventional Flow-dephasing method, since a dephasing
pulse is applied to a gradient magnetic field in an RO direction in
a scan under the FASE method, a depiction performance of blood
vessels depends on a blood vessel direction and a depiction
performance accordingly has a limitation.
BRIEF SUMMARY
[0014] The present exemplary embodiments have been made in light of
conventional situations, and it is an object of the present
exemplary embodiments to provide a magnetic resonance imaging
apparatus and a magnetic resonance imaging method which make it
possible to acquire a blood flow image in a blood vessel which is
an imaging target in a more appropriate condition.
[0015] The present exemplary embodiments provide a magnetic
resonance imaging apparatus comprising: an imaging condition
setting unit configured to set a sequence accompanying application
of a motion probing gradient pulse as an imaging condition; a scan
performing unit configured to perform an imaging scan according to
the sequence; and a blood flow image generating unit configured to
generate a blood flow image based on data acquired by the imaging
scan.
[0016] The present exemplary embodiments also provide a magnetic
resonance imaging apparatus comprising: an imaging condition
setting unit configured to set an imaging condition using a
sequence independent from a travel direction of a blood vessel to
be a target of a blood flow image; a scan performing unit
configured to perform an imaging scan according to the sequence;
and a blood flow image generating unit configured to generate a
blood flow image based on data acquired by the imaging scan.
[0017] The present exemplary embodiments also provide a magnetic
resonance imaging apparatus comprising: an imaging condition
setting unit configured to set a sequence as an imaging condition
for applying motion probing gradient pulses each having a mutually
different intensity to acquire imaging data with each intensity of
the motion probing gradient pulses; a preparation scan performing
unit configured to perform a preparation scan according to the
sequence; and a reference blood flow image generating unit
configured to generate blood flow images for a reference based on
data corresponding to each intensity of the motion probing gradient
pulses, the data being acquired by the preparation scan.
[0018] The present exemplary embodiments also provide a magnetic
resonance imaging apparatus comprising: an imaging condition
setting unit configured to set a data acquisition timing as an
imaging condition for acquiring data in a vicinity of a center of
k-space at systole and diastole in a heart rate of a heart; a scan
performing unit configured to perform an imaging scan according to
the imaging condition; and a blood flow image generating unit
configured to generate a blood flow image based on data, pieces of
the data being acquired at systole and diastole, respectively, by
the imaging scan.
[0019] The present exemplary embodiments also provide a magnetic
resonance imaging apparatus comprising: a scan performing unit
configured to perform an imaging scan according to a sequence
independent from a travel direction of a blood vessel to be a
target subsequently to applying a gradient magnetic field pulse for
a flow selection to serve one of a purpose of compensating a flow
and another purpose of facilitating flow void effect in a blood
vessel of an object; and a blood flow image generating unit
configured to generate a non-contrast-enhanced blood flow image of
the object based on data acquired by the imaging scan.
[0020] The present exemplary embodiments also provide a magnetic
resonance imaging apparatus comprising: an imaging condition
setting unit configured to set a sequence accompanying application
of a flow encode pulse as an imaging condition; a scan performing
unit configured to perform an imaging scan according to the
sequence; and a blood flow image generating unit configured to
generate a non-contrast-enhanced blood flow image based on data
acquired by the imaging scan.
[0021] The present exemplary embodiments also provide a magnetic
resonance imaging method comprising steps of: setting a sequence
accompanying application of a motion probing gradient pulse as an
imaging condition; performing an imaging scan according to the
sequence; and generating a blood flow image based on data acquired
by the imaging scan.
[0022] The present exemplary embodiments also provide a magnetic
resonance imaging method comprising steps of: setting an imaging
condition using a sequence independent from a travel direction of a
blood vessel to be a target of a blood flow image; performing an
imaging scan according to the sequence; and generating a blood flow
image based on data acquired by the imaging scan.
[0023] The present exemplary embodiments also provide a magnetic
resonance imaging method comprising steps of: setting a sequence as
an imaging condition for applying motion probing gradient pulses
each having a mutually different intensity to acquire imaging data
with each intensity of the motion probing gradient pulses;
performing a preparation scan according to the sequence; and
generating blood flow images for a reference based on data
corresponding to each intensity of the motion probing gradient
pulses, the data being acquired by the preparation scan.
[0024] The present exemplary embodiments also provide a magnetic
resonance imaging method comprising steps of: setting a data
acquisition timing as an imaging condition for acquiring data in a
vicinity of a center of k-space at systole and diastole in a heart
rate of a heart; performing an imaging scan according to the
imaging condition; and generating a blood flow image based on data,
pieces of the data being acquired at systole and diastole
respectively by the imaging scan.
[0025] The present exemplary embodiments also provide a magnetic
resonance imaging method comprising steps of: performing an imaging
scan according to a sequence independent from a travel direction of
a blood vessel to be a target subsequently to applying a gradient
magnetic field pulse for a flow selection to serve one of a purpose
of compensating a flow and another purpose of facilitating flow
void effect in a blood vessel of an object; and generating a
non-contrast-enhanced blood flow image of the object based on data
acquired by the imaging scan.
[0026] The present exemplary embodiments also provide a magnetic
resonance imaging method comprising steps of: setting a sequence
accompanying application of a flow encode pulse as an imaging
condition; performing an imaging scan according to the sequence;
and generating a non-contrast-enhanced blood flow image based on
data acquired by the imaging scan.
[0027] The magnetic resonance imaging apparatus and the magnetic
resonance imaging method as described above make it possible to
acquire a blood flow image in a blood vessel which is an imaging
target in a more appropriate condition.
BRIEF DESCRIPTION OF THE DRAWINGS
[0028] In the accompanying drawings:
[0029] FIG. 1 is a block diagram showing a magnetic resonance
imaging apparatus according to an embodiment of the present
invention;
[0030] FIG. 2 is a functional block diagram of the computer in the
magnetic resonance imaging apparatus shown in FIG. 1;
[0031] FIG. 3 is a diagram showing an example of a flow control
pre-pulse part set in the pulse sequence setting unit shown in FIG.
2;
[0032] FIG. 4 is a diagram showing another example of a flow
control pre-pulse part set in the pulse sequence setting unit shown
in FIG. 2;
[0033] FIG. 5 is a diagram showing a performing order of scans to
be purposes of pulses sequence set for acquiring a blood flow image
by the pulse sequence setting unit shown in FIG. 2;
[0034] FIG. 6 is a diagram showing an example of a DWI-Prep
sequence set in the pulse sequence setting unit shown in FIG.
2;
[0035] FIG. 7 is a diagram showing an example of a travel direction
of a blood vessel referred to by the pulse sequence setting unit
shown in FIG. 2 at setting an intensity of an MPG pulse;
[0036] FIG. 8 is a diagram indicating an order for arranging ECHO
data acquired by a scroll acquisition in k-space;
[0037] FIG. 9 is a diagram showing an example of a sequence for an
imaging scan set in the pulse sequence setting unit shown in FIG.
2;
[0038] FIG. 10 is a diagram showing an example of timings for
acquiring ECHO data set in the pulse sequence setting unit shown in
FIG. 2; and
[0039] FIG. 11 is a flowchart showing an example of flow for
acquiring a blood flow image with the magnetic resonance imaging
apparatus shown in FIG. 1.
DESCRIPTION OF PREFERRED EMBODIMENTS
[0040] A magnetic resonance imaging apparatus and a magnetic
resonance imaging method according to exemplary embodiments of the
present invention will be described with reference to the
accompanying drawings.
[0041] FIG. 1 is a block diagram showing a magnetic resonance
imaging apparatus according to an exemplary embodiment of the
present invention.
[0042] A magnetic resonance imaging apparatus 20 includes a static
field magnet 21 for generating a static magnetic field, a shim coil
22 arranged inside the static field magnet 21 which is
cylinder-shaped, a gradient coil unit 23 and an RF coil 24. The
static field magnet 21, the shim coil 22, the gradient coil unit 23
and the RF coil 24 are built in a gantry (not shown).
[0043] The magnetic resonance imaging apparatus 20 also includes a
control system 25. The control system 25 includes a static magnetic
field power supply 26, a gradient power supply 27, a shim coil
power supply 28, a transmitter 29, a receiver 30, a sequence
controller 31 and a computer 32. The gradient power supply 27 of
the control system 25 includes an X-axis gradient power supply 27x,
a Y-axis gradient power supply 27y and a Z-axis gradient power
supply 27z. The computer 32 includes an input device 33, a monitor
34, an operation unit 35 and a storage unit 36.
[0044] The static field magnet 21 communicates with the static
magnetic field power supply 26. The static magnetic field power
supply 26 supplies electric current to the static field magnet 21
to get the function to generate a static magnetic field in an
imaging region. The static field magnet 21 includes a
superconductivity coil in many cases. The static field magnet 21
gets current from the static magnetic field power supply 26 which
communicates with the static field magnet 21 at excitation.
However, once excitation has been made, the static field magnet 21
is usually isolated from the static magnetic field power supply 26.
The static field magnet 21 may include a permanent magnet which
makes the static magnetic field power supply 26 unnecessary.
[0045] The static field magnet 21 has the cylinder-shaped shim coil
22 coaxially inside itself. The shim coil 22 communicates with the
shim coil power supply 28. The shim coil power supply 28 supplies
current to the shim coil 22 so that the static magnetic field
becomes uniform.
[0046] The gradient coil unit 23 includes an X-axis gradient coil
unit 23x, a Y-axis gradient coil unit 23y and a Z-axis gradient
coil unit 23z. Each of the X-axis gradient coil unit 23x, the
Y-axis gradient coil unit 23y and the Z-axis gradient coil unit 23z
which is cylinder-shaped is arranged inside the static field magnet
21. The gradient coil unit 23 has also a bed 37 in the area formed
inside it which is an imaging area. The bed 37 supports an object
P. Around the bed 37 or the object P, the RF coil 24 may be
arranged instead of being built in the gantry.
[0047] The gradient coil unit 23 communicates with the gradient
power supply 27. The X-axis gradient coil unit 23x, the Y-axis
gradient coil unit 23y and the Z-axis gradient coil unit 23z of the
gradient coil unit 23 communicate with the X-axis gradient power
supply 27x, the Y-axis gradient power supply 27y and the Z-axis
gradient power supply 27z of the gradient power supply 27
respectively.
[0048] The X-axis gradient power supply 27x, the Y-axis gradient
power supply 27y and the Z-axis gradient power supply 27z supply
currents to the X-axis gradient coil unit 23x, the Y-axis gradient
coil unit 23y and the Z-axis gradient coil unit 23z respectively so
as to generate gradient magnetic fields Gx, Gy and Gz in the X, Y
and Z directions in the imaging area.
[0049] The RF coil 24 communicates with the transmitter 29 and the
receiver 30. The RF coil 24 has a function to transmit a RF signal
given from the transmitter 29 to the object P and receive a MR
signal generated due to an nuclear spin inside the object P which
is excited by the RF signal to give to the receiver 30.
[0050] The sequence controller 31 of the control system 25
communicates with the gradient power supply 27, the transmitter 29
and the receiver 30. The sequence controller 31 has a function to
storage a pulse sequence describing control information needed in
order to make the gradient power supply 27, the transmitter 29 and
the receiver 30 drive and generate gradient magnetic fields Gx, Gy
and Gz in the X, Y and Z directions and a RF signal by driving the
gradient power supply 27, the transmitter 29 and the receiver 30
according to imaging conditions defined by a predetermined pulse
sequence stored. The control information above-described includes
motion control information, such as intensity, impression period
and impression timing of the pulse electric current which should be
impressed to the gradient power supply 27. The control information
supplied from the sequence controller 31 to the transmitter 29
includes a phase for a transmission and a current intensity of an
RF pulse which corresponds to a flip angle for transmission.
[0051] The sequence controller 31 is also configured to give raw
data to the computer 32. The raw data is complex number data
obtained through the detection of a MR signal and A/D conversion to
the MR signal detected in the receiver 30.
[0052] The transmitter 29 has a function to give a RF signal to the
RF coil 24 in accordance with control information provided from the
sequence controller 31. The receiver 30 has a function to generate
raw data which is digitized complex number data by detecting a MR
signal given from the RF coil 24 and performing predetermined
signal processing and A/D converting to the MR signal detected. The
receiver 30 also has a function to give the generated raw data to
the sequence controller 31.
[0053] In addition, an ECG unit 38 for acquiring an ECG signal of
the object P is provided with the magnetic resonance imaging
apparatus 20. The ECG signal detected by the ECG unit 38 is
outputted to the computer 32 through the sequence controller
31.
[0054] Note that, a PPG (peripheral pulse gating) signal may be
acquired instead of an ECG signal. A PPG signal is acquired by
detecting a pulse wave of e.g., tip of a finger as an optical
signal. When a PPG signal is acquired, a PPG signal detection unit
is provided with the magnetic resonance imaging apparatus 20.
[0055] The computer 32 gets various functions by the operation unit
35 executing some programs stored in the storage unit 36 of the
computer 32. The computer 32 may include some specific circuits
instead of using some of the programs.
[0056] FIG. 2 is a functional block diagram of the computer 32 in
the magnetic resonance imaging apparatus 20 shown in FIG. 1.
[0057] The computer 32 functions as a sequence controller control
unit 40, a k-space database 41, an image reconstruction unit 42, an
image database, a blood flow image generating unit 44 and a pulse
sequence setting unit 45 by program.
[0058] The sequence controller control unit 40 has a function for
controlling the driving of the sequence controller 31 by giving a
predetermined pulse sequence acquired from the pulse sequence
setting unit 45 to the sequence controller 31 based on information
from the input device 33 or another element. Further, the sequence
controller control unit 40 has a function for receiving raw data
which is k-space data from the sequence controller 31 and arranging
the raw data to k-space (Fourier space) formed in the k-space
database 41. In addition, the sequence controller control unit 40
is configured to obtain parameters necessary for performing a pulse
sequence from the input device 33 or other elements and give them
to the sequence controller 31. The sequence controller control unit
40 is also configured to control the sequence controller 31 so that
a scan is performed with an ECG synchronous based on an ECG signal
obtained by the ECG unit 38 as needed.
[0059] Therefore, the k-space database 41 stores each pieces of raw
data generated by the receiver 30 as k-space data, and the k-space
data is arranged to the k-space formed in the k-space database
41.
[0060] The image reconstruction unit 42 has a function for
capturing the k-space data from the k-space database 41, performing
predetermined image reconstruction processing, such as three
dimensional (3D) Fourier transform processing, to the k-space data,
reconstructing three dimensional image data of the object P, and
writing the image data to the image database 43. Incidentally,
intermediate data, such as two dimensional (2D) image data, may be
temporarily generated by processing, such as two-dimensional
Fourier transform processing, and thereafter the three-dimensional
image data may be reconstructed.
[0061] Therefore, the image database 43 stores the
three-dimensional image data of the object P.
[0062] The blood flow image generating unit 44 has a function to
read image data from the image database 43 and generate a blood
flow image. In case of imaging under the FBI method, an
arteriovenous-separated blood flow image can be generated by
subtraction processing between arteries-enhanced image data and
arteries-suppressed image data acquired in a diastole and a systole
of a myocardium respectively in synchronization with ECG based on
an ECG signal. Therefore, the blood flow image generating unit 44
has a function to read 3D image data in a diastole and a systole of
a myocardium from the image database 43 and cancel vein data by
subtraction processing to the read 3D image data to extract artery
data as a blood flow image. However, generating a blood flow image
without subtraction processing is also possible. In this case,
acquiring image data in a systole of a myocardium makes
arteriovenous separation easier. Hereinafter, generating a blood
flow image with subtraction processing will be described.
[0063] In addition, the blood flow image generating unit 44 has a
function to perform various processing such as MIP processing for a
blood flow image as needed. Further, the blood flow image
generating unit 44 has a function to provide a blood flow image
generated finally to the display unit 34 to be displayed on it.
[0064] Alternatively, the blood flow image generating unit 44 may
be configured to generate a blood flow image from raw data read
from the k-space database 41 without the image reconstruction unit
42. Further, an MIP image, an SVR (shaded volume rendering) image
or another three-dimensional image may be generated as a blood flow
image.
[0065] That is, the magnetic resonance imaging device 20 has a
function to generate a blood flow image from raw data by the image
reconstruction unit 42 and the blood flow image generating unit
44.
[0066] The pulse sequence setting unit 45 has a function to set a
pulse sequence to acquire a non-contrast-enhanced blood flow image
as an imaging condition and provide the set pulse sequence to the
sequence controller control unit 40 so that a scan can be performed
according to a desired imaging condition.
[0067] An arbitrary sequence for a radial scan, a line scan or a
spiral scan can be used for an imaging sequence for acquiring a
blood flow image. More specifically, an artery and a venation can
be represented by using a desired sequence suitable for acquiring a
blood flow image, such as a balanced SSFP (steady state free
precession) sequence, an FSE (fast spin echo) sequence, an EPI
(echo planar imaging) sequence, an FASE sequence, a half-Fourier
FSE sequence, as an imaging sequence.
[0068] When imaging is performed by using a balanced SSFP sequence
or under PROPELLER (Periodically Rotated Overlapping ParallEL Lines
with Enhanced Reconstruction) method using an FSE sequence, data
can be acquired without depending to directionality of a blood flow
to be a target. Therefore, by using a balanced SSFP sequence and an
FSE sequence as an imaging sequence, signals from blood vessels
traveling in arbitrary directions can be acquired. The balanced
SSFP sequence is a sequence for aligning a phase of a transverse
magnetization in every repeated excitation or acquiring signals in
an SSFP state. The PROPELLER method is a method for radially
acquiring data passing the origin in k-space with changing a
gradient magnetic field by an FSE sequence. Specifically, in the
PROPELLER method, mutually parallel data groups forming a blade are
acquired in 1 TR (repetition time) and the k-space is filled with
data by rotating the blade every TR.
[0069] Note that, a sequence similar to the SSFP sequence may be
used for an imaging sequence. An SSFP sequence is a sequence for
imaging using a spin echo and a stimulated echo. For example, a
sequence for imaging by combining an FID (free induction decay)
signal with a spin echo and a stimulated echo may be used as an
imaging sequence.
[0070] An imaging scan under an imaging sequence can be performed
in synchronization with an ECG by using an ECG signal as needed as
mentioned above. Performing an imaging scan in synchronization with
an ECG makes it possible to acquire image data at a desired cardiac
time phase such as a diastole and a systole of a myocardium.
Especially in case of imaging under the FBI method, a blood flow
image can be obtained by acquiring an echo signal set consisting of
plural echo signals in mutually different cardiac time phases such
as a diastole and a systole respectively and by subtraction
processing to pieces of image data each generated based on the
corresponding echo signal set.
[0071] In addition, a flow control pre-pulse part can be added to
previously to an imaging sequence. The flow control pre-pulse part
can change correspondence between a flow velocity of a blood of an
object and an image value (a pixel value). In the flow control
pre-pulse part, a flow selective gradient magnetic field pulse
having a function as a flow control pulse can be applied.
[0072] Note that, and another pulse such as a fat saturation pulse
may be applied between the flow control pre-pulse part for applying
a flow selective gradient magnetic field pulse and an imaging
sequence such as an SSFP sequence.
[0073] The flow selective gradient magnetic field pulse is
categorized into a flow encode pulse for compensating an
intravascular blood flow and a flow spoiler pulse facilitating flow
void effect.
[0074] The flow encode pulse changes a phase of spins (a transverse
magnetization) in proportion to a flow velocity of a fluid like a
blood. An application of this pulse produces a phase distribution
in a transverse magnetization according to a flow velocity. When a
longitudinal magnetization recovery pulse is applied subsequently,
a distribution of a longitudinal magnetization (a spatial
distribution) according to the flow velocity appears. Consequently,
background part of a blood flow image is suppressed and blood
vessels are enhanced. A flow encode pulse is applied largely in a
direction of a blood-flow velocity such as a body axis
direction.
[0075] A flow spoiler pulse changes a phase of spins (a transverse
magnetization) in proportion to a flow velocity of a fluid like a
blood as with a flow encode pulse. Specifically, the flow spoiler
pulse produces a large phase difference from a slight flow velocity
difference in a voxel by producing a phase shift with highly
sensitivity to a variation of a flow velocity, and shows an effect
to spoil signals from a part where a fluid like a blood has a high
flow velocity due to interference effect between spins. It is
general for the flow spoiler pulse to use a waveform of a gradient
magnetic field pulse by which a phase is shifted to an extent great
larger than that by a normal flow encode pulse per unit flow
velocity, i.e. a flow encoding amount is large.
[0076] When a flow spoiler pulse is used for a flow control
pre-pulse part, an application of a longitudinal magnetization
recovery pulse subsequently to a pulse application brings a
distribution of a longitudinal magnetization (a spatial
distribution) according to a flow velocity as in the case of using
a flow encode pulse. Accordingly, a scan by an imaging sequence
part is performed with a slow recovery of only a longitudinal
magnetization in a high-velocity blood flow so that signals from
blood vessels are suppressed.
[0077] A flow spoiler pulse is applied to suppress signals from a
single or plural blood flows which flow in a certain direction or
unspecified directions. Therefore, a flow spoiler pulse is often
applied in three directions of a slice selection direction (also
referred to a slice encode direction), a phase encode direction and
a readout direction. An MPG (motion probing gradient) pulse for DWI
(diffusion weighted imaging) is an example of flow spoiler
pulse.
[0078] A type of flow selective gradient magnetic field pulse is
determined depending on a purpose of imaging and a method for
imaging. An example of practical use is a case where a flow
selective gradient magnetic field pulse is applied in an FBI. An
FBI is carried out in synchronization with ECG by using an ECG
signal and image data is generated from data acquired in a diastole
and a systole respectively. A non-contrast-enhanced blood flow
image is generated by subtraction processing between pieces of
image data corresponding to the diastole and the systole
respectively. If a flow encode pulse is applied to arteries to
enhance signals from the arteries prior to data acquisition in a
diastole while a flow spoiler pulse is applied to arteries to
suppress signals from the arteries prior to data acquisition in a
systole, subtraction processing can achieve a satisfactory
arteriovenous separation to depict the arteries since a difference
of intensities of the signals acquired from the arteries in the
diastole and the systole increases. In addition, using an SSFP
sequence as an imaging sequence for FBI makes it possible to
acquire data independent from travel directions of blood
vessels.
[0079] Another example of practical use, for a purpose of obtaining
a non-contrast-enhanced MRA image at a time phase at which a flow
velocity is high like as a systole, is a case where a flow encode
pulse is applied prior to data acquisition without applying a flow
spoiler pulse at another time phase.
[0080] In this type of flow control pre-pulse part where a flow
selective gradient magnetic field pulse is applied, an excitation
pulse, a refocus pulse and a longitudinal magnetization recovery
pulse are applied as RF pulses.
[0081] FIG. 3 is a diagram showing an example of a flow control
pre-pulse part set in the pulse sequence setting unit 45 shown in
FIG. 2.
[0082] In FIG. 3, the abscissa denotes time, RF denotes RF pulses
and Gf denotes flow selective gradient magnetic field pulses
respectively. As shown in FIG. 3, an excitation pulse, a refocus
pulse and a longitudinal magnetization recovery pulse are applied
as RF pulses. The longitudinal magnetization recovery pulse is an
RF pulse to transform forcibly a transverse magnetization of spins
into a longitudinal magnetization. A flip angle of the excitation
pulse is set to a desired angle such as 90 degrees or 45 degrees. A
flip angle of the longitudinal magnetization recovery pulse is
often set to the same angle as that of the excitation pulse. A flip
angle of the refocus pulse is set to 180 degrees, for example.
Then, two flow selective gradient magnetic field pulses are set to
be applied twice before and after the refocus pulse respectively
subsequently to an application of the excitation pulse and
previously to an application of the longitudinal magnetization
recovery pulse.
[0083] An imaging sequence such as an SSFP sequence is set to be
performed subsequently to the flow control pre-pulse part described
above.
[0084] FIG. 4 is a diagram showing another example of a flow
control pre-pulse part set in the pulse sequence setting unit 45
shown in FIG. 2.
[0085] In FIG. 4, the abscissa denotes time, RF denotes RF pulses
and Gf denotes flow selective gradient magnetic field pulses
respectively. As shown in FIG. 4, an excitation pulse, two refocus
pulses and a longitudinal magnetization recovery pulse are applied
as RF pulses. Then, a flow selective gradient magnetic field pulse
is applied between the two refocus pulses. As the flow selective
gradient magnetic field pulse, a bipolar pulse of which the area of
positive pole side is the same as that of the negative pole side is
used.
[0086] Whether a flow selective gradient magnetic field pulse shown
in FIG. 3 is set or that shown in FIG. 4 is set, similar control
effect can be obtained. An intensity and a direction for
application of a flow selective gradient magnetic field pulse are
set to an appropriate value and direction as imaging conditions
respectively. For example, an intensity and a direction for
application of a flow selective gradient magnetic field pulse can
be determined depending on the travel direction and/or a flow
velocity of a target blood flow. Then, a flow selective gradient
magnetic field pulse is applied to target vessels carrying blood
flows such as blood flows of arteries and blood flows having high
flow velocities in an object.
[0087] Note that, when an intensity and/or a direction for
application necessary to set a flow selective gradient magnetic
field pulse are unknown at setting for an imaging sequence, a
preparation scan can be performed to determine them as needed. The
preparation scan acquires pieces of echo data according to
intensities and/or directions for application of plural types of
flow selective gradient magnetic field pulses. The preparation scan
is preferably set to be a two-dimensional scan for reduction of an
imaging period. Based on data, acquired by the preparation scan,
corresponding to each intensity and/or application direction of
flow selective gradient magnetic field pulses, plural blood flow
images for reference are generated respectively and a reference
image depicting a blood flow satisfactorily can be selected from
the generated plural blood flow images for reference automatically
or manually with visual observation. Then, appropriate intensity
and/or application direction of a flow selective gradient magnetic
field pulse can be determined by selecting a reference image.
[0088] Signal values of blood flow data corresponding to respective
intensities of flow selective gradient magnetic field pulses can be
obtained by performing the preparation scan described above.
Therefore, it is also possible to display a graph showing
relationship between the intensities of flow selective gradient
magnetic field pulses and signal values of data and to determine
the intensity of the flow selective gradient magnetic field pulse
with referring to the graph. The graph showing the relationship
between the intensities of flow selective gradient magnetic field
pulses and signal values of data can be created according to the
following procedure (algorithm).
[0089] First, plural blood flow images for reference corresponding
to mutually different intensities of flow selective gradient
magnetic field pulses respectively are generated by a preparation
scan. In case of generating a subtraction image by imaging, one of
the plural blood flow images for reference is set as a standard
image and the difference between each blood flow image for
reference and the standard image is calculated. Or differences
between all two which can be combined of the plural blood flow
images for reference are calculated. Consequently, plural
subtraction images are generated.
[0090] Next, an MIP image is generated by MIP processing in time
axis direction to the plural blood flow images for reference or the
plural subtraction images in case of performing subtraction
processing. Then, a mask image is created by binarizing the MIP
image. The created mask image is multiplied by each of the plural
blood flow images for reference. Consequently, characteristic
amounts corresponding to the respective intensities of the flow
selective gradient magnetic field pulses are calculated. Thus, the
graph showing the relationship between the respective intensities
and the corresponding characteristic amounts, each calculated as
described above, of the flow selective gradient magnetic field
pulses is created.
[0091] For displaying the graph, the pulse sequence setting unit 45
is configured to obtain necessary data from other elements and
generate graph information representing the graph to be displayed
on the display unit 34.
[0092] Without or with displaying the graph, an appropriate
intensity of a flow selective gradient magnetic field pulse can be
determined by automatically or manually selecting an image with a
large amount of flow encode under MIP processing to the reference
images in the time axis direction, i.e., an image showing many
white parts depicted as blood vessels.
[0093] The pulse sequence setting unit 45 has a function to set a
sequence for performing a preparation scan as described above.
Hereinafter, concrete examples of applying an MPG pulse for DWI as
a flow selective gradient magnetic field pulse will be
described.
[0094] Specifically, the pulse sequence setting unit 45 is
configured to set a DWI-Prep sequence for performing a DWI-Prep
scan as a preparation scan prior to a sequence for an imaging scan
to image a blood vessel. A DWI generates an image with using
velocities and directions of diffusion, each serving as a
parameter, of water molecules in a tissue by applying an MPG pulse
as a pre-pulse.
[0095] FIG. 5 is a diagram showing a performing order of scans to
be purposes of pulses sequence set for acquiring a blood flow image
by the pulse sequence setting unit 45 shown in FIG. 2.
[0096] As shown in FIG. 5, a blood flow image can be acquired by
performing an imaging scan subsequently to performing a DWI-Prep
scan which is a preparation scan. In the imaging scan, a DWI pulse
is applied as a pre-pulse. The DWI-Prep scan is performed to
determine a DWI intensity necessary for performing the imaging
scan. Then, the imaging scan is performed with the DWI intensity
determined by performing the DWI-Prep scan and the blood flow image
is acquired by performing the imaging scan.
[0097] The DWI-Prep sequence to perform the DWI-Prep scan is a
sequence by which the DWI sequence and the imaging sequence are
repeated plural times. The DWI sequence is a sequence for applying
an MPG pulse to determine a DWI intensity. An intensity of an MPG
pulse is changed per TR.
[0098] It is preferable that the imaging sequence for the DWI-Prep
sequence uses a sequence equivalent to the imaging sequence used
for the imaging scan as possible.
[0099] When the imaging sequence of the DWI-Prep sequence is set to
acquire two-dimensional data, it is possible to reduce an image
processing throughput and an imaging period in the DWI-Prep scan.
However, a three-dimensional image may be acquired under the
DWI-Prep scan by setting a three-dimensional sequence for the
imaging sequence of the DWI-Prep sequence.
[0100] FIG. 6 is a diagram showing an example of a DWI-Prep
sequence set in the pulse sequence setting unit 45 shown in FIG.
2.
[0101] In FIG. 6, ECG denotes an ECG signal, RF/ECHO denotes RF
signals and ECHO data, Gse denotes a gradient magnetic field for
slice encoding, Gro denotes a gradient magnetic field for readout
and Gpe denotes a gradient magnetic field for phase encoding
respectively. The pulse sequence setting unit 45 sets a DWI-Prep
sequence shown in FIG. 6, for example. FIG. 6 shows an example of
setting a balanced SSFP sequence for an imaging sequence of the
DWI-Prep sequence. Therefore, subsequently to a DWI sequence, the
balanced SSFP sequence is set. In addition, subsequently to the
balanced SSFP sequence, the next DWI sequence having a changed MPG
pulse intensity is set.
[0102] The DWI-Prep sequence consisting of the DWI sequence and the
balanced SSFP sequence is performed in synchronization with an ECG
signal by using an R wave of the ECG signal as a trigger, for
example. The balanced SSFP sequence is preferably set to a single
shot sequence suitable for acquiring a blood flow image and an
.alpha..degree. pulse and a -.alpha..degree. pulse are applied
repeatedly according to the number of pieces of echo data to be
acquired. Further, a pulse for various purposes (not shown) such as
a fat saturation pulse is applied prior to the first
.alpha..degree. pulse as needed.
[0103] Then, a DWI sequence is set prior to the balanced SSFP
sequence for echo data acquisition. In the DWI sequence, a
90-degree excitation pulse, a subsequent 180-degree refocus pulse
and a subsequent 90-degree longitudinal magnetization recovery
pulse are applied as RF signals. Each flip angle and flop angle of
an excitation pulse, a refocus pulse and a longitudinal
magnetization recovery pulse may be set to other angles
respectively. Further, MPG pulses are applied before and after the
180-degree refocus pulse as gradient magnetic field pulses. The MPG
pulses are applied in necessary directions of a slice encode
direction, a readout direction and a phase encode direction. The
DWI sequence in FIG. 6 shows an example that a readout direction
MPG pulse (MPGro1) and a phase encode direction MPG pulse (MPGpe1)
are applied while a slice encode direction MPG pulse (MPGse1) is
not applied. Then, echo data is acquired by applying the
.alpha..degree. and -.alpha..degree. pulses and the gradient
magnetic field pulse of the balanced SSFP sequence with spins
dispersed (spoiled) due to diffusion of water molecules in tissues
by applying the MPG pulses.
[0104] Further, when necessary echo data is acquired after applying
the MPG pulse, a 90-degree excitation pulse and a subsequently
180-degree refocus pulse are applied again as RF signals. Then, MPG
pulses MPGro2, MPGpe2 with changing intensities are applied before
and after the 180-degree refocus pulse again. Thus, similarly, echo
data is acquired by applying the .alpha..degree. and
-.alpha..degree. pulses and the gradient magnetic field pulse of
the balanced SSFP sequence again with spins dispersed (spoiled) due
to diffusion of water molecules in tissues by applying the MPG
pulses each having a different intensity. This application of the
MPG pulses and echo data acquisition are repeatedly performed by
the number of intensities of the MPG pulses.
[0105] That is to say, the DWI-Prep sequence is a sequence for
single shot multi-DWI imaging which performs imaging by a single
nuclear magnetic excitation and applies an MPG pulse plural times
with changing a DWI intensity, i.e., an intensity of the MPG
pulse.
[0106] The intensities of an MPG pulse can be changed arbitrarily
in three axis directions of a slice direction, a readout direction
and a phase encode direction depending on travel directions of
blood vessels to be depicted. Therefore, MPG pulses can be applied
in one axis direction or two axis directions, as well as the
example in FIG. 6. For example, when travel directions of blood
vessels are three axis directions, the intensities of the MPG
pulses can be changed to be equivalent to each other in the three
axis directions. When a travel direction of blood vessels is known
and particular, the intensities of the MPG pulses can be changed to
be different from each other in three axis directions depending on
the travel direction of the blood vessels so as to achieve a
satisfactory arteriovenous separation in the travel direction of
the blood vessels.
[0107] By changing the intensities of the MPG pulses arbitrarily in
three axis directions depending on the travel direction of the
blood vessels in the DWI-Prep sequence as described above, setting
intensities of an MPG pulse for an imaging sequence can be variable
in three axis directions depending on the travel direction of the
blood vessels.
[0108] The intensities of the MPG pulse in a phase encode direction
and a read out direction are changed in the example shown in FIG.
6. Note that, the intensity of the MPG pulse in the phase encode
direction is set to be larger than that in the read out direction.
The intensity of the MPG pulse in a slice direction is set to zero.
If the intensities of the MPG pulse are set as described above,
appropriate intensities of the MPG pulse can be determined to
differentiate signals in blood vessels traveling in the phase
encode direction and the read out direction satisfactorily.
[0109] FIG. 7 is a diagram showing an example of a travel direction
of a blood vessel referred to by the pulse sequence setting unit 45
shown in FIG. 2 at setting an intensity of an MPG pulse.
[0110] For example, as shown in FIG. 7, a blood is assumed to flow
in a body-axis (HF: head feet) direction when a coronal section is
imaged. In this case, if the DWI-Prep sequence is set so that the
intensity of the MPG pulse in the HF direction which is a blood
flow direction, i.e., an RO direction, is set to be larger than
that in a PE direction which is an RL (right left) direction
perpendicular to the HF direction while an MPG pulse having a
slight intensity is applied in an SL (slice) direction, appropriate
intensities of the MPG pulse can be determined to differentiate
signals in blood vessels traveling in the HF direction
satisfactorily.
[0111] An intensity and a variation width and variation range of an
intensity of an MPG pulse can be set arbitrarily by providing
instruction information to the pulse sequence setting unit 45
through operation of the input device 33.
[0112] According to the DWI-Prep sequence like this, the DWI-Prep
scan is performed and artery data are depicted as a blood flow
image with arteriovenous separation by the image reconstruction
unit 42 and the blood flow image generating unit 44, pieces of
image data of arteries corresponding to mutually different
intensities of DWI can be obtained. The intensity of artery signals
acquired with a high DWI intensity becomes high; on the contrary,
the intensity of artery signals acquired with a low DWI intensity
becomes low. For this reason, artery data with arteriovenous
separation depend on a DWI intensity.
[0113] Therefore, by automatic image processing, such as threshold
processing, to artery data through arteriovenous separation with
each intensity of DWI or user's selection of artery data with
visual observation, image data with satisfactorily arteriovenous
separation can be selected. Consequently, an appropriate intensity
of an MPG pulse can be determined to obtain image data with
satisfactorily arteriovenous separation.
[0114] An intensity of an MPG pulse can be determined, for example,
by selecting a blood flow image where target vessels are depicted
appropriately from plural blood flow images, acquired with mutually
different intensities of DWI, displayed on the display unit 34
through operation of the input device 33. Therefore, the pulse
sequence setting unit 45 is configured to obtain a DWI intensity
(an intensity of an MPG pulse) used for imaging a selected blood
flow image in response to selection information of a blood flow
image from the input device 33. Alternatively, an intensity of an
MPG pulse may be inputted as a numeric value into the pulse
sequence setting unit 45 through operation of the input device
33.
[0115] By the way, scroll acquisition of data by an imaging scan is
known to be able to improve effect of an MPG pulse. Therefore, it
is preferable to perform scroll acquisition of data in an imaging
scan. In addition, it is preferable to match conditions of an
imaging sequence for a DWI-Prep scan to that used for an imaging
scan as possible. For this purpose, the pulse sequence setting unit
45 is configured to generate a two-dimensional imaging sequence for
scroll acquisition of data under a DWI-Prep scan when the pulse
sequence setting unit 45 receives instruction for scroll
acquisition from the input device 33.
[0116] FIG. 8 is a diagram indicating an order for arranging ECHO
data acquired by a scroll acquisition in k-space.
[0117] FIG. 8 represents k-space. That is, in FIG. 8, the ordinate
denotes a phase encode direction (Kpe) and the abscissa denotes a
readout direction (Kro). As shown in FIG. 8, data are acquired
towards the arrow 1 and the arrow 2 under the scroll acquisition.
When 128 pieces of data are to be acquired in a PE direction for
example, pieces of data are acquired in order of the number
described inside of the arrow 1 and the arrow 2 under the scroll
acquisition. More specifically, the pieces of data are acquired
outward from the vicinity of the center in k-space along the arrow
1. Then, the pieces of data are acquired from a position away from
the center of k-space toward the center of k-space along the arrow
2.
[0118] By acquiring data of the center of k-space following to
application of an MPG pulse in this way, effect of the MPG pulse
can be improved. The modification in effect of an MPG pulse based
on an order of data acquisition can be obtained not only in imaging
by a balanced SSFP sequence but also in imaging under a PROPELLER
method. In case of using a sequence such as an FSE sequence, an
FASE sequence or an EPI sequence, it is suitable to set the time
between application timing of an MPG pulse and acquisition timing
for data of the center of k-space to the optimum TE (echo time) by
which effect of an MPG pulse is improved.
[0119] Note that, as well as the scroll acquisition mentioned
above, data can be acquired by sequential acquisition for acquiring
the data in one direction in k-space as shown by the arrow 3 in
FIG. 8 or by centric acquisition for acquiring data in a positive
and negative area alternately from the vicinity of the center of
k-space toward a side away from the center of k-space as shown by
the arrows 4 and 5. Numbers described inside the arrows 3, 4 and 5
show an acquisition order of 128 pieces of data, respectively.
[0120] A sequence for an imaging scan is also set in the pulse
sequence setting unit 45. The sequence for the imaging scan also
consists of a DWI sequence and an imaging sequence.
[0121] FIG. 9 is a diagram showing an example of a sequence for an
imaging scan set in the pulse sequence setting unit 45 shown in
FIG. 2.
[0122] In FIG. 9, ECG denotes an ECG signal, RF/ECHO denotes RF
signals and ECHO data, Gse denotes a gradient magnetic field for
slice encoding, Gro denotes a gradient magnetic field for readout
and Gpe denotes a gradient magnetic field for phase encoding
respectively. The pulse sequence setting unit 45 sets a sequence
for an imaging scan as shown in FIG. 9, for example. The sequence
for the imaging scan has a DWI sequence and an imaging sequence
following the DWI sequence.
[0123] The DWI sequence for the imaging scan is set so that an MPG
pulse having intensities determined in three axis directions by the
DWI-Prep scan is applied as gradient magnetic field pulses. The
imaging sequence for the imaging scan can use an arbitrary sequence
for acquiring three-dimensional data. Note that, as described
above, if an FSE sequence to perform a balanced SSFP sequence or a
PROPELLER method is used as the imaging sequence, a blood flow
image can be obtained without depending on travel directions of
blood vessels.
[0124] Further, from the perspective of setting an appropriate DWI
intensity, it is preferable that a sequence as equivalent to the
imaging sequence for the DWI-Prep scan as possible is used as the
imaging sequence for imaging scan. It is preferable to use a
sequence for two-dimensional data acquisition in the DWI-prep scan,
and to use a sequence for three-dimensional data acquisition of
which the other imaging conditions are same as those of the imaging
sequence for the DWI-prep scan in the imaging scan.
[0125] FIG. 9 shows an example of setting a balanced SSFP sequence
as the imaging sequence for the imaging scan. Therefore, the
balanced SSFP sequence is set following to a DWI sequence.
[0126] The sequence for the imaging scan consisting of the DWI
sequence and the balanced SSFP sequence is performed in
synchronization with an ECG signal by using an R wave of the ECG
signal as a trigger for example. The Balanced SSFP sequence is
preferably set to a single shot sequence suitable for acquiring a
blood flow image and an .alpha..degree. pulse and a
-.alpha..degree. pulse are applied repeatedly according to the
number of pieces of echo data to be acquired. In addition, A
pre-pulse (not shown) for various purposes such as a fat saturation
pulse is applied subsequently to the first .alpha..degree. pulse as
needed.
[0127] Then, the DWI sequence is set prior to echo data acquisition
under the balanced SSFP sequence. In the DWI sequence, a 90-degree
excitation pulse, a subsequent 180-degree refocus pulse and a
90-degree longitudinal magnetization recovery pulse are applied. In
addition, MPG pulses are applied before and after the 180-degree
refocus pulse. The MPG pulses are applied with intensities
determined by the DWI-Prep scan in desired directions of a slice
encode direction, a readout direction and a phase encode direction.
FIG. 9 shows an example that a readout direction MPG pulse (MPGro0)
and a phase encode direction MPG pulse (MPGpe0) are applied while a
slice encode direction MPG pulse (MPGse0) is not applied.
[0128] Then, with spins dispersed (spoiled) due to diffusion of
water molecules in tissues by application of the MPG pulses, echo
data is acquired by application of the .alpha..degree. and
-.alpha..degree. pulses and the gradient magnetic field pulse of
the balanced SSFP sequence.
[0129] Further, by quickening and delaying acquisition timings of
the echo data according to an ECG waveform, a blood flow image with
arteriovenous separation can be generated from echo data acquired
in a single heart rate. For the purpose, the pulse sequence setting
unit 45 is configured to set an imaging condition in which
acquisition timings of echo data are scrolled to timings suitable
for generating a blood flow image with arteriovenous separation in
response to an instruction to scroll an acquisition timing of echo
data from the input device 33.
[0130] FIG. 10 is a diagram showing an example of timings for
acquiring ECHO data set in the pulse sequence setting unit 45 shown
in FIG. 2.
[0131] In FIG. 10, each abscissa denotes time, ECG denotes an ECG
signal and ECHO denotes timings for acquiring ECHO data
respectively. In the balanced SSFP sequence, approximately 128
pieces of data are acquired between adjacent R waves of an ECG
signal (around 1000 ms). When data acquisition timings (cardiac
time phase) are scrolled so that data near the center of k-space is
acquired in each section of a systole and a diastole between
adjacent R waves of an ECG signal, data are acquired with blood
flow signals from arteries suppressed in the systole while data are
acquired with blood flow signals from arteries unsuppressed in the
diastole. Therefore, by calculating a difference between pieces of
data acquired in the systole and the diastole respectively, a blood
flow image of arteries with arteriovenous separation can be
obtained from data acquired in a single heart rate.
[0132] According to an example shown in FIG. 10, acquisition
timings of pieces of data acquired from the first are set in a
systole while those acquired from I-th are set in a diastole. Both
of the first acquired data and the I-th acquired data are set to
pieces of data of the center of k-space.
[0133] Next, the operation and action of a magnetic resonance
imaging apparatus 20 will be described.
[0134] FIG. 11 is a flowchart showing an example of flow for
acquiring a blood flow image with the magnetic resonance imaging
apparatus 20 shown in FIG. 1. The symbols including S with a number
in FIG. 3 indicate each step of the flowchart. Here, a case of
generating a blood flow image through subtraction processing by DWI
with application of an MPG pulse will be described.
[0135] First in step S1, a DWI-Prep sequence is set by the pulse
sequence setting unit 45. Specifically, intensities, respective
variation widths of the intensities, respective variation ranges of
the intensities (or respective numbers of times of changes of the
intensities) of an MPG pulse in three axis directions and a type of
imaging sequence are inputted into the pulse sequence setting unit
45 from the input device 33. The intensities, the respective
variation widths of the intensities, the respective variation
ranges of the intensities (or the respective numbers of times of
changes of the intensities) of the MPG pulse in the three axis
directions are determined depending on travel directions of blood
vessels respectively so that the blood vessels can be imaged more
satisfactorily. When the imaging sequence is a balanced SSFP
sequence or a sequence under a PROPELLER method, information
instructing which of a scroll acquisition, a sequential acquisition
or a centric acquisition should be chosen as a data acquisition
method is inputted into the pulse sequence setting unit 45 from the
input device 33. Alternatively, when the imaging sequence is
another sequence, values including a TE value are inputted into the
pulse sequence setting unit 45 from the input device 33.
[0136] In case of generating a blood flow image from data in a
single heart rate with scrolling data acquisition timings in the
imaging scan, instructions from the input device 33 are provided to
the pulse sequence setting unit 45 so that data acquisition timings
in the imaging sequence of the DWI-Prep sequence are set to those
for the imaging scan.
[0137] Then, the pulse sequence setting unit 45 generates a
DWI-Prep sequence as shown in FIG. 6 according to instructions from
the input device 33. The pulse sequence setting unit 45, for
example, sets a two-dimensional single shot balanced SSFP sequence
as the imaging sequence of the DWI-prep sequence. The DWI-Prep
sequence set as the single shot multi DWI sequence is provided to
the sequence controller control unit 40.
[0138] Next in step S2, the DWI-prep scan is performed. For this
purpose, an object P is set on the bed 37 and a static magnetic
field is generated in an imaging area of the static magnetic field
magnet 21 (super conductive magnet) excited by static magnetic
field power supply 26. When an instruction to perform the DWI-Prep
scan from the input device 33 is provided to the sequence
controller control unit 40, the sequence controller control unit 40
drives and controls the sequence controller 31 by providing the
DWI-Prep sequence to the sequence controller 31.
[0139] Then, the sequence controller 31 forms an X-axis gradient
magnetic field Gx, a Y-axis gradient magnetic field Gy and a Z-axis
gradient magnetic field Gz and generates RF signals in the imaging
area where the object P is set by driving the gradient power supply
27, the transmitter 29 and the receiver 30 according to the
DWI-Prep sequence received from the sequence controller control
unit 40. Specifically, the transmitter 29 transmits the RF signals
to the RF coil 24 sequentially according to the DWI-Prep sequence,
and the RF coil 24 transmits the RF signals to the object P.
[0140] MR signals generated in a selected slice in the object P due
to the transmitted RF signals are received by the RF coil 24. When
the MR signals are received by the RF coil 24, the receiver 30
receives the MR signals from the RF coil 24 to perform various
signal processing including pre-amplification, intermediate
frequency conversion, phase detection, low-frequency amplification
and filtering. The receiver 30 generates raw data which are the MR
signals of digital data by A/D conversion of the MR signals. The
receiver 30 provides the generated raw data to the sequence
controller 31.
[0141] This acquisition of raw data is performed in synchronization
with ECG based on an ECG signal acquired by the ECG unit 38.
Herewith, pieces of raw data corresponding to a systole and a
diastole of the myocardium are acquired respectively.
[0142] The sequence controller 31 provides the raw data received
from the receiver 30 to the sequence controller control unit 40,
and the sequence controller control unit 40 arranges the raw data
obtained by the DWI-Prep scan as k-space data in k-space formed in
the k-space database 41.
[0143] Then, the image reconstruction unit 42 reconstructs three
dimensional image data of the object P by reading the k-space data
from the k-space database 41 and performing a predetermined image
reconstruction processing such as three-dimensional Fourier
transformation. The image reconstruction unit 42 the writes
three-dimensional image data into the image database 43. Then, the
blood flow image generating unit 44 reads pieces of 3D image data
corresponding to a diastole and a systole of the myocardium,
respectively, from the image database 43, cancels vein data by
subtraction processing to the pieces of 3D image data and depicts
artery data as a blood flow image. Thus, blood flow images
corresponding to the respective intensities of the MPG pulse are
depicted. The depicted blood flow images are displayed on the
display unit 34.
[0144] Since the blood flow images displayed on the display unit 34
are obtained with the MPG pulses having mutually different
intensities respectively, depiction accuracies of arteries are
different between the blood flow images. In addition, since the
intensities of the MPG pulses are changed in three axis directions
depending on travel directions of blood vessels, a blood flow image
depicting arteries satisfactorily exists in the acquired plural
blood flow images. Especially when data was acquired with a scroll
acquisition, effect of the MPG pulse on the blood flow image is
improved.
[0145] Then, in Step S3, the optimum intensity of DWI to depict a
blood flow image, which is a combination of intensities of an MPG
pulse in three axis directions, is determined. The intensity of DWI
can be determined by selecting a blood flow image depicting target
blood vessels most satisfactorily with arteriovenous separation
from multiple blood flow images displayed on the display unit 34
through user's operation of the input device 33 for example. When
the user selects one blood flow image, selection information of
blood flow image is provided from the input device 33 to the pulse
sequence setting unit 45. The pulse sequence setting unit 45
obtains the combination of the intensities of the MPG pulse in
three axis directions corresponding to the selected blood flow
image from information concerning imaging conditions attached to
blood flow image data for example.
[0146] Then, in Step S4, a sequence for the imaging scan is set in
the pulse sequence setting unit 45. The sequence for the imaging
scan has a DWI sequence and an imaging sequence. An intensity of an
MPG pulse in the DWI sequence is set to the intensity determined in
step S3. The imaging sequence for the imaging scan uses a sequence
equivalent to that in the DWI-Prep sequence as possible. Therefore,
for example, the pulse sequence setting unit 45 sets a
three-dimensional single shot balanced SSFP sequence as the imaging
sequence for the imaging scan.
[0147] Consequently, a sequence for the imaging scan as shown in
FIG. 9 is generated in the pulse sequence setting unit 45. Further,
a scroll of data acquisition timings and an order of data
acquisition are set and reflected on the imaging sequence for the
imaging scan in the pulse sequence setting unit 45 according to
instructing information from the input device 33. The imaging
sequence for the imaging scan generated ultimately is provided from
the pulse sequence setting unit 45 to the sequence controller unit
40.
[0148] Then, in Step S5, the imaging scan is performed.
Specifically, when an instruction to start the imaging scan is
provided from the input device 33 to the sequence controller unit
40, the sequence controller unit 40 drives and controls the
sequence controller 31 by providing the sequence for the imaging
scan to the sequence controller 31. Consequently, the imaging scan
is performed and k-space data acquired by the imaging scan are
arranged in k-space formed in the k-space database 41.
[0149] Then, in Step S6, a blood flow image is generated from data
acquired by the imaging scan and is displayed on the display unit
34. Specifically, arteries data with arteriovenous separation are
depicted as the blood flow image through image reconstruction
processing by the image reconstruction unit 42 and subtraction
processing of 3D image data by the blood flow image generating unit
44, and are displayed on the display unit 34.
[0150] Since the blood flow image displayed on the display unit 34
is imaged with optimizing the intensities of the MPG pulse in the
three axis directions depending on the travel directions of the
blood vessels, the blood flow image depicts the arteries very
satisfactorily. Especially when data is acquired under the scroll
acquisition, the blood flow image shows an improved effect of the
MPG pulse. In addition, when the acquisition timings of data near
the center of k-space are scrolled into the diastole and the
systole, the blood flow image depicting the arteries satisfactorily
as described above can be generated from only data acquired in a
single heart rate.
[0151] That is, the magnetic resonance imaging apparatus 20 as
mentioned above applies a flow selective gradient magnetic field
pulse for compensating a blood flow or accelerating flow void
effect and also performs an imaging scan for a no-contrast-enhanced
MRA using a sequence without dependence on travel directions of
target blood vessels.
[0152] Further, as needed for a no-contrast-enhanced MRA, the
magnetic resonance imaging apparatus 20 performs a DWI-Prep scan
which is a preparation scan for single shot multi DWI for imaging
with changing an intensity of DWI (an MPG pulse) as an example of
flow selective gradient magnetic field pulse, like as an ECG-Prep
scan which is a preparation scan performed with changing
parameters, prior to an imaging scan. Thus, the magnetic resonance
imaging apparatus 20 measures an intensity of an MPG pulse suitable
to depict target blood vessels with arteriovenous separation in
advance. Then, the magnetic resonance imaging apparatus 20 performs
a 3D scan using an imaging sequence such as a SSFP sequence with
applying an MPG pulse having a determined intensity suitable for 3D
imaging. Accordingly, by the magnetic resonance imaging apparatus
20, it is possible to obtain a 3D image of blood vessels with
satisfactory arteriovenous separation.
[0153] Especially in the magnetic resonance imaging apparatus 20,
intensities of an MPG pulse applied as a flow selective gradient
magnetic field pulse can be changed arbitrarily in three axis
directions. Further, a sequence without dependence on
directionality of blood flows can be used as an imaging sequence.
For this reason, according to the magnetic resonance imaging
apparatus 20, it is only necessary to set an intensity of an MPG
pulse depending on travel directions of blood vessels in order to
improve arteriovenous separation performance so that an intensity
of a signal from a blood flow having a high-velocity in a systole
is suppressed to increase a difference between respective signals
from a blood flow in a diastole and a systole for example.
[0154] Therefore, the magnetic resonance imaging apparatus 20 has
no necessity to increase an ETS of an FASE method or an SSFP method
in order to improve arteriovenous separation performance. As a
result, the magnetic resonance imaging apparatus 20 can achieve
satisfactory arteriovenous separation of blood vessels having
higher velocities, thereby achieving arteriovenous separation
without dependence on a velocity of a blood flow. In addition, the
magnetic resonance imaging apparatus 20 can also improve
flexibility for setting an imaging sequence.
[0155] Additionally, in the magnetic resonance imaging apparatus
20, when a sequence without dependence on directionality of blood
flows is used as an imaging sequence, a depiction performance of
blood flows can be improved by satisfactory arteriovenous
separation of blood vessels traveling in arbitrary directions.
Especially in case of performing arteriovenous separation of blood
flows having low velocities like as a lower limb MRA, a dephasing
pulse needed to be applied in an RO direction conventionally. For
this reason, a depiction performance of blood vessels depended on
travel directions of the blood vessels. To the contrary, the
magnetic resonance imaging apparatus 20 can perform satisfactory
arteriovenous separation even of blood flows having low velocities
like as a lower limb MRA.
[0156] Further, the magnetic resonance imaging apparatus 20 can
also determine an optimum intensity, depending on a blood flow
velocity, of a flow selective gradient magnetic field pulse such as
an MPG pulse to maximize a blood-flow signal from target vessels in
advance by a preparation scan such as a DWI-Prep scan without
changing an imaging sequence.
* * * * *