I’m always searching for ways to illustrate concepts using “simple” analytical examples (I’ll let you decide whether or not this example is simple). Today, I present analytical examples of frequency and phase encoding during magnetic resonance imaging. Russ Hobbie and I discuss MRI in Chapter 18 of

*Intermediate Physics for Medicine and Biology*.

####
1. **Introduction **

Our goal is to understand how the measured MRI signal changes when magnetic field gradients are present. These gradients are essential for “encoding” information about the spatial distribution of spins in the frequency and phase of the signal. To simplify our discussion, we make several assumptions:
- The radio-frequency
*π*/2 and*π*pulses, used to rotate the spins into the*x*-*y*plane and then create an echo, are so brief that the spins rotate instantaneously compared to all other time scales. Similarly, any slice selection gradient*G*exists only during the radio-frequency pulses. We won’t include_{z}= dB_{z}/dz*G*in our drawings of pulse sequences._{z} -
We ignore relaxation, so the longitudinal and transverse time constants
*T*and_{1}*T*are infinite._{2} - Despite ignoring relaxation, the spins do dephase leading to a free induction decay with time constant
*T**. Dephasing is caused by a distribution of spin frequencies, corresponding to small-scale static heterogeneities of the magnetic field. We assume that the spin frequencies_{2}*ω*have the distribution*ω*_{o}is the Larmor frequency equal to*γB*_{o}, where*γ*is the gyromagnetic ratio and*B*_{o}is the main magnetic field. The time constant*τ*indicates the width of the frequency distribution. - The spins are distributed uniformly along the
*x*axis from -*Δx*to +*Δx*.

####
2. **Spin-Echo**

The spin-echo pulse sequence, with no gradients and no frequency or phase encoding, is similar to Fig. 18.24 in *IPMB*. Our pulse sequences consist of three functions of time. The radio-frequency (RF) pulses are shown on the first line; the time between the

*π*/2 and

*π*pulses is

*T*/2. The magnetic field gradient in the

_{E}*x*direction,

*G*=

_{x}*dB*, is indicated in the second line; for this first example

_{z}/dx*G*is zero. The recorded signal,

_{x}*M*, is in the third line.

_{x}Our goal is to calculate

*M*(

_{x}*t*). During the time between the two radio frequency pulses, we calculate the signal by integrating the precessing spins over

*x*and

*ω*

In this case the

*x*integral is trivial: the integrand does not depend on

*x*. We can solve the

*ω*integral analytically using the

*u*-substitution

*u*=

*τ*(

*ω*-

*ω*

_{o}), the cosine addition formula cos(

*A*+

*B*) = cos

*A*cos

*B*– sin

*A*sin

*B*, and the definite integral

The resulting free induction decay (FID) is

where

*τ*corresponds to

*T**. The exponential shape of the free induction decay arises from the particular form of our spin distribution. The wider the distribution of frequencies, the faster the decay.

_{2}The spins accumulate phase relative to those precessing at the Larmor frequency. Just before the

*π*pulse the extra phase is (

*ω*-

*ω*

_{o})

*T*/2. The

_{E}*π*pulse changes the sign of this phase, or in other words adds an additional phase -(

*ω*-

*ω*

_{o})

*T*. After the

_{E}*π*pulse the signal is

The

*x*integral is again trivial and the

*ω*integral produces an echo

which peaks at

*t*=

*T*and decays with time constant

_{E}*τ*.

####
3. **Phase Encoding**

Phase encoding adds a gradient field *G*of duration

_{x}*T*between the radio-frequency

*π*/2 and

*π*pulses. It shifts the phase of the spins by different amounts at different

*x*locations (thus, position information is encoded in the phase of the signal). This phase shift is then reversed by the

*π*pulse.

The trickiest part of calculating

*M*(

_{x}*t*) is keeping track of the phase shifts: (

*ω*-

*ω*

_{o})

*t*is the phase shift up to time

*t*because of the distribution of frequencies, -(

*ω*-

*ω*

_{o})

*T*arises because the spins are flipped by the

_{E}*π*pulse,

*γ*

*G*is caused by the phase-encoding gradient, and -2

_{x}xT*γ*

*G*is again from flipping by the

_{x}xT*π*pulse. During the echo the signal simplifies to

We can solve both the

*x*and

*ω*integrals by repeatedly using the cosine addition formula (it is tedious but not difficult; I leave the details to you), and find

The amplitude of the echo depends on the factor sin(

*γ*

*G*)/ (

_{x}ΔxT*γ*

*G*). For a

_{x}ΔxT*G*of zero this factor is one and the result is the same as for the spin-echo. If we repeat this pulse sequence with different values of

_{x}*G*and measure the amplitude of each echo, we can trace out the function sin(

_{x}*γ*

*G*)/ (

_{x}ΔxT*γ*

*G*), which is the Fourier transform of the spin distribution as a function of position.

_{x}ΔxT####
4. **Frequency Encoding**

To do frequency encoding, we add a readout gradient *G*that is on during the echo and lasts a time

_{x}*T*, like in Fig. 18.26 of

*IPMB*. In addition, we include a prepulse of opposite polarity and half duration just before the readout, to cancel any extra phase shift accumulated during the echo. (Russ and I discuss this extra lobe of the

*G*pulse when analyzing Fig. 18.29c, but we get its sign wrong).

_{x}The free induction decay and the phase reversal caused by the

*π*-pulse are the same as in the spin-echo example. Once

*G*begins the result differs. The frequency again depends on

_{x}*x*. The phase shifts are: (

*ω*-

*ω*

_{o})

*t*because of the distribution of frequencies, -(

*ω*-

*ω*

_{o})

*T*from the

_{E}*π*pulse, -

*γ*

*G*/2 caused by the prepulse, and

_{x}xT*γ*

*G*(

_{x}x*t*-(

*T*-

_{E}*T*/2)) during readout. The recorded signal simplifies to

The echo during the readout gradient is (you really must fill in the missing steps yourself to benefit from this post)

The envelope of the echo is the product of two terms, which are both functions of time: An exponential e

^{-|t-TE|/τ}that has the shape of the echo with no gradient, and a factor sin(

*γ*

*G*

_{x}*Δx*(

*t*-

*T*))/ (

_{E}*γ*

*G*

_{x}*Δx*(

*t*-

*T*)). The amplitude of the echo at

_{E}*t*=

*T*is the same as if

_{E}*G*were zero, but the shape of the echo has changed because of the time-dependent factor containing the gradient. The function containing the sine is the Fourier transform of the spin distribution. Therefore, the extra time-dependent modulation of the echo by

_{x}*G*contains information about the spatial distribution of spins.

_{x}####
5. **Conclusion**

What do we learn from this example? A phase-encoding gradient changes the amplitude of the echo but not its shape. A frequency-encoding gradient, on the other hand, changes the shape but not the amplitude. Both can be written as a modulated Larmor-frequency signal. In the pulse sequences shown above, the Larmor frequency is drawn too low in order to make the figure clearer. In fact, the Larmor frequencies in MRI are many megahertz, and thousands of oscillations occur during the free induction decay and echo. I analyzed both phase encoding and frequency encoding in the

*x*direction and considered each individually, because I wanted to compare and contrast their behavior. In practice, frequency encoding is performed using a

*G*gradient in the

_{x}*x*direction and phase encoding with a

*G*gradient in the

_{y}*y*direction, mapping out the two-dimensional Fourier transform of the spin distribution (see

*IPMB*for more).

Until I did this calculation I never completely understood what the shape of the echo looks like during readout. I hope it helps you as much as it helped me. Enjoy!

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