Gradient echo

Last updated November 29, 2023

Gradient echo is a magnetic resonance imaging (MRI) sequence that has wide variety of applications, from magnetic resonance angiography to perfusion MRI and diffusion MRI. Rapid imaging acquisition allows it to be applied to 2D and 3D MRI imaging. Gradient echo uses magnetic gradients to generate a signal, instead of using 180 degrees radiofrequency pulse like spin echo; thus leading to faster image acquisition time.^[1]

Mechanism

Unlike spin-echo sequence, a gradient echo sequence does not use a 180 degrees RF pulse to make the spins of particles coherent. Instead, the gradient echo uses magnetic gradients to manipulate the spins, allowing the spins to dephase and rephase when required. After an excitation pulse (usually less than 90 degrees), the spins are dephased after a period of time (due to free induction decay) and also by applying a reversed magnetic gradient to decay the spins.^[2] No signal is produced because the spins are not coherent. When the spins are rephased via a magnetic gradient, they become coherent, and thus signal (or "echo") is generated to form images. Unlike spin echo, gradient echo does not need to wait for transverse magnetisation to decay completely before initiating another sequence, thus it requires very short repetition times (TR), and therefore to acquire images in a short time.^[2]

After echo is formed, some transverse magnetisations remains because of short TR.^[2] Manipulating gradients during this time will produce images with different contrast. There are three main methods of manipulating contrast at this stage, namely steady-state free-precession (SSFP) that does not spoil the remaining transverse magnetisation, but attempts to recover them in subsequent RF pulses (thus producing T2-weighted images); the sequence with spoiler gradient that averages the transverse magnetisations in subsequent RF pulses by rotating residual transverse magnetisation into longitudinal plane and longitudinal magnetisation into transverse planes (thus producing mixed T1 and T2-weighted images), and RF spoiler that vary the phases of RF pulse to eliminates the transverse magnetisation, thus producing pure T1-weighted images.^[1]^[2]

Gradient echo uses a flip angle smaller than 90 degrees, thus longitudinal magnetisation is not eliminated while flipping the spins. The larger the flip angle, the higher the T1 weighing of the tissue because more longitudinal magnetisation most recover to produce a difference in signals between the tissues.^[2]

Steady-state free precession

Steady-state free precession imaging (SSFP) or balanced SSFP is an MRI technique which uses short repetition times (TR) and low flip angles (about 10 degrees) to achieve steady state of longitudinal magnetizations as the magnetizations does not decay completely nor achieving full T1 relaxation.^[1] While spoiled gradient-echo sequences refer to a steady state of the longitudinal magnetization only, SSFP gradient-echo sequences include transverse coherences (magnetizations) from overlapping multi-order spin echoes and stimulated echoes. This is usually accomplished by refocusing the phase-encoding gradient in each repetition interval in order to keep the phase integral (or gradient moment) constant. Fully balanced SSFP MRI sequences achieve a phase of zero by refocusing all imaging gradients.

MP-RAGE (magnetization-prepared rapid acquisition with gradient echo) ^[3] improves images of multiple sclerosis cortical lesions.^[4]

Spoiling

At the end of the reading, the residual transverse magnetization can be terminated (through the application of suitable gradients and the excitation through pulses with a variable phase radiofrequency) or maintained.

In the first case there is a spoiled sequence, such as the fast low-angle shot MRI (FLASH MRI) sequence, while in the second case there are steady-state free precession imaging (SSFP) sequences.

In-phase and out-of-phase

In-phase (IP) and out-of-phase (OOP) sequences correspond to paired gradient echo sequences using the same repetition time (TR) but with two different echo times (TE).^[5] This can detect even microscopic amounts of fat, which has a drop in signal on OOP compared to IP. Among renal tumors that do not show macroscopic fat, such a signal drop is seen in 80% of the clear cell type of renal cell carcinoma as well as in minimal fat angiomyolipoma.^[6]

Effective T₂ (T₂* or "T2-star")

T₂*-weighted imaging can be created as a postexcitation refocused gradient echo sequence with small flip angle. The sequence of a GRE T₂*WI requires high uniformity of the magnetic field.^[7]

Commercial names of gradient echo sequences

Academic Classification	Spoiled gradient echo		Steady-State Free Precession (SSFP)		Balanced Steady-State Free Precession (bSSFP)
Academic Classification	Ordinary type	Turbo type (Magnetization preparation, extremely low angle shot, short TR)	FID-like	Echo-like	Balanced Steady-State Free Precession (bSSFP)
Siemens	FLASH Fast Imaging using Low Angle Shot	TurboFLASH TurboFLASH	FISP Fast Imaging with Steady-state Precession	PSIF Reversed FISP	TrueFISP TrueFISP
GE	SPGR Spoiled GRASS	FastSPGR FastSPGR	GRASS Gradiant Recall Acquisition using Steady States	SSFP Steady State Free Precession	FIESTA Fast Imaging Employing Steady-state Acquisition
Philips	T₁ FFE T₁-weighted Fast Field Echo	TFE Turbo Field Echo	FFE Fast Field Echo	T₂-FFE T₂-weighted Fast Field Echo	b-FFE Balanced Fast Field Echo

VIBE (volumetric interpolated breath-hold examination) is an MRI sequence that produces T1-weighted gradient echo images in three-dimensions (3D). Apart from lower fluid signal intensity than a typical T1-weighted image, other appearances of VIBE images is similar to a typical T1-weighted image. Since its acquisition is only 30 seconds, suitable for breath-holding, it is used in breast and abdominal imaging to obtain high-resolution images minimising respiratory movement artifacts. VIBE images have low contrast in soft tissues and cartilage but have high contrast between the bony cortex and bone marrow. Bony lesions such as callus and fibrous tissue can also be readily distinguished from surrounding cortical bone because high contrast between the bone lesions and the bony cortex.^[8]

Related Research Articles

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<span class="mw-page-title-main">Magnetic resonance angiography</span> Group of techniques based on magnetic resonance imaging (MRI) to image blood vessels.

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In MRI and NMR spectroscopy, an observable nuclear spin polarization (magnetization) is created by a homogeneous magnetic field. This field makes the magnetic dipole moments of the sample precess at the resonance (Larmor) frequency of the nuclei. At thermal equilibrium, nuclear spins precess randomly about the direction of the applied field. They become abruptly phase coherent when they are hit by radiofrequency (RF) pulses at the resonant frequency, created orthogonal to the field. The RF pulses cause the population of spin-states to be perturbed from their thermal equilibrium value. The generated transverse magnetization can then induce a signal in an RF coil that can be detected and amplified by an RF receiver. The return of the longitudinal component of the magnetization to its equilibrium value is termed spin-latticerelaxation while the loss of phase-coherence of the spins is termed spin-spin relaxation, which is manifest as an observed free induction decay (FID).

<span class="mw-page-title-main">Steady-state free precession imaging</span>

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In magnetic resonance, a spin echo or Hahn echo is the refocusing of spin magnetisation by a pulse of resonant electromagnetic radiation. Modern nuclear magnetic resonance (NMR) and magnetic resonance imaging (MRI) make use of this effect.

Fast low angle shot magnetic resonance imaging is a particular sequence of magnetic resonance imaging. It is a gradient echo sequence which combines a low-flip angle radio-frequency excitation of the nuclear magnetic resonance signal with a short repetition time. It is the generic form of steady-state free precession imaging.

In physics, the spin–spin relaxation is the mechanism by which $M xy$ , the transverse component of the magnetization vector, exponentially decays towards its equilibrium value in nuclear magnetic resonance (NMR) and magnetic resonance imaging (MRI). It is characterized by the spin–spin relaxation time, known as $T$ ₂, a time constant characterizing the signal decay. It is named in contrast to $T$ ₁, the spin–lattice relaxation time. It is the time it takes for the magnetic resonance signal to irreversibly decay to 37% (1/e) of its initial value after its generation by tipping the longitudinal magnetization towards the magnetic transverse plane. Hence the relation

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References

1 2 3 Hargreaves BA (December 2012). "Rapid gradient-echo imaging". Journal of Magnetic Resonance Imaging. 36 (6): 1300–1313. doi:10.1002/jmri.23742. PMC 3502662 . PMID 23097185.
1 2 3 4 5 Kim, Jane J.; Mukherjee, Pratik (2013). Static Anatomic Techniques. Elsevier. pp. 3–22. doi:10.1016/b978-1-4160-5009-4.50009-1. ISBN 978-1-4160-5009-4.
↑ Nelson F, Poonawalla A, Hou P, Wolinsky JS, Narayana PA (November 2008). "3D MPRAGE improves classification of cortical lesions in multiple sclerosis". Multiple Sclerosis. 14 (9): 1214–1219. doi:10.1177/1352458508094644. PMC 2650249 . PMID 18952832.
↑ Brant-Zawadzki M, Gillan GD, Nitz WR (March 1992). "MP RAGE: a three-dimensional, T1-weighted, gradient-echo sequence--initial experience in the brain". Radiology. 182 (3): 769–775. doi:10.1148/radiology.182.3.1535892. PMID 1535892.^{[ permanent dead link ]}
↑ Tatco V, Di Muzio B. "In-phase and out-of-phase sequences". Radiopaedia . Retrieved 2017-10-24.
↑ Reinhard R, van der Zon-Conijn M, Smithuis R. "Kidney - Solid masses". Radiology Assistant. Retrieved 2017-10-27.
↑ Chavhan GB, Babyn PS, Thomas B, Shroff MM, Haacke EM (2009). "Principles, techniques, and applications of T2*-based MR imaging and its special applications". Radiographics. 29 (5): 1433–1449. doi:10.1148/rg.295095034. PMC 2799958 . PMID 19755604.
↑ Koh E, Walton ER, Watson P (July 2018). "VIBE MRI: an alternative to CT in the imaging of sports-related osseous pathology?". The British Journal of Radiology. 91 (1088): 20170815. doi:10.1259/bjr.20170815. PMC 6209485 . PMID 29474097.

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[Hargreaves_BA_2012-1] 1 2 3 Hargreaves BA (December 2012). "Rapid gradient-echo imaging". Journal of Magnetic Resonance Imaging. 36 (6): 1300–1313. doi:10.1002/jmri.23742. PMC 3502662 . PMID 23097185.

[Kim_2013-2] 1 2 3 4 5 Kim, Jane J.; Mukherjee, Pratik (2013). Static Anatomic Techniques. Elsevier. pp. 3–22. doi:10.1016/b978-1-4160-5009-4.50009-1. ISBN 978-1-4160-5009-4.

[3] Nelson F, Poonawalla A, Hou P, Wolinsky JS, Narayana PA (November 2008). "3D MPRAGE improves classification of cortical lesions in multiple sclerosis". Multiple Sclerosis. 14 (9): 1214–1219. doi:10.1177/1352458508094644. PMC 2650249 . PMID 18952832.

[4] Brant-Zawadzki M, Gillan GD, Nitz WR (March 1992). "MP RAGE: a three-dimensional, T1-weighted, gradient-echo sequence--initial experience in the brain". Radiology. 182 (3): 769–775. doi:10.1148/radiology.182.3.1535892. PMID 1535892.^{[ permanent dead link ]}

[5] Tatco V, Di Muzio B. "In-phase and out-of-phase sequences". Radiopaedia . Retrieved 2017-10-24.

[ra-kidney-6] Reinhard R, van der Zon-Conijn M, Smithuis R. "Kidney - Solid masses". Radiology Assistant. Retrieved 2017-10-27.

[7] Chavhan GB, Babyn PS, Thomas B, Shroff MM, Haacke EM (2009). "Principles, techniques, and applications of T2*-based MR imaging and its special applications". Radiographics. 29 (5): 1433–1449. doi:10.1148/rg.295095034. PMC 2799958 . PMID 19755604.

[pmid29474097-8] Koh E, Walton ER, Watson P (July 2018). "VIBE MRI: an alternative to CT in the imaging of sports-related osseous pathology?". The British Journal of Radiology. 91 (1088): 20170815. doi:10.1259/bjr.20170815. PMC 6209485 . PMID 29474097.

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