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MRI medical imaging
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Fundamentals of Magnetic Resonance
Imaging
- Hardware and Principle
Outline
History of Magnetic Resonance Imaging
MR Imaging Hardware System
Principle of MRI
Timeline of MR Imaging
1920 1930 1940 1950 1960 1970 1980 1990 2000
1924 - Pauli suggests
that nuclear particles
may have angular
momentum (spin).
1937 Rabi measures
magnetic moment of
nucleus. Coins
magnetic resonance.
1946 Purcell shows that
matter absorbs energy at a
resonant frequency.
1946 Bloch demonstrates
that nuclear precession can be
measured in detector coils.
1972 Damadian
patents idea for large
NMR scanner to detect
malignant tissue.
1959 Singer
measures blood flow
using NMR (in mice).
1973 Lauterbur
publishes method for
generating images
using NMR gradients.
1973 Mansfield
independently
publishes gradient
approach to MR.
1975 Ernst develops
2D-Fourier transform for
MR.
NMR renamed MRI
MRI scanners become
clinically prevalent.
1990 Ogawa and
colleagues create
functional images using
endogenous, blood-
oxygenation contrast.
1985 Insurance
reimbursements for
MRI exams begin.
Source: http://www.fonar.com/timelineofmri.htm
Nobel Prizes for Magnetic Resonance
1944: Rabi (Physics)
resonance method for recording magnetic properties of atomic nuclei
1952: Felix Bloch and Edward Mills Purcell (Physics)Basic science of NMR phenomenon
1991: Richard ErnstChemistry (High-resolution pulsed FT-NMR)
2002: Kurt WthrichChemistry (3D molecular structure in solution by NMR)
2003: Paul Lauterbur & Peter MansfieldPhysiology or Medicine (MRI technology)
Modern 3 Tesla
MRI unit (Philips)
Main magnet
body
Patient Couch
Bore of the magnet
Instrumentation (1)
RF Coil (for head)
Instrumentation (2)
Magnet RF Coil
Source: Joe Gati, photos
Gradient Coil
Main Components of a Scanner Static Magnet (1)
Permanent Magnet
open
C-Shape
Standing MRI
Advantage:
-Simple
-Comfortable
-Inexpensive
-No need to use liquid Helium
-Low maintenance cost
Disadvantage:
-Low field strength (normally
Superconductive Magnet
closed
cylindrical
Static Magnet (2)
Advantage:
-High-field (normally >1.5T)
-High stability
-High homogeneity
-Cost low
Disadvantage:
-Expensive
-Helium needed
-High maintenance cost
Magnetic Field Strength
Measured by Tesla (T) vs Gauss (G)
1T = 10,000G
Earths magnetic field ~ 0.3~0.7G
Clinical MRI typically between 0.7T and 3.0T. It is very strong!
High field MRI
Advantage:
1) High SNR
2) Short acquisition time
3) Enable advanced MR
imaging, such as
MRS, BOLD etc
1cm
5 A
1 Guass
Disadvantage:
1) High cost
2) High noise
3) High SAR
4) High artefact
Gradient Magnets RF Coils
"antenna" of the MRI system
broadcasts the RF signal
and/or
receives the return signal
loop of wire
depth of the image generally limited to about one radius
for spines, shoulders, small body parts
Commonly for the knee
Better homogeneity
Volume coil
two parallel circular coils
pelvis imaging and cervical
spine imaging
Provides the best RF homogeneity
Commonly used as a transceiver coil
e.g., head, knee
Start
Atom = nucleus + electrons
Nucleus = neutrons + protons
Atom number = # protons
Atom weight = #neutrons + # protons
About Atom: A Review
To differentiate
atoms
Same atom
number but
different atom
weight are
different isotopes
Spin
Protons (nuclear constituent of atom) have a property of angular
momentum known as spin
Motion of electrically charged particles results in a magnetic force
orthogonal to the direction of motion
The spin value depends on the atomic number and atomic weight of the
particular nucleus.
Why 1H?
Reasons for choosing 1H:
1)1H occupies the largest proportion
- 3*1022/ml in water
1) Gyromagnetic ratio is much larger than others, and thus the magnetic
resonance signal is the largest
3) Different forms in biological organ
- water
- fat
So by default, MRI is 1H imaging!
Protons Aligning within a Magnetic Field
In field free space
randomly oriented
Source: Mark Cohens web slides Source: Robert Coxs web slides Source: Jody Culhams web slides
when placed in a magnetic field (B0; e.g., our MRI machines) protons will either align
with the magnetic field
there is a small difference in the number of protons in the low and high energy
states with more in the low state leading to a net magnetization (M)
Inside magnetic field
oriented with or against B0M = net magnetization
M
Precession
Protons precess in external magnetic field. The precessional axis is
parallel to the external magnetic field.
Source: Mark A. Brown, Richard C. Semelka
The Nobel Prize in Physics 1944
Rabi predicted that the magnetic moments of nuclei
could be induced to flip their magnetic orientation if
they absorbed energy from an electromagnetic wave
of the right frequency. They would also emit this
same amount of energy in falling back to the lower
energy orientation, and Rabi would be able to detect
this transition from one energy state to the other. He
called this method molecular beam magnetic
resonance.
Isidor Isaac Rabi
(1898-1988)
Austrian
For resonance method for recording the magnetic
properties of atomic nuclei
Larmor Equation
Frequency (rate) of precession is proportional to the strength of
magnetic field
: Gyromagnetic ratio
Unit of /2 pi : MHz/T
Resonance
frequency (MHz)Magnetic field (T)
Larmor frequency slightly depends on the molecular structure the
protons 1H belong to. Fat molecules are large and surrounded by many
electrons, which reduce the effective external field. This way the Larmor
frequency of fat is roughly 150 Hz lower at 1 T (220 Hz at 1.5 T) than that
of water.
Gyromagnetic Ratio
For the following scanners,
What is the resonance frequency of the following nuclei in
each of the magnetic fields?
1H23Na31P
Question
/2
(MHz/T)
Bo
= 0.7T Bo
= 3.0T Bo
= 7T
1H 42.57
23Na 11.26
31P 17.23
Phillips 3.0 Tesla
Clinical MRI
GE 0.7 Tesla
low field MRI
SIEMENS 7.0 Tesla
High field MRI
Question Net Macroscopic Magnetization (no B0)
when an external magnetic field is absence
= (0,0,0)
Net Macroscopic Magnetization (with B0)
The phenomenon of quantized energy states in the presence of an
external magnetic field is known as the Zeeman effect
The energy difference (E) between the two levels is exactly
proportional to the frequency v and thus the magnetic field B0:
Zeeman Effect
h (Planck's constant)
= 6.626 10-34 Js
low energy state (spin up)
high energy state (spin down)
Net Macroscopic Magnetization (with RF)
Before:
1) # low-energy protons are slightly more than # high energy protons
2) No net magnetization in the transverse plane -- the phase of transverse components
are random
After:
1) half of the different protons with low energy reversed their energy state no net
macroscopic longitudinal magnetization
2) The phase of the transverse component are consistent
Effect of a 90o Pulse Excitation
Bo
Coordinate System
Absorption of the RF energy of frequency causes M0 to
rotate away from its equilibrium orientation by an angle
Flip Angle
Break
Types of Relaxation
When the RF is turned off, the return to equilibrium iscalled relaxation
The protons immediately begin to realign themselves and return to their original equilibrium orientation
Longitudinal relaxation precessing protons are pulled back into alignment with main magnetic field of the scanner (B
o) reducing
size of the magnetic moment vector in the x-y plane
Transverse relaxation precessing protons become out of phase leading to a drop in the net magnetic moment vector (M
o)
Transverse relaxation occurs much faster than longitudinal relaxation
T1 decay describes the longitudinal magnetization returns to equilibrium.
Longitudinal Relaxation
T1 = time required for Mz to recover 63% of its original value
http://www.youtube.com/watch?v=A0dl4_wxr1c&list=PLCD41685D8499AAB1
Mz(t) = Mo(1 - e-t/T1).
Transverse Relaxation
T2 decay describes the return to equilibrium of the transverse magnetization, MXY
T2 = time required for 63% of the initial magnetization (Mxy) to dissipate
Mxy(t) = Mxyoe-t/T2
http://www.youtube.com/watch?v=7K-Dg5jmV-8&list=PLCD41685D8499AAB1
Summary of Relaxation
Energy emission
After break
MR signal
Tissue A
Mxy
Tissue B
MxyMR signal
Tissue B
MR signal
Tissue A
T2 Weighted Imaging
Tissue A
Mz
Tissue B
Mz
Tissue A
Mxy
Tissue B
Mxy
Tissue A
Mxy
Tissue B
Mxy
Signal
Tissue A
Signal
Tissue B
1. For Tissue A and B
PD are the same
Mz are the same
when 900 RF pulse is
on, Mz changed to 0
2. When 900 RF pulse
is on, for Mxy, A = B
3. After some time, for
Mxy, A > B
For T2: A > B
4. The MR signal: A > B
T1 Weighted Imaging
Tissue A
Mz
Tissue B
Mz
Tissue A
Mz
Tissue B
Mz
Tissue A
Mxy
Tissue B
Mxy
Signal
Tissue A
Signal
Tissue B1. For Tissue A and B
PD are the same
Mz are the same
when 900 RF pulse is
on, Mz changed to 0
2. When 900 RF pulse
is off, Mz gradually
recovered.
For Mz, A > B
Given T1: A > B
3. Apply another 900 RF pulse
Mz gradually recovered.
For Mxy, A > B4. MR signal: A > B
The Nobel Prize in Physics 1952
Felix Bloch
Switzerland Edward Mills Purcell
U.S.A
for their development of new methods for nuclear magnetic precision
measurements and discoveries in connection therewith
- Scientific principle of MRI
- determine the time evolution
of nuclear magnetization
- relaxation phenomena
- related problems of molecular structure
- measurement of atomic constants,
- nuclear magnetic behaviour at low
temperatures
PD=proton density
Summary
For samples in external magnetic field, the
sample is exposed to energy at the correct
frequency that will be absorbed.
A short time later, this energy is reemitted,
which can be detected and processed.
A brief summary video
http://www.youtube.com/watch?v=1CGzk-
nV06g