Reza Babaloo1,2, Soheil Taraghinia1, Volkan Acikel3, Manoochehr Takrimi1, and Ergin Atalar1,2
1National Magnetic Resonance Resarch Center (UMRAM), Bilkent University, Ankara, Turkey, 2Department of Electrical and Electronics Engineering, Bilkent University, Ankara, Turkey, 3Aselsan, REHIS Power Amplifier Technologies, Ankara, Turkey
Synopsis
Gradient array systems can produce highly
flexible spatial encoding magnetic fields. In the array structure, time
fidelity of gradient current waveforms decreases due to high mutual coupling
between gradient coils. Here we propose a closed-loop feedback in combination
with feedforward to compensate for errors in the gradient current waveforms. A real-time digital PID controller is designed by considering the transfer function
of the array system. The controller updates the applied voltage on the gradient
coil by changing the duty cycle of pulse-width modulated (PWM) signals to
decrease the error between desired and measured currents.
Introduction and Purpose
Gradient array systems have been used to
generate dynamically controllable magnetic field profiles1-4. In
these systems, multiple gradient coils are driven individually by independent gradient
power amplifiers (GPAs). The accuracy of gradient current waveforms has a
significant effect on the image quality and providing gradient coil currents
with high fidelity might be challenging due to mutual coupling between coils, GPA
imperfections, and time-varying parameters in gradient hardware. Although
considering the first-order model in the feedforward including mutual
coupling provides adequate currents to the coils1, residual errors
due to measurement errors in the determination of model parameters, not
considering GPAs in the model, high order effects and time-varying
parameters can still decrease the accuracy of coil currents time-courses. A
close-loop feedback can be used to overcome these imperfections5. In
this work, a digital real-time (proportional–integral–derivative) PID
controller is designed to compensate for the above-mentioned effects which are not
corrected by the feedforward model. The controller also degrades current
waveforms sensitivity to the time-varying parameters and undesired external
disturbances like droop in the supply voltage.Methods
The block diagram of gradient array system
is shown in Fig.1. A typical trapezoid current waveform is used to drive two
channels of z-gradient array coils. The hardware limitations are considered in
designing input current waveforms. The first-order model including mutual
coupling provides the required voltage. This model acts like a multi-input-multi-output
(MIMO) proportional-derivate (PD) controller in the open-loop configuration. The
parameters were determined by measuring self-inductance, mutual inductance, and
resistance of coils.
$$\left[{\begin{array}{*{20}{c}}{{v_1}\left(t\right)}\\{{v_2}\left(t\right)}\end{array}}\right]=\left[{\begin{array}{*{20}{c}}{{L_1}}&M\\M&{{L_2}}\end{array}}\right]\left[{\begin{array}{*{20}{c}}{\frac{{d{i_1}\left(t\right)}}{{dt}}}\\{\frac{{d{i_2}\left(t\right)}}{{dt}}}\end{array}}\right]+\left[{\begin{array}{*{20}{c}}{{R_1}}&0\\0&{{R_2}}\end{array}}\right]\left[{\begin{array}{*{20}{c}}{{i_1}\left(t\right)}\\{{i_2}\left(t\right)}\end{array}} \right]$$
The close-loop feedback PID controller is used
in parallel with the feedforward model which will update the required voltage
to minimize the error between desired input and measured output. The
transfer function analysis can be used for the determination of PID
parameters.
$${I_m}\left(s\right)={\left[{{\rm{I}}+{G_c}\left(s\right){G_p}\left(s\right)}\right]^{-1}}\left[{{G_m}\left(s\right){G_p}\left(s\right)+{G_c}\left(s\right){G_p}\left(s\right)}\right]{I_d}\left(s\right)$$
Where,
Gm(s), Gp(s), Gc(s) are transfer functions for the model,
gradient coil with amplifier and PID controller respectively. Assuming no
mutual coupling and single-input-single-output
PID, the transfer function for channel 1 is as
follow:
$$\frac{{{I_{m1}}\left(s\right)}}{{{I_{d1}}\left(s\right)}}=\frac{{{G_{m1}}\left(s\right){G_{p1}}\left(s\right)+{G_{c1}}\left(s\right){G_{p1}}\left(s\right)}}{{1+{G_{c1}}\left(s\right){G_{p1}}\left(s\right)}}$$
Gm1(s) is the model of channel 1 which is
the inverse of Gp1(s) in
the ideal case. Assuming Gm1(s)Gp1(s) ≈ 1, to have an accurate regulation on the output current, |Gc1(s)Gp1(s)| >> 1. Therefore, by increasing the gain of controller (Gc1)
at the operating frequency, the measured current approaches to the desired one.
The PID block changes the desired voltage in a real-time fashion which results in
a change in the duty cycle of PWM signals. The transfer function analysis
reveals two things, (a) if the model can be determined exactly, there
is no need for the feedback loop. However, in the real case, the imperfections
and measurement errors affect the system which cannot be modeled, (b) considering mutual coupling in the model is not compulsory and the feedback loop can compensate for it.
The whole control system was designed digitally
using the Xilinx VC707 FPGA board. The PWM signals were generated with 15-bit
resolution and duty cycles can be controlled in the range of picosecond. A
home-built full-bridge power amplifier with 1 MHz effective switching frequency
is used to provide 10V and 8A at the output.Results
The coil currents were measured by fluxgate
current sensors (IT 205-S) and results are shown on the oscilloscope. The
output currents are shown for driving the coils individually (no mutual
coupling, no feedback, Fig. 2a,b) and simultaneously (Fig. 2c,d). Due to
measurement errors in the model parameters and not considering GPA, the
desired waveform cannot be achieved. It is possible to change the parameters
manually and iteratively to get the desired one, however, the model may change
caused by time-varying parameters such as temperature. The output currents in
the presence of feedback loop are depicted in Fig. 2e,f. The feedback
performance is tested in two cases, input currents are applied with (a)
different amplitudes, same phases (Fig. 3a,b), (b) same amplitudes,
different phases (Fig. 3c,d). The robustness of system is tested for droop
in the supply voltage (Fig. 3e,f). The simulation of magnetic field profiles
generated by actual current values on the coils, with and without the controller is shown in Fig.4.Discussion and Conclusion
In this work, to compensate the mutual coupling
and undesired imperfections, a real-time digital PID controller design is
proposed. The feedback loop in combination with feedforward PD model
provides the desired voltage which has to be applied to the coils. The PID
controller can adjust the PWMs duty cycle in order to minimize the error
between desired and measured current. Although adding PID can make the correction
for undesired distortions, the stability of the system has to be considered
in the presence of the controller. To have a perfect current regulation, the
gain of controller has to be high which may cause instability in the system or
exceeds the GPAs limitation.Acknowledgements
No acknowledgement found.References
1. K.
Ertan, S. Taraghinia, and E. Atalar, “Driving Mutually Coupled Gradient Array
Coils in Magnetic Resonance Imaging,” Magnetic resonance in medicine,
(2019).
2. K. Ertan, S.Taraghinia, A. Sadeghi, E. Atalar “A
z-gradient array for spatially oscillating magnetic fields in multi-slice
excitation,” Magn Reson Mater Phy (2016) 29: 1. doi:10.1007/s10334-016-0568-x,
Abstract No:81.
3. Smith, E., Freschi, F., Repetto, M., &
Crozier, S. (2017). The coil array method for creating a dynamic imaging
volume. Magnetic resonance in medicine, 78(2), 784-793.
4. Littin, S., Jia, F., Layton, K. J., Kroboth, S.,
Yu, H., Hennig, J., & Zaitsev, M. (2017). Development and implementation of
an 84‐channel matrix gradient coil. Magnetic Resonance in Medicine.
5. Y. Duerst, B.J. Wilm, B.E. Dietrich, S.J.
Vannesjo, C. Barmet, T. Schmid, D.O. Brunner, and K.P. Pruessmann, “Real‐time
feedback for spatiotemporal field stabilization in MR systems,” Magnetic
resonance in medicine, 73:884-893,2015.