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A bipolar gradient is a magnetic field gradient waveform with lobes of opposite sign. In nuclear magnetic resonance, such waveforms can control sensitivity to position and motion. Opposite signs alone do not guarantee equal signed areas, and an applied waveform must be distinguished from its effective encoding waveform when refocusing pulses change phase evolution.

For an original counterexample, apply $+10mT/m$ for $1\mathrm{ms}$ and then $-10mT/m$ for $2\mathrm{ms}$. The gradient zeroth moment isThe waveform is bipolar but unbalanced.

If the two durations are instead equal to $\tau$, and the effective lobes are contiguous, $+G$ from time 0 to $\tau$ and $-G$ from $\tau$ to $2\tau$, then $m_0=0$ but the gradient first moment is $m_1=-G{\tau }^2$. Thus cancellation of stationary-position phase can coexist with sensitivity to constant velocity. The sign follows this stated ordering.

Bipolar pulses also appear outside flow imaging. A 1989 stimulated echo study addressed background gradients that distort diffusion measurements. Alternating pulses could cancel a cross term under specified conditions; tests used proton signals from homogeneous and granular samples.^[ref] This is a sequence-specific result, not a promise that every bipolar pair removes every imaging error.

John E. Tanner was a physical chemistry researcher whose work with Edward O. Stejskal established pulsed field gradient NMR as a method for measuring self-diffusion. He studied physical chemistry at Oberlin, Indiana and Wisconsin, and later worked at Idaho National Laboratory. His early NMR work received renewed recognition with an honorary fellowship in 2016.^[ref]

The appeal of pulsed field gradient NMR was practical as well as theoretical: strong magnetic field gradients could encode motion without remaining strong during excitation or detection. In a 2017 interview with Derek Jones, Tanner recalled choosing Stejskal's laboratory because it had a magnet and because he wanted to measure slow diffusion. He also described rebuilding the probe to deal with eddy currents generated by switching the magnetic field gradients.^[ref]

Tanner made restricted diffusion experimentally concrete. He described assembling 99 layers of mica with aluminium foil spacers, carefully removing wrinkles and burrs to obtain regular gaps. Such a controlled geometry lets an echo probe displacement between known barriers, rather than treating every loss of NMR signal as free diffusion with a smaller diffusion coefficient.^[ref]

His 1970 work used a stimulated echo to extend the observation interval when spin-lattice relaxation is slower than transverse relaxation. The interval can store the relevant pattern as longitudinal magnetization, rather than keeping it transverse throughout.^[ref] For an illustrative ideal comparison, take $T_1=1\mathrm{s}$, $T_2=0.1\mathrm{s}$ and storage time $T=0.5\mathrm{s}$. The storage-dependent nuclear spin relaxation factors are $e^{-T/T_1}\simeq 0.607$ and $e^{-T/T_2}\simeq 0.00674$. Even allowing the ideal three-pulse pathway's initial factor of $1/2$, the former factor is about 45 times larger. This compares only that storage contribution: pulse losses, the other transverse intervals and diffusion attenuation still matter.^[ref]

Pulsed field gradient NMR, or PFG NMR, uses timed magnetic field gradients to encode position in the phase of a nuclear magnetic resonance signal. An appropriately refocused pair of encoding episodes cancels the position-dependent phase for stationary spins. Motion between the episodes can prevent cancellation, making the echo sensitive to displacement.

For an original narrow-pulse derivation in one spatial direction, let each effective encoding pulse have gradient magnitude $g$ and short duration $\delta$, and write $q=\gamma g\delta$, where $\gamma$ is the angular gyromagnetic ratio. Neglect displacement during each pulse. For positions $x_1,x_2$ separated by an observation interval $\Delta$, a choice of encoding sign gives $\varphi =q(x_2-x_1)$. The normalized signal is the ensemble average of $e^{i\varphi }$.

For free diffusion with diffusion coefficient $D$, displacement has a zero-mean normal distribution of variance $2D\Delta$. Its characteristic function givesFor invented values $q=10^5{\mathrm{m}}^{-1}$, $D=10^{-9}{\mathrm{m}}^2{\mathrm{s}}^{-1}$ and $\Delta =0.1\mathrm{s}$, the attenuation is $e^{-1}\approx 0.368$. Finite pulse duration, restricted motion and other sequence details require their corresponding model rather than automatic use of this narrow-pulse result.

The 1965 experiment of E. O. Stejskal and J. E. Tanner combined a derivation for time-dependent gradients with experimental tests. Reducing gradients during radio-frequency pulses and echo detection relaxed practical limitations of a continuously strong gradient; the authors measured slow diffusion in dry glycerol.^[ref]

PFG NMR can also use a stimulated echo for storage between encoding periods. Distinguishing motion-induced attenuation from other signal losses is part of the measurement, not a consequence of the method's name alone.

R. M. Cotts is a credited coauthor of Pulsed field gradient stimulated echo methods for improved NMR diffusion measurements in heterogeneous systems by R. M. Cotts and others, published in 1989. The joint work develops stimulated echo sequences for measuring the translational diffusion of resonant atomic nuclei in materials whose internal magnetic environment is not uniform.^[ref]

Pulsed field gradient NMR relates the attenuation of a stimulated echo to motion. In heterogeneous materials, components with different magnetic susceptibilities can produce background magnetic field gradients, which add attenuation and can bias the inferred diffusion coefficient. The paper describes three modified sequences that reduce these effects; under the stated conditions, bipolar gradient pulses cancel a problematic cross term. Two sequences were tested using proton signals in both a homogeneous liquid and a heterogeneous granular solid.^[ref]

The experimental comparison makes a useful measurement principle concrete: an apparatus can respond to both molecular motion and an unwanted background field variation. A sequence designed to separate these contributions improves the interpretation of a diffusion coefficient measurement.

A stimulated echo is a delayed nuclear magnetic resonance signal produced by a sequence that stores part of a dephased magnetization pattern along the static magnetic field and later converts it back into detectable transverse magnetization. In a common ideal sequence, three $90^{\circ }$ pulses are applied at times $0$, $\tau$ and $\tau +T_{mathrmm}$. The selected stimulated echo appears a further $\tau$ after the third pulse, at $2\tau +T_{mathrmm}$.^[ref]

The first interval lets spins with different Larmor frequencies accumulate different phases. The second pulse converts part of that frequency-dependent pattern into longitudinal magnetization. During the storage interval $T_{mathrmm}$ this component does not precess as transverse magnetization does. The third pulse returns part of the pattern to the transverse plane, where the appropriate contribution rephases. Storage retains a frequency-dependent population pattern, not a continuously rotating transverse vector.^[ref]

For an original ideal calculation, hold $\tau$ fixed and neglect diffusion, pulse errors and exchange. If $T_1$ is the spin-lattice relaxation time, the selected echo contribution obeysA storage interval $T_{mathrmm}=T_1\ln 2$ therefore halves that contribution. The two transverse intervals still incur transverse relaxation; longitudinal storage does not undo every source of signal loss.

This distinction is useful for diffusion measurements when a longer observation interval is wanted without keeping the relevant pattern transverse throughout. A 1989 experiment used pulsed-gradient stimulated echo sequences to reduce particular background-gradient effects in heterogeneous samples. It tested specified pulse arrangements, rather than establishing that every stimulated echo removes every gradient error.^[ref]