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MR artefacts

Motion artefacts

Patient motion

  • e.g. patient moving during scan, cardiac motion, breathing
  • Effect:
    • Ghosting: low intensity copies of the original image are shifted in the phase-encoding direction
  • Solutions:
    • Acquire more signals
    • Image with very fast single shot sequences
    • Change phase and frequency directions during the scan
    • ECG gating for cardiac motion artefacts
    • Breath-hold scanning for breathing artefacts
    • Navigator echo triggering for breathing artefacts: triggers scan only when boundary between lung and liver is within a certain acceptance window

Flow artefacts

(See “MR angiography” chapter for more information)

Distortion artefacts

  • Due to inhomogeneities in the magnetic field:
    • Local field inhomogeneity
    • Non-linearities in gradient magnetic fields
    • Boundaries between tissues of different magnetic susceptibilities

Local field inhomogeneity

The local field is most commonly distorted by metal present in the object which causes two types of artefacts: signal loss due to dephasing and distortion. An air-fluid interface can also cause similar inhomogeneities.

  • Dephasing of transverse magnetisation
    • Interferes with T2 transverse magnetisation so it dephases much quicker and doesn’t return an echo
  • Distortion
    • Local field inhomogeneities affect the magnetic field gradient and, therefore, the Larmor frequency
    • As location is encoded based on Larmor frequency this leads to protons in the area of the inhomogeneity being encoded in the incorrect position
Metal artefact

Non-linearities in magnetic field gradient

Non-linear gradient

The gradients used in spatial encoding are meant to be linear but often they roll off from the straight line towards the edges of the FOV. The distortion created occurs in both the frequency- and phase-encoding directions.


  • Correction often made automatically as the non-linearities are known and can be adjusted for.

Boundaries between tissues

The most common two substances in the human body are water and fat. Protons in water and fat will resonate at slightly different Larmor frequencies despite being in the same position in the magnetic field gradients. There are two artefacts that are produced by this property when protons from these two tissues are in close proximity: chemical-shift and fat/water cancellation.

Chemical shift

Chemical shift artefact

Protons in fat and water resonate at slightly different Larmor frequencies. This means that even when they exist in the same position they will be interpreted as being in slightly different positions in the frequency-encoding direction which uses the precessing frequency to encode position.

Fat/water cancellation

Fat cancellation

As protons from fat and water have different Larmor frequencies they will go in and out of phase over time. If a voxel contains both fat and water the signals from the two may cancel each other out if the TE of a certain length is used (2.24 ms at 1.5 T). This creates a signal loss with a black line between tissues that contain both fat and water.

This is used in liver MRI out-of-phase imaging as fatty infiltration results in cancelling of the signal helping with diagnosis.


  • Chemical shift is from boundaries between fat and water (i.e. macroscopic)
  • Fat/water cancellation nulls the signal from microscopic fat (i.e. fat and water present in the same voxel)
  • Fat saturation imaging cancels signal from macroscopic fat (i.e. fat and water present in different voxels)

Fat saturation artefact

Failure of fat saturation

Fat saturation imaging exploits the different Larmor frequencies of fat and water by applying a narrow RF pulse centred over the fat peak that nulls the signal. If the frequency of the fat peak is slightly different – most commonly due to anatomy with a rapidly changing contour (e.g. ankle and foot) or non-linearity of the magnetic field gradient at the periphery of the image as explained earlier – the RF pulse will not be positioned over the fat peak any more and will fail to null the signal.

Written by radiologists, for radiologists with plenty of easy-to-follow diagrams to explain complicated concepts. An excellent resource for radiology physics revision.

Radiofrequency artefacts

Improper coil selection

RF coil elements can be switched on and off depending on the FOV required.

  • RF coil in FOV switched off = loss of signal in this area
  • RF coil outside FOV switched on = artefacts such as ghosting from motion being aliased back onto the FOV

Spurious RF signals

RF signals arising from outside due to an inadequately shielded MRI room or inside from faulty equipment will contribute to the image. A band of noise will appear in the image in the phase-encoding direction depending upon the frequency/frequencies of the external RF signal.

Data collection artefacts

Inadequate FOV

Signal from structures that lie outside the FOV in the phase encoding direction will be aliased back onto the image (aka phase wrap).


  • Adequate FOV in phase-encoding direction
  • If small FOV required can use over-sampling

Spurious data

Any spurious data will be encoded into the k-space data as a wave which is encoded into the final image as a “herringbone” artefact with alternating light and dark bands.

Sources of spurious data:

  • Malfunctioning equipment in scanner room
  • Static build-up on clothing

Edge representation

Gibbs artefact
Gibbs artefact

Imaging an edge boundary can create a Gibbs or edge ringing artefact. The more data points that are acquired the better the boundary edges are represented. However, at the edges of the image the extra data points create superimposed waves which are encoded into the image. This is of particular importance in imaging the spine in which encoding the edge boundary between the spinal cord and CSF can create artefactual lesions within the cord.

Sequence specific artefacts

Echo-planar imaging (EPI)

Local magnetic field inhomogeneity distortion

In EPI the whole of the k-space is acquired in one RF excitation resulting in very rapid imaging. The horizontal acquisition is very quick but the vertical acquisition is slower. This difference leads to distortion, especially where there are small local magnetic field inhomogeneities such as around the nasal cavity or the orbits.


  • Parallel or multi-shot EPI: k-space acquired in more than one shot but each shot is faster

N/2 ghosts

A low intensity copy of the image which is shifted by half the FOV in the phase encoding direction can occur which is due to misalignment of echoes as the k-space is acquired back and forth.


  • Careful gradient calibrations

Fast spin echo (FSE)

Multiple lines of the k-space are acquired after a signal RF excitation as explained in Spin echo sequences – Detailed. The number of lines acquired per TR (or echo-train length, ETL) can be very long to the point that the whole of k-space is acquired in a single TR (single-shot FSE). However, over time there will be T2 relaxation that will cause blurring in the image in the phase encoding direction.

Steady state free precession (SSFP)

In SSFP imaging if there are local magnetic field inhomogeneities this can produce a banding pattern on the image with signal void and stimulated-echoes that constructively and destructively interfere.

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