# Relaxation (NMR)

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

For spin=½ nuclei (such as 1H), the polarization due to spins oriented with the field N relative to the spins oriented against the field N+ is given by the Boltzmann distribution:

${\displaystyle {\frac {N_{+}}{N_{-}}}=e^{-{\frac {\Delta E}{kT}}}}$

where ΔE is the energy level difference between the two populations of spins, k is the Boltzmann constant, and T is the sample temperature. At room temperature, the number of spins in the lower energy level, N−, slightly outnumbers the number in the upper level, N+. The energy gap between the spin-up and spin-down states in NMR is minute by atomic emission standards at magnetic fields conventionally used in MRI and NMR spectroscopy. Energy emission in NMR must be induced through a direct interaction of a nucleus with its external environment rather than by spontaneous emission. This interaction may be through the electrical or magnetic fields generated by other nuclei, electrons, or molecules. Spontaneous emission of energy is a radiative process involving the release of a photon and typified by phenomena such as fluorescence and phosphorescence. As stated by Abragam, the probability per unit time of the nuclear spin-1/2 transition from the + into the - state through spontaneous emission of a photon is a negligible phenomenon.[1][2] Rather, the return to equilibrium is a much slower thermal process induced by the fluctuating local magnetic fields due to molecular or electron (free radical) rotational motions that return the excess energy in the form of heat to the surroundings.

## T1 and T2

The decay of RF-induced NMR spin polarization is characterized in terms of two separate processes, each with their own time constants. One process, called T1, is responsible for the loss of resonance intensity following pulse excitation. The other process, called T2, characterizes the width or broadness of resonances. Stated more formally, T1 is the time constant for the physical processes responsible for the relaxation of the components of the nuclear spin magnetization vector M parallel to the external magnetic field, B0 (which is conventionally designated as the z-axis). T2 relaxation affects the coherent components of M perpendicular to B0. In conventional NMR spectroscopy, T1 limits the pulse repetition rate and affects the overall time an NMR spectrum can be acquired. Values of T1 range from milliseconds to several seconds, depending on the size of the molecule, the viscosity of the solution, the temperature of the sample, and the possible presence of paramagnetic species (e.g., O2 or metal ions).

### T1

The longitudinal (or spin-lattice) relaxation time T1 is the decay constant for the recovery of the z component of the nuclear spin magnetization, Mz, towards its thermal equilibrium value, ${\displaystyle M_{z,\mathrm {eq} }}$. In general,

${\displaystyle M_{z}(t)=M_{z,\mathrm {eq} }-[M_{z,\mathrm {eq} }-M_{z}(0)]e^{-t/T_{1}}}$

In specific cases:

• If M has been tilted into the xy plane, then ${\displaystyle M_{z}(0)=0}$ and the recovery is simply
${\displaystyle M_{z}(t)=M_{z,\mathrm {eq} }\left(1-e^{-t/T_{1}}\right)}$

i.e. the magnetization recovers to 63% of its equilibrium value after one time constant T1.

• In the inversion recovery experiment, commonly used to measure T1 values, the initial magnetization is inverted, ${\displaystyle M_{z}(0)=-M_{z,\mathrm {eq} }}$, and so the recovery follows
${\displaystyle M_{z}(t)=M_{z,\mathrm {eq} }\left(1-2e^{-t/T_{1}}\right)}$

T1 relaxation involves redistributing the populations of the nuclear spin states in order to reach the thermal equilibrium distribution. By definition, this is not energy conserving. Moreover, spontaneous emission is negligibly slow at NMR frequencies. Hence truly isolated nuclear spins would show negligible rates of T1 relaxation. However, a variety of relaxation mechanisms allow nuclear spins to exchange energy with their surroundings, the lattice, allowing the spin populations to equilibrate. The fact that T1 relaxation involves an interaction with the surroundings is the origin of the alternative description, spin-lattice relaxation.

Note that the rates of T1 relaxation (i.e., 1/T1) are generally strongly dependent on the NMR frequency and so vary considerably with magnetic field strength B. Small amounts of paramagnetic substances in a sample speed up relaxation very much. By degassing, and thereby removing dissolved oxygen, the T1/T2 of liquid samples easily go up to an order of ten seconds.

#### Spin saturation transfer

Especially for molecules exhibiting slowly relaxing (T1) signals, the technique spin saturation transfer (SST) provides information on chemical exchange reactions. The method is widely applicable to fluxional molecules. This magnetization transfer technique provides rates, provided that they exceed 1/T1.[3]

### T2

Visual representation of the spin of a proton under a constant magnetic field B0. Visualization of the ${\displaystyle T_{1}}$ and ${\displaystyle T_{2}}$ relaxation times.

The transverse (or spin-spin) relaxation time T2 is the decay constant for the component of M perpendicular to B0, designated Mxy, MT, or ${\displaystyle M_{\perp }}$. For instance, initial xy magnetization at time zero will decay to zero (i.e. equilibrium) as follows:

${\displaystyle M_{xy}(t)=M_{xy}(0)e^{-t/T_{2}}\,}$

i.e. the transverse magnetization vector drops to 37% of its original magnitude after one time constant T2.

T2 relaxation is a complex phenomenon, but at its most fundamental level, it corresponds to a decoherence of the transverse nuclear spin magnetization. Random fluctuations of the local magnetic field lead to random variations in the instantaneous NMR precession frequency of different spins. As a result, the initial phase coherence of the nuclear spins is lost, until eventually the phases are disordered and there is no net xy magnetization. Because T2 relaxation involves only the phases of other nuclear spins it is often called "spin-spin" relaxation.

Spin echo pulse sequence and magnetization decay animation.

T2 values are generally much less dependent on field strength, B, than T1 values.

Hahn echo decay experiment can be used to measure the T2 time, as shown in the animation below. The size of the echo is recorded for different spacings of the two applied pulses. This reveals the decoherence which is not refocused by the 180° pulse. In simple cases, an exponential decay is measured which is described by the ${\displaystyle T_{2}}$ time.

### T2* and magnetic field inhomogeneity

In an idealized system, all nuclei in a given chemical environment, in a magnetic field, precess with the same frequency. However, in real systems, there are minor differences in chemical environment which can lead to a distribution of resonance frequencies around the ideal. Over time, this distribution can lead to a dispersion of the tight distribution of magnetic spin vectors, and loss of signal (Free Induction Decay). In fact, for most magnetic resonance experiments, this "relaxation" dominates. This results in dephasing.

However, decoherence because of magnetic field inhomogeneity is not a true "relaxation" process; it is not random, but dependent on the location of the molecule in the magnet. For molecules that aren't moving, the deviation from ideal relaxation is consistent over time, and the signal can be recovered by performing a spin echo experiment.

The corresponding transverse relaxation time constant is thus T2*, which is usually much smaller than T2. The relation between them is:

${\displaystyle {\frac {1}{T_{2}^{*}}}={\frac {1}{T_{2}}}+{\frac {1}{T_{inhom}}}={\frac {1}{T_{2}}}+\gamma \Delta B_{0}}$

where γ represents gyromagnetic ratio, and ΔB0 the difference in strength of the locally varying field.[4][5]

Unlike T2, T2* is influenced by magnetic field gradient irregularities. The T2* relaxation time is always shorter than the T2 relaxation time and is typically milliseconds for water samples in imaging magnets.

### Is T1 always longer than T2?

In NMR systems, the following relation holds absolute true[6] ${\displaystyle T_{2}\leq 2T_{1}}$. In most situations (but not in principle) ${\displaystyle T_{1}}$ is greater than ${\displaystyle T_{2}}$. The cases in which ${\displaystyle 2T_{1}>T_{2}>T_{1}}$ are rare, but not impossible.[7]

## Bloch equations

Bloch equations are used to calculate the nuclear magnetization M = (Mx, My, Mz) as a function of time when relaxation times T1 and T2 are present. Bloch equations are phenomenological equations that were introduced by Felix Bloch in 1946.[8]

${\displaystyle {\frac {\partial M_{x}(t)}{\partial t}}=\gamma (\mathbf {M} (t)\times \mathbf {B} (t))_{x}-{\frac {M_{x}(t)}{T_{2}}}}$
${\displaystyle {\frac {\partial M_{y}(t)}{\partial t}}=\gamma (\mathbf {M} (t)\times \mathbf {B} (t))_{y}-{\frac {M_{y}(t)}{T_{2}}}}$
${\displaystyle {\frac {\partial M_{z}(t)}{\partial t}}=\gamma (\mathbf {M} (t)\times \mathbf {B} (t))_{z}-{\frac {M_{z}(t)-M_{0}}{T_{1}}}}$

Where ${\displaystyle \times }$ is the cross-product, γ is the gyromagnetic ratio and B(t) = (Bx(t), By(t), B0 + Bz(t)) is the magnetic flux density experienced by the nuclei. The z component of the magnetic flux density B is typically composed of two terms: one, B0, is constant in time, the other one, Bz(t), is time dependent. It is present in magnetic resonance imaging and helps with the spatial decoding of the NMR signal.

The equation listed above in the section on T1 and T2 relaxation are those in the Bloch equations.

## Solomon equations

Solomon equations are used to calculate the transfer of magnetization as a result of relaxation in a dipolar system. They can be employed to explain the nuclear Overhauser effect, which is an important tool in determining molecular structure.

## Common relaxation time constants in human tissues

Following is a table of the approximate values of the two relaxation time constants for hydrogen nuclear spins in nonpathological human tissues.

At a main field of 1.5 T
Tissue type Approximate T1 value in ms Approximate T2 value in ms
Adipose tissues 240-250 60-80
Whole blood (deoxygenated) 1350 50
Whole blood (oxygenated) 1350 200
Cerebrospinal fluid (similar to pure water) 4200 - 4500 2100-2300
Gray matter of cerebrum 920 100
White matter of cerebrum 780 90
Liver 490 40
Kidneys 650 60-75
Muscles 860-900 50

Following is a table of the approximate values of the two relaxation time constants for chemicals that commonly show up in human brain magnetic resonance spectroscopy (MRS) studies, physiologically or pathologically.

At a main field of 1.5 T
Signals of chemical groups Relative resonance frequency Approximate T1 value (ms) Approximate T2 value (ms)
Creatine (Cr) and Phosphocreatine (PCr)[9] 3.0 ppm gray matter: 1150-1340,
white matter: 1050-1360
gray matter: 198-207,
white matter: 194-218
N-Acetyl group (NA),
mainly from N-acetylaspartate (NAA)[9]
2.0 ppm gray matter: 1170-1370,
white matter: 1220-1410
gray matter: 388-426,
white matter: 436-519
—CH3 group of
Lactate[10]
1.33 ppm
(doublet: 1.27 & 1.39 ppm)
(To be listed) 1040

## Relaxation in the rotating frame, T1ρ

The discussion above describes relaxation of nuclear magnetization in the presence of a constant magnetic field B0. This is called relaxation in the laboratory frame. Another technique, called relaxation in the rotating frame, is the relaxation of nuclear magnetization in the presence of the field B0 together with a time-dependent magnetic field B1. The field B1 rotates in the plane perpendicular to B0 at the Larmor frequency of the nuclei in the B0. The magnitude of B1 is typically much smaller than the magnitude of B0. Under these circumstances the relaxation of the magnetization is similar to laboratory frame relaxation in a field B1. The decay constant for the recovery of the magnetization component along B1 is called the spin-lattice relaxation time in the rotating frame and is denoted T. Relaxation in the rotating frame is useful because it provides information on slow motions of nuclei.

## Microscopic mechanisms

Relaxation of nuclear spins requires a microscopic mechanism for a nucleus to change orientation with respect to the applied magnetic field and/or interchange energy with the surroundings (called the lattice). The most common mechanism is the magnetic dipole-dipole interaction between the magnetic moment of a nucleus and the magnetic moment of another nucleus or other entity (electron, atom, ion, molecule). This interaction depends on the distance between the pair of dipoles (spins) but also on their orientation relative to the external magnetic field. Several other relaxation mechanisms also exist. The chemical shift anisotropy (CSA) relaxation mechanism arises whenever the electronic environment around the nucleus is non spherical, the magnitude of the electronic shielding of the nucleus will then be dependent on the molecular orientation relative to the (fixed) external magnetic field. The spin rotation (SR) relaxation mechanism arises from an interaction between the nuclear spin and a coupling to the overall molecular rotational angular momentum. Nuclei with spin I ≥ 1 will have not only a nuclear dipole but a quadrupole. The nuclear quadrupole has an interaction with the electric field gradient at the nucleus which is again orientation dependent as with the other mechanisms described above, leading to the so-called quadrupolar relaxation mechanism.

Molecular reorientation or tumbling can then modulate these orientation-dependent spin interaction energies. According to quantum mechanics, time-dependent interaction energies cause transitions between the nuclear spin states which result in nuclear spin relaxation. The application of time-dependent perturbation theory in quantum mechanics shows that the relaxation rates (and times) depend on spectral density functions that are the Fourier transforms of the autocorrelation function of the fluctuating magnetic dipole interactions.[11] The form of the spectral density functions depend on the physical system, but a simple approximation called the BPP theory is widely used.

Another relaxation mechanism is the electrostatic interaction between a nucleus with an electric quadrupole moment and the electric field gradient that exists at the nuclear site due to surrounding charges. Thermal motion of a nucleus can result in fluctuating electrostatic interaction energies. These fluctuations produce transitions between the nuclear spin states in a similar manner to the magnetic dipole-dipole interaction.

## BPP theory

In 1948, Nicolaas Bloembergen, Edward Mills Purcell, and Robert Pound proposed the so-called Bloembergen-Purcell-Pound theory (BPP theory) to explain the relaxation constant of a pure substance in correspondence with its state, taking into account the effect of tumbling motion of molecules on the local magnetic field disturbance.[12] The theory agrees well with experiments on pure substances, but not for complicated environments such as the human body.

This theory makes the assumption that the autocorrelation function of the microscopic fluctuations causing the relaxation is proportional to ${\displaystyle e^{-t/\tau _{c}}}$, where ${\displaystyle \tau _{c}}$ is called the correlation time. From this theory, one can get T1 > T2 for magnetic dipolar relaxation:

${\displaystyle {\frac {1}{T_{1}}}=K\left[{\frac {\tau _{c}}{1+\omega _{0}^{2}\tau _{c}^{2}}}+{\frac {4\tau _{c}}{1+4\omega _{0}^{2}\tau _{c}^{2}}}\right]}$
${\displaystyle {\frac {1}{T_{2}}}={\frac {K}{2}}\left[3\tau _{c}+{\frac {5\tau _{c}}{1+\omega _{0}^{2}\tau _{c}^{2}}}+{\frac {2\tau _{c}}{1+4\omega _{0}^{2}\tau _{c}^{2}}}\right]}$,

where ${\displaystyle \omega _{0}}$ is the Larmor frequency in correspondence with the strength of the main magnetic field ${\displaystyle B_{0}}$. ${\displaystyle \tau _{c}}$ is the correlation time of the molecular tumbling motion. ${\displaystyle K={\frac {3\mu _{0}^{2}}{160\pi ^{2}}}{\frac {\hbar ^{2}\gamma ^{4}}{r^{6}}}}$ is defined for spin-1/2 nuclei and is a constant with ${\displaystyle \mu _{0}}$ being the magnetic permeability of free space of the ${\displaystyle \hbar ={\frac {h}{2\pi }}}$ the reduced Planck constant, γ the gyromagnetic ratio of such species of nuclei, and r the distance between the two nuclei carrying magnetic dipole moment.

Taking for example the H2O molecules in liquid phase without the contamination of oxygen-17, the value of K is 1.02×1010 s−2 and the correlation time ${\displaystyle \tau _{c}}$ is on the order of picoseconds = ${\displaystyle 10^{-12}}$ s, while hydrogen nuclei 1H (protons) at 1.5 Tesla precess at a Larmor frequency of approximately 64 MHz (Simplified. BPP theory uses angular frequency indeed). We can then estimate using τc = 5×10−12 s:

${\displaystyle \omega _{0}\tau _{c}=3.2\times 10^{-5}}$(dimensionless)
${\displaystyle T_{1}=\left(1.02\times 10^{10}\left[{\frac {5\times 10^{-12}}{1+(3.2\times 10^{-5})^{2}}}+{\frac {4\cdot 5\times 10^{-12}}{1+4\cdot (3.2\times 10^{-5})^{2}}}\right]\right)^{-1}}$= 3.92 s
${\displaystyle T_{2}=\left({\frac {1.02\times 10^{10}}{2}}\left[3\cdot 5\times 10^{-12}+{\frac {5\cdot 5\times 10^{-12}}{1+\left(3.2\times 10^{-5}\right)^{2}}}+{\frac {2\cdot 5\times 10^{-12}}{1+4\cdot (3.2\times 10^{-5})^{2}}}\right]\right)^{-1}}$= 3.92 s,

which is close to the experimental value, 3.6 s. Meanwhile, we can see that at this extreme case, T1 equals T2. As follows from the BPP theory, measuring the T1 times leads to internuclear distances r. One of the examples is accurate determinations of the metal – hydride (M-H) bond lengths in solutions by measurements of 1H selective and non-selective T1 times in variable-temperature relaxation experiments via the equation:[13][14]

${\displaystyle r(M-H)=C\left({\frac {(1.4k+4.47)T_{1min}}{\nu }}\right)^{1/6}}$
${\displaystyle k=(f-1)/(0.5-f/3)}$, with ${\displaystyle f=T_{1s}/T_{1}}$
${\displaystyle C=10^{7}\left({\frac {{\gamma }_{H}^{2}{\gamma }_{M}^{2}\hbar ^{2}I_{M}(I_{M}+1)}{15}}\right)^{1/6}}$

where r, frequency and T1 are measured in Å, MHz and s, respectively, and IM is the spin of M.

## References

1. ^ Abragam, A. (1961). "VII Thermal Relaxation in Liquids and Gases". Principles of Nuclear Magnetism. Oxford University Press. p. 264. ISBN 019852014X.
2. ^ Hoult, D.I.; Bahkar, B. (1998). "NMR Signal Reception: Virtual Photons and Coherent Spontaneous Emission". Concepts in Magnetic Resonance. 9 (5): 277–297.
3. ^ Jarek, R. L., Flesher, R. J., Shin, S. K., "Kinetics of Internal Rotation of N,N-Dimethylacetamide: A Spin-Saturation Transfer Experiment", Journal of Chemical Education 1997, volume 74, page 978. doi:10.1021/ed074p978.
4. ^ Chavhan, Govind B; Babyn, Paul S; Thomas, Bejoy; Shroff, Manohar M; Haacke, E. Mark (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.
5. ^ "T2* vs T2 relaxation time". Questions and Answers in MRI. Retrieved 2018-08-13.
6. ^ Malcolm H. Levitt: Spin Dynamics: Basics of Nuclear Magnetic Resonance, 2nd edition, John Wiley & Sons, New York 2008, ISBN 0-470-51117-6, Section 11.9.2
7. ^ Traficante, Daniel D. (1991). "Relaxation. Can T2, be longer than T1?". Concepts in Magnetic Resonance. 3 (3): 171–177. doi:10.1002/cmr.1820030305.
8. ^ F Bloch, Nuclear Induction, Physical Review 70, 460-473 (1946)
9. ^ a b Chemicals of brain relaxation time at 1.5T. Kreis R, Ernst T, and Ross BD "Absolute Quantification of Water and Metabolites in the Human Brain. II. Metabolite Concentrations" Journal of Magnetic Resonance, Series B 102 (1993): 9-19
10. ^ Lactate relaxation time at 1.5 T. Isobe T, Matsumura A, Anno I, Kawamura H, Muraishi H, Umeda T, Nose T. "Effect of J coupling and T2 Relaxation in Assessing of Methyl Lactate Signal using PRESS Sequence MR Spectroscopy." Igaku Butsuri (2005) v25. 2:68-74.
11. ^ A. Abragam "Principles of Nuclear Magnetism" (Oxford University Press, 1961)
12. ^ Bloembergen, E.M. Purcell, R.V. Pound "Relaxation Effects in Nuclear Magnetic Resonance Absorption" Physical Review (1948) v73. 7:679-746
13. ^ Dmitry G. Gusev, Daniel Nietlispach, Alexey B. Vymenits, Vladimir I. Bakhmutov, Heinz Berke Synthesis and NMR T1 relaxation study of rhenium and manganese hydride complexes
14. ^ D. G. Gusev, A. B. Vymenits, V. I. Bakhmutov Short spin-lattice relaxation times of hydride ligands. Proton-metal dipole-dipole interactions Inorg. Chem., 1991, 30 (16), p. 3116. DOI: 10.1021/ic00016a003Inorg. Chem., 1993, 32 (15), p. 3270. doi:10.1021/ic00067a013