Presentation on theme: "Introduction to Medical Imaging MRI – Magnetic Resonance Imaging"— Presentation transcript:
1Introduction to Medical Imaging MRI – Magnetic Resonance Imaging CourseIntroduction to Medical Imaging MRI – Magnetic Resonance ImagingGuy Gilboa
2MRI invention Several involved: Nobel prize 2003, Raymond Damadian – 1971, idea still very sketchy, no images produces.Paul Lauterbur – , mature technique for 2D and 3D imaging. Produced first image of a living mouse.Peter Mansfield - developed a mathematical technique where scans take seconds rather than hours also producing clearer images.Nobel prize 2003,Paul LauterburSir Peter Mansfield(Damadian left out, protests of him and colleagues).From top: Damadian, Lauterbur, Mansfield.
3MRI scannerThe lecture is based mainly on:   Ch. 5 of the book by N. B. Smith and A. Webb, Introduction to Medical Imaging, Cambridge University Press, 2011.
5MRI – basic operation principle The MRI is comprised of 3 main components:A superconducting primary magnet3 magnetic field gradient coilsRF transmitter and receiverTaken from https://wiki.engr.illinois.edu/display/BIOE414/Team+4+-+MRI+Radio+Frequency+Coils
6Movie – how MRI works (8.5 min.) https://www.youtube.com/watch?v=Ok9ILIYzmaY
7Energy unitsTesla: A particle carrying a charge of 1 coulomb and passing through a magnetic field of 1 tesla at a speed of 1 meter per second perpendicular to said field experiences a force with magnitude 1 newton, according to the Lorentz force law. 𝑇= 𝑉∙𝑠 𝑚 2 = 𝐽 𝐴𝑚 2 = 𝑊𝑏 𝑚 2 = 𝑁∙𝑠 𝐶∙𝑚 = 10 4 gV=volt; s=second; m=meter; J=joule; A=ampere; Wb=webber; N=newton; C=coulomb; g=gauss.
8Lorentz force 𝐹=𝑞(𝐸+𝑣×𝐵) A particle of charge q moving at velocity v in the presence of an electric field E and a magnetic field B, experiences the force:𝐹=𝑞(𝐸+𝑣×𝐵)
9Faraday inductionThe voltage induced V is proportional to the time rate of change of the magnetic flux 𝜑: 𝑉∝− 𝑑𝜑 𝑑𝑡
10Some symbols 𝜇 [ J/T] = magnetic moment P [ J ∙ s] = angular momentum 𝛾 [Hz/T] gyromagnetic ratioFor protons: 𝛾= Mhz/T𝜇 =𝛾| 𝑃 |∆𝐸 [𝐽] Energy difference between parallel and anti-parallel. ∆𝐸= 𝛾ℎ 𝐵 0 2𝜋M [A/m] = net magnetization.Torque [N ∙m] = moment of force
11Magnetic Fields used in MR: 1) Static main field Bo2) Radio frequency (RF) field B13) Gradient fields Gx, Gy, Gz
16Magnetic MomentsMR is exhibited in atoms with odd # of protons or neutrons.Spin angular momentum creates adipole magnetic momentPlanck’s constant / 2Intuitively current, but nuclear spinoperator in quantum mechanics= gyromagnetic ratio : the ratio of the dipole moment to angular momentumWhich atoms have this phenomenon?1H - abundant, largest signal31P23NaModel proton as a ring of current.
17Energy states resonance frequency fo Energy of Magnetic Moment in Hydrogen has two quantized currents,Bo field creates 2 energy states for Hydrogen whereenergy separationresonance frequency fo
18Nuclei spin states There are two populations of nuclei: n+ - called paralleln- - called anti parallelhigher energyn-lower energyn+Which state will nuclei tend to go to? For B= 1.0TBoltzman distribution:Slightly more will end up in the lower energy state. We call thenet difference “aligned spins”.Only a net of 7 in 2*106 protons are aligned for H+ at 1.0 Tesla.(consider 1 million +3 in parallel and 1 million -3 anti-parallel. But...
19There is a lot of a water!18 g of water is approximately 18 ml and has approximately 2 moles of hydrogen protonsConsider the protons in 1mm x 1 mm x 1 mm cube.2*6.62*1023*1/1000*1/18 = 7.73 x1019 protons/mm3If we have 7 excesses protons per 2 million protons, we get .25 million billion protons per cubic millimeter!!!!
20Torque – mechanical analogy Spins in a magnetic field are analogous to a spinning top in a gravitational field.Magnetic Torque(gravity - similar to Bo)Top precesses about
21Precession rotates (precesses) about Usually, Bo = .1 to 3 Tesla Precessional frequency:oris known as the Larmor frequency.for 1HUsually, Bo = .1 to 3 TeslaSo, at 1 Tesla,fo = MHz for 1H1 Tesla = 104 Gauss
22Precession – Movie (7 min.) https://www.youtube.com/watch?v=7aRKAXD4dAg
23RF Magnetic field The RF Magnetic Field, also known as the B1 field To excite nuclei ,apply rotating field at o in x-y plane. (transverse plane)B1 radiofrequency field tuned to Larmor frequency and applied in transverse (xy) plane induces nutation (at Larmor frequency) of magnetization vector as it tips away from the z-axis.- lab frame of reference
24RF general excitation (rotating frame) By design ,In the rotating frame, the frame rotates about z axis at o radians/secxyz1) B1 applies torque on M2) M rotates away from z.(screwdriver analogy)3) Strength and duration of B1 determines flip angle.This process is referred to as RF excitation.
25Coils diagram Simplified Drawing of Basic Instrumentation. Body lies on table encompassed by coils for static field Bo,gradient fields (two of three shown), and radiofrequency field B1.Image, caption: copyright Nishimura, Fig. 3.15
26Detection - Switch RF coil to receive mode. xyzMPrecession of M induces EMF in the RF coil. (Faraday’s Law)EMF time signal - Lab frameVoltaget(free induction decay)for 90 degree excitation
27T1 and T2 relaxation times Application of RF pulse creates non- equilibrium state (adding energy to the system).After the pulse is switched off, the system is relaxed back to equilibrium.There are 2 relaxation times which govern the return to equilibrium:T1 (spin-lattice), equilibrium of z component.T2 (spin-spin), x and y components.
28Tissue relaxation times for 1.5 Tesla T1 (ms)T2 (ms)White matter79090Gray matter920100Liver50050Skeletal muscle87060Lipid (מסיס שומן)290160Cartilage (סחוס)106042S?Table: 5.1 from 
29Bloch Equation Solution: Longitudinal Magnetization Relaxation Component The greater the difference from equilibrium,the faster the changeSolution:Initial MzDoesn’t have to be 0!Return to Equilibrium
30Transverse time constant T2 - spin-spin relaxationT2 values: < 1 ms to 250 msWhat is T2 relaxation?- z component of field from neighboring dipoles affects theresonant frequencies.- spread in resonant frequency (dephasing) happens on themicroscopic level.- low frequency fluctuations create frequency broadening.Image Contrast:Longer T2’s are brighter in T2-weighted imaging, darker in T1-weighted imagingS?
31MR: Relaxation: Some sample tissue time constants - T1 Approximate T1 values as a function of Bogray mattermusclewhite matterkidneyliverS?fatImage, caption: Nishimura, Fig. 4.2
32Gradient Fields - key for imaging - Paul Lauterbur Gradient coils are designed to create an additional B field that varies linearly across the scanner as shown below when current is driven into the coil. The slope of linear change is known as the gradient field and is directly proportional to the current driven into the coil.The value of Bz varies in x linearly.zBzBoslope = GzWhole Body Scanners:|G| = 1-4 G/cm(10-40 mT/m)Gz can be considered as the magnitude of the gradient field, or as the current level being driven into the coil.
33Basic Procedure 1) Selectively excite a slice (z) - time? .4 ms to 4 ms- thickness? 2 mm to 1 cm2) Record FID, control Gx and Gy- time? 1 ms to 50 ms3) Wait for recovery- time? 5 ms to 3s4) Repeat for next measurement.- measurements? 128 to 512- in just 1 flip5) Next: More on spatial encoding
34Phase and frequency encoding It is not important which dimension encodes frequency and which phase.We assume:X encodes frequencyY encodes phase
35Frequency encodingX-dimension is encoded by applying a frequency-encoding gradient 𝐺 𝑓𝑟𝑒𝑞 .Protons precess at the frequency 𝜔 𝑥 = 𝛾 𝐺 𝑥 𝑥A total of 𝑁 𝑓 data points are acquired while the receiver is on (e.g. 256).There is a delay between successive RF pulses, called TR = time of repetition.
36Phase encodingY-dimension is encoded by applying a phase- encoding gradient 𝐺 𝑝ℎ𝑎𝑠𝑒 for a period of 𝜏 𝑝𝑒 and then switched off.During the interval 𝜏 𝑝𝑒 protons precess at the frequency 𝜔 𝑦 =𝛾 𝐺 𝑦 𝑦 and we have a spatially dependent phase shift𝜑 𝑝𝑒 = 𝜔 𝑦 𝜏 𝑝𝑒 =𝛾 𝐺 𝑦 𝑦 𝜏 𝑝𝑒 .A total of 𝑁 𝑝𝑒 dphase encoding steps are applied, with a total slice acquisition time of 𝑇𝑅∙𝑁 𝑝𝑒 .
37K-space formalism (5.10)Given the proton density 𝜌(𝑥,𝑦), the 𝑁 𝑓 ×𝑁 𝑝𝑒 data samples can be expressed as:𝑠 𝐺 𝑦 , 𝜏 𝑝𝑒 , 𝐺 𝑦 ,𝑡 = 𝑠𝑙𝑖𝑐𝑒 𝜌(𝑥,𝑦) 𝑒 −𝑗𝛾 𝐺 𝑦 𝑦 𝜏 𝑝𝑒 𝑒 −𝑗𝛾 𝐺 𝑥 𝑥𝑡 𝑑𝑥𝑑𝑦In the k-space formalism [Ljunggren-1983] we assign 𝑘 𝑥 = 𝛾 2𝜋 𝐺 𝑥 𝑡, 𝑘 𝑦 = 𝛾 2𝜋 𝐺 𝑦 𝜏 𝑝𝑒 to get𝑆 𝑘 𝑥 , 𝑘 𝑦 = 𝑠𝑙𝑖𝑐𝑒 𝜌(𝑥,𝑦) 𝑒 −𝑗2𝜋 𝑘 𝑥 𝑥 𝑒 −𝑗2𝜋 𝑘 𝑦 𝑦 𝑑𝑥𝑑𝑦
38Image recoveryTo recover the proton density 𝜌(𝑥,𝑦), we simply use the inverse Fourier transform:𝜌(𝑥,𝑦) = −∞ ∞ 𝑆 𝑘 𝑥 , 𝑘 𝑦 𝑒 +𝑗2𝜋 (𝑘 𝑥 𝑥+ 𝑘 𝑦 𝑦) 𝑘 𝑥 𝑘 𝑦
39k-Space Acquisition ky kx Phase Direction One line of k-space EncodeSampledSignalDAQkxkyPhaseDirectionOne line of k-spaceacquired per TRFrequency DirectionTaken from 
47Signal Intensity and SNR The signal is proportional to:The number of protons in the voxel.The square of B0 fieldNet magnetization 𝑀 0 ∝ 𝐵 0Induced voltage 𝑉∝ 𝜔 0 ∝ 𝐵 0SNR:𝑆𝑁𝑅∝ 𝐵 0 3/2𝜔 0 =precession frequency
48Multiple slice imaging The TR time required between successive RF excitations for each phase encoding step is much longer than TE.In this time other adjacent slices are usually acquired (maximum of TR/TE)Usually this is done in an interlacing fashion – od numbered slices are followed by even-numbered slices.
49Spin-echo imaging sequence SS – Slice selection, PE – Phase encoding, FE – Frequency encoding, TR – Time of repetition, TE – Time of echo.
50T1, T2, PDA long TR and short TE sequence is usually called Proton Density (PD) –weighted.A short TR and short TE sequence is usually called T1- weightedA long TR and long TE sequence is usually called T2-weightedTaken from
51MR angiographyIncrease signal difference between flowing blood and tissueBased on TOF (time-of-flight) technique, shorter effective T1 due to flow if the slice is oriented perpendicular to the direction of flow.1 𝑇 1,𝑒𝑓𝑓 = 1 𝑇 1 + 𝑏𝑙𝑜𝑜𝑑 𝑣𝑒𝑙𝑜𝑐𝑖𝑡𝑦 𝑆𝑙𝑖𝑐𝑒 𝑡ℎ𝑖𝑐𝑘𝑛𝑒𝑠𝑠
52Functional MRIDetermines which areas of the brain are involved in cognitive tasks and brain functions such as speech and sensory motion.Based on the fact that MRI signal intensity changes depending upon the level of oxygenation of the blood in the brain (indicating increased neuronal activity).Uses fast scans which can cover the brain in a few seconds.
53Example of fMRIBrain activity changes of teenagers playing violent video games.Taken from
54MR contrast agents Positive Negative Paramagnetic contrast agents, shorten the T1 of tissue in which they accumulate.Based on gadolinium ion (Gd).Used to detect tumors, lesions in the central nervous system (brain and spine).NegativeSuperprparamgnetic (iron oxides), reduce T2 relaxation time.Used in detection of liver lesions.
55Image characteristics (5.20) SNR trends∝𝐵 0 3/2Inverse proportional to spatial resolution.Proportional to the square-root of acquisition time.Spatial resolution defined byThe slice thickness.The field-of-view (FOV) divided by the number of phase-encoding steps.The FOV in the frequency-encoded dimension divided by the number of acquired data points.
56Characteristics (cont’) Contrast to noiseContrast is based on T1, T2, PD scans.Can be manipulated by choices of TR, TE.For small lesions, the contrast is increased by having higher spatial resolution to minimize partial volume artifacts.
57Examples – brainComparison of PD, T1, T2 and angiography.
58Cardiology4 chamber view MR angiography of the chest (18 sec scan time)
59Some clinical applications of MRI Used widely to scan almost every organ in the body, popular uses are:Neurological applicationsCan diagnose both acute and chronic neurological deseases.Method of choice for brain tumor detection.Most protocols involve administration of Gd.Many pathological conditions in the brain result in increased water content, which gives high signal intensity on T2-weighted sequences.
60Clinical apps (cont’) Liver and Muscoloskeletal Cardiology Can diagnose well lesions in fatty liver. Also iron overload, liver cysts, several lesions.Muscle-skeleton system. Knee scans to diagnose arthritis (joint inflammation).CardiologyTo reduce motion artifacts - scans are gated according to the cardiac cycle, based on electrocardiograms (ECG).Detects myocardial infarcts, can measure left ventricular volume and ejection fraction. Good contrast between blood and myocardial wall.Diagnose coronary artery stenosis using angiography.
61MRI summary Advantages: Drawbacks: 3D data – basically measures concentration of water.Many possible modes.Very good for soft tissues.No ionizing radiation.Drawbacks:Expensive.Slow scan time.Large magnets → cannot scan people with metal implants.
62MRI vs CT – Brain imageBetter contrast in MRI for soft tissues, easy to distinguish between gray and white matter.
63Comparison between MRI and CT Ionizing radiationYesNoCostlowerHigher (x3?)Speed10-30 s (full scan 5-10 min).Several minutes (full scan 30-60min)Data modesFewMany3D imagesResolution~7 lp/cm~3 lp/cmWork with metal in the bodySNR increases asRadiation increases, or body is smaller.Primary magnet is stronger (also acquisition time)