What is MRI?
MRI stands for Magnetic Resonance Imaging; it is a technique that has been used over the last 35 years for medical diagnostics. It involves the interaction of the atoms in the body with electromagnetic fields – we rely on the nuclear spin of an atom to create the images.
The human body is largely composed of water molecules (H2O). These molecules contain 2 hydrogen nuclei, which is 2 protons. When protons come under the effect of a magnetic field, the magnetic moments of these protons align with the direction of the field.
Essentially all MRI is hydrogen (proton) imaging.
Physics of MRI
Nuclear Magnetism Resonance (NMR)
Subatomic particles have quantum properties of a “spin”. (A spin is a form of angular momentum). Some nuclei, such a protons, have a non-zero spin, and therefore a magnetic moment – the nuclei produces a tiny magnetic field around itself. When these spins are placed in a strong external magnetic field, they precess around an axis along the direction of the field.
The best way to think of this effect is to consider each atom as a tiny bar magnet – because we have a system of tiny magnets, by applying a bigger magnetic field, we can manipulate their direction. It is worth noting that because their coupling is very weak, this does not change their physical or chemical properties and that other than radicals, molecules tend to gave zero magnetic moment.
If we apply an external magnetic field B0 to our system of tiny magnets, we can cause some of the to line up with it resulting in a non zero bulk magnetisation M. This effect is called nuclear spin polarisation and B0 is often called the polarising field.
Resonance and Relaxation
Magnetisation can be manipulated by changing the magnetic field environment (static, gradient and RF fields). RF waves are used to manipulate the magnetization of protons; externally applied RF waves perturb magnetisation into different axis (transverse axis). Only transverse magnetisation produces signal. When perturbed protons return to their original state, they emit RF signals that are detected by coils in the MRI machine.When RF pulses are stopped, the high energy gained by the protons are re-transmitted, and the protons relax by two mechanisms:
- T1 (spin lattice relaxation) – by which original magnetisation begins to recover.
- T2 (spin spin relaxation) – by which magnetisation in x-y plane decays towards zero in an exponential fashion. This is due to incoherence of protons.
T1 Relaxation
After protons are excited with an RF pulse, they move out of alignment with B0 (the polarising field). Once the RF is stopped, they realign after some time – this is called T1 relaxation. T1 is defined as the time it takes to recover 63% of it longitudinal magnetisation.
T2 Relaxation
When the tipped spins of the protons are precessing, they de-phase; this is die to them not spinning at precisely the same speed. As they get out of phase, the magnetisation is no longer coherent, and the signal delays. T2 relaxation is the time for 63% of the protons to become dephased owing to interactions among nearby protons.
TR (echo time) & TR (repetition time)
TE – time interval in which signals are measured after RF excitation.
TR – the time between two excitation is called repetition time.
Construction of an MRI scanner
In a clinical environment, magnetic fields of above 0.5 Teslas are mostly desired; superconducting magnets are therefore required in the scanners as they produce very large magnetic fields that are exceptionally stable.
Magnets
Superconducting magnets are used for MRI scanning; they are solenoid-shaped coil made of alloys surrounded by copper.
Maintaining large magnetic fields require a large amount of energy which is accomplished by superconductivity, or reducing the resistance in the wire to almost zero. To do this, the wires are continually bathed in liquid helium, at around 10 Kelvin. This cold is then insulated by a vacuum.
Gradient Coils
Gradient coils are used to spatially encode the positions of the protons by varying the magnetic field linearly across the imaging volume. They produce deliberate variations in the magnetic field B0. There are 3 sets of gradient coils – one for each direction. The variation in the magnetic field permits localisation of image slices, as well as phase encoding and frequency encoding.
Radio frequency coil
These coils broadcast the RF signal to the patient, and also receives the returning signal. Different coils can be used when imaging different parts of the body:
- Birdcage coil – commonly used for imaging of the head
- Paired saddle coil – commonly used for imaging of the knee. These coils are used as volume coils, and provide better homogeneity of the RF in areas of interest.
- Surface coils – used for spines, shoulders, joints, and small body parts.
- Helmholtz pair coil – these are two circular coils parallel to each other. They are used as Z gradient coils, and sometimes as RF coils for pelvis and cervical spine imaging.
Imaging Techniques
Different tissues have different relaxation times. These relaxation time differences are used to generate image contrast.
Contrast enhanced imaging
Image contrast is created by differences in the strength of the NMR signal, recovered from different locations within the sample (eg. fat and muscle). This depends on the relative density of the excited nuclei (protons), on difference in relaxation times (T1, T2 & T2*) of the nuclei after the pulse sequence.
Contrast in most MR images is actually a mixture of all these effects, but by carefully planning the design of the imaging pulse sequence allows one contrast mechanism to be emphasized, whilst the others are minimised. This ability to choose different contrast mechanisms gives MRI tremendous flexibility in imaging.
In some situations, it is not possible to generate enough image contrast to adequately show the anatomy or pathology of interest by adjusting the pulse sequence – in this case, a contrast agent would be administered.
Echo-planar imaging
In brain scanning, or in cases where images are needed rapidly, echo-planar imaging (EPI) is used. In each case, each RF excitation is followed by a train of gradient echoes with different spatial coding.
Benefits:
- Reduced imaging time
- Decreased motion artifact
- Ability to image rapid physiologic processes of the human body
Drawbacks:
- Sensitive to susceptibility effects
- Sensitive to main magnetic field inhomogeneity
- Long gradient echo train causes greater T2* weighting
- Requires high-performance gradients
MRI Sequences
Spin echo sequences
T1 weighted image (T1)
This technique measures the spin-lattice relaxation by using a short repetition time (TR) and echo time (TE).
Main significance:
- Lower signal for more water content (highlights tumors, inflammation, infection, hemorrhage etc.)
- High signal for fat
- High signal for paramagnetic substances such as MRI contrasts.
T2 weighted image (T2)
This technique measures the spin-spin relaxation by using longer TR and TE times.
Main significance:
- Higher signal for more water content
- Low signal for fat
- Low signal for paramagnetic substances
Both T1 and T2 are used as standard foundations and comparisons for other sequences.
Inversion recovery sequences
Short tau inversion recovery (STIR)
This technique suppresses fat by setting an inversion time where the signal of fat is zero.
Main significance:
- Gives high signal for edema, such as in more severe stress fractures.
Fluid attenuated inversion recovery (FLAIR)
This technique suppresses fluid by setting an inversion time that nulls fluids. By choosing a careful inversion time (TI), the signal from any particular tissue can be nulled. The TI depends on the tissue from the formula: TI = ln(2)*T1.
Main significance:
- It can be used in brain imaging to suppress cerebrospinal fluid effects on the image
- Gives high signal in cases such as multiple sclerosis plaques, subarachnoid haemorrhages, and meningitis.
Double inversion recovery (DIR)
This technique simultaneously suppresses cerebrospinal fluid and white matter by two inversion times.
Main significance:
- Gives high signal of multiple sclerosis plaques.
Gradient echo sequences
Steady-state free precession imaging (SSFP)
This technique maintains a steady residual transverse magnetisation over successive cycles. States of SSFP is a kind of steady states of magnetisation achieved by a series of RF irradiation and natural relaxation behaviors of spins. The influencing factors include, the flip angles of RF pulses, repetition time (TR) of pulse repeats, and the relaxation time constants (T1 & T2).
Main significance:
- Creations of cardiac MRI videos
Commercial names for this sequence include FLASH: fast imaging using low angle shot (Siemens), SPGR (GE), and T1 FFE: T1 fast field echo (Phillips)
Diffusion weighted imaging (DWI)
DWI uses specific MRI sequences as well as a software that generates images from the resulting data, that uses the diffusion of water molecules to generate contrast in MR images.
Conventional (DWI)
This technique measure the Brownian motion of water molecules.
Main significance:
- Produces high signal within cerebral infarction (an area of tissue in the brain resulting from a blockage/narrowing in the arteries).
Apparent diffusion coefficient imaging (ADC)
Reduces T2 weighting by taking multiple conventional DWI images with different DWI weighting, and the change corresponds to diffusion.
Main significance:
- Gives low signal minutes after cerebral infarction
Diffusion tensor imaging (DTI)
Produces tractography (3D model to visualise neural tracts), by an overall greater Brownian motion of water molecules in the directions of the nerve fibers.
Main significance:
- Evaluates white matter deformation by tumors
Perfusion-weighted imaging (PWI)
PWI sequence postprocesses data to obtain perfusion maps with different parameters, such as BV (blood volume), BF (blood flow), MTT (mean transit time) and TTP (time to peak).
Main significance of PWI:
- In cerebral infarction, the infarcted core and the penumbra have decreased perfusion (as show in picture).
Dynamic susceptibility (DSC)
Gadolinium contrast in injected, and rapid repeated imaging (generally gradient-echo echo-planar T2 weighted) quantifies susceptibility-induced signal loss.
Dynamic contrast enhance (DCE)
Measured the shortening of the spin-lattice relaxation (T1) induced by a gadolinium contrast bolus.
Arterial Spin labelling (ASL)
Magnetic labeling of arterial blood below the imaging slab, which subsequently enters the region of interest. It does not need gadolinium contrast.
Functional MRI (fMRI)
Blood-oxygen-level dependent imaging (BOLD)
This techniques recognises the changes in oxygen saturation-dependent magnetism of hemoglobin reflects tissue activity.
Main significance:
- Localises highly active brain areas before surgery.
Magnetic resonance angiography (MRA) and venography
Time-of-flight (TOF)
Blood entering the imaged area is not yet magnetically saturated, giving it a much higher signal when using short echo time and flow compensation.
Main significance:
- Detects aneurysms, stenosis or dissections.
Phase-contrast MRA (PC-MRA)
PC-MRA determines flow velocitites. Two gradients with equal magnitude but opposite direction are used to encode a phase shift, which is proportional to the velocity of spins.
Main significance:
- Detects aneurysms, stenosis or dissections (as pictured).
Susceptibility weighted imaging (SWI)
This sequence is sensitive for blood and calcium, by a fully flow compensated, long echo, gradient recalled echo (GRE) pulse sequence to exploit magnetic susceptibility difference between tissues.
Main significance:
- Detects small amounts of hemorrhage or calcium.
Safety of MRI applications
Strength of magnetic field
A magnetic field of 1.5T is about 30,000 times the strength of the Earth’s magnetic field. It is so strong that it can pull stretchers, beds and oxygen cylinders across the room – this can create flying projectiles – deaths have occurred from traumas as a results of this!
The strong field can also effect devices such as pacemakers; patients who have a pacemaker are not allowed to undergo an MRI scan. Intracranial aneurysm clips are ferromagnetic, and as a result experience a torque. Several cases of a fatal hemorrhage have been reported when a patient with an clip has entered a magnetic field.
Gradient fields
Changing the magnetic fields induces electrical currents in conductors – patient with metal within their body have the potential for electrical currents to be induced in the metal, with subsequent heating. This may occur to metal foreign bodies or some surgical implants.
Quenching
Quenching is rapid expulsion of the liquid cryogen used to maintain the MR magnet in a superconducting state.
In the result of the emergency stop button being pressed or there is an equipment fault, the liquid helium boils off rapidly and a loud bang is given off. This gas should be safely expelled via a dedicated venting system. If somewhat the system fails and the gas is emitted into the room, there is a risk of asphyxiation and frost bite.