In Ok Ko1, Bup Kyung Choi2, Nitish Katoch2, Ji Ae Park1, Yong Soo Cho3, Jin Woong Kim3, Hyung Joong Kim2, and Eung Je Woo2
1Korea Institute of Radiological and Medical Sciences, Seoul, Korea, Republic of, 2Kyung Hee University, Seoul, Korea, Republic of, 3Chosun University Hospital and Chosun University College of Medicine, Gwangju, Korea, Republic of
Synopsis
Conductivity tensor can realize volume conductor model of brain for neuroimaging and electrical stimulation. We report
validation of electrodeless conductivity tensor imaging (CTI) method [1].
From CTI imaging using giant vesicle suspension at 9.4T MRI,
relative error in conductivity tensor image was found to be
less than 1.7% compared with the measured values using an impedance analyzer. High- and low-frequency conductivity can quantify total and
extracellular water contents, respectively, at every pixel. Their
difference can quantify intracellular water content at every pixel. Current CTI method can separately quantify the contributions of ion
concentrations and mobility to the conductivity tensor.
Purpose
The purpose of this study is to
validate the performance of the CTI method to produce low-frequency
conductivity tensor images using a conductivity phantom including a giant
vesicle suspension.Methods
Giant vesicles dispersed in aqueous
solution were prepared as described by Moscho et al. [2]. 2 ml of phospholipids
dissolved in chloroform with a concentration of 30 mg/ml was added to a 1 liter
round-bottom flask containing 3 ml of chloroform and 400 μm of methanol. The
handling of phospholipids was
proceeded only under argon atmosphere. Distilled water or 0.75 % NaCl solution
in a volume of 20 ml was carefully added not to disturb the interface between
the aqueous phase and organic solution phase. The round-bottom flask was
installed to a rotary evaporator to remove organic solvent at 47 °C under vacuum with nitrogen trap for 20 min at 10 rpm
and then followed by another 20 min at 60 rpm. During evaporation of organic
solvents, phospholipids in organic solution trapped in the saline phase and
assembled to form giant vesicles. The resultant aqueous solution containing
giant vesicles was subjected to centrifugation at 1,500 rpm for 10 min. The
volume fraction of the giant vesicles after the centrifugation was about 80 to
90 % by visual observations. The mean and standard deviation (SD) of the diameters
of the giant vesicles were 13 ± 4.7 μm.
A
9.4T MRI scanner was used for imaging experiments. The high-frequency
conductivity images were acquired using the multi-echo spin-echo sequence with
an isotropic voxel resolution of 0.5 mm. The imaging parameters were as
follows: TR/TE = 2200/22 ms, number of signal acquisitions = 5, field-of-view
(FOV) = 65 × 65 mm2, slice thickness = 0.5 mm, flip angle = 90, and image matrix size
= 128 × 128. Six echoes were acquired with the total scan time of 23 min.
Diffusion weighted MR imaging was separately performed using the single-shot
spin-echo echo-planar-imaging sequence. The imaging parameters were as follows:
TR/TE = 2000/70 ms, number of signal acquisitions = 2, FOV = 65 × 65 mm2,
slice thickness = 0.5 mm, flip angle = 90, and image matrix size
= 128 × 128. The number of directions of the diffusion-weighting gradients was
30 with 15 b-values.Results and Discussion
Fig. 1(b)
shows the intermediate variables including the high-frequency
conductivity σH,
extracellular volume fraction χ,
extracellular water diffusion coefficient dew, intracellular water diffusion coefficient diw, and scale factor η
where the relation between the conductivity tensor C and the extracellular
water diffusion tensor Dew is given by C =
ηDew [1]. Fig. 1(c)
is the image of Dew estimated by
the CTI method [1] and (d) shows the reconstructed CTI image. Table 1 shows the mean and standard deviation
of the intermediate variables and the diagonal components Cxx, Cyy, and Czz. These values were computed from all pixels within each
region. The
value of σH
measured in the CTI framework at 400 MHz (Larmor frequency at 9.4 T) were 1.86
± 0.04 and 1.11 ± 0.04 S/m in the electrolytes #1 and #2, respectively. In the
giant vesicle suspension, σH
was 1.89 ± 0.02 S/m. The value of χ in both electrolyte regions was 1.00 ± 0.02 as expected. The
value of χ in the giant vesicle
suspension was 0.13 ± 0.04, which was in good agreement with the visually
observed value after the giant vesicles were concentrated by centrifugation.
The
value of dew in the
electrolytes #1 and #2 were 2.90 ± 0.01 and 2.85 ± 0.02 μm2/ms,
respectively, which are close to the free water diffusion coefficient. The value of diw in the
electrolytes #1 and #2 were meaningless since they contained no cells. In the
giant vesicle suspension, dew was 1.93 ± 0.12
μm2/ms indicating that water diffusion in the extracellular space of
the giant vesicle suspension was hindered by the closely packed giant vesicles. The
value of diw in the giant
vesicle suspension was 0.98 ± 0.10 μm2/ms. Considering that the
average diameter of the giant vesicles was 13 μm, the small value of diw should have
stemmed from the restricted water diffusion [3] inside the giant vesicles.
Multiplying η to the diffusion tensor
Dew at each pixel,
the image of the conductivity tensor C
in Fig. 1 was reconstructed. Cxx,
Cyy, and Czz
in the giant vesicle suspension region were 0.29 ± 0.05, 0.30 ± 0.07, and 0.29
± 0.05 S/m, respectively. The reconstructed
high- and low-frequency conductivity values from the CTI were marked
Fig. 2 for comparisons by using the
impedance analyzer.Conclusion
The
performance of the CTI method to produce low-frequency conductivity tensor
images is validated using a conductivity phantom including a giant vesicle
suspension. Note that the high-frequency and low-frequency conductivity values
are correlated with the total and extracellular water contents, respectively,
at every pixel. The difference between them is correlated with the
intracellular water content at every pixel. In addition, the CTI method can
quantitatively separate the contributions of ion concentrations and mobility to
the conductivity tensor at every pixel
.Acknowledgements
This
work was supported by the National Research Foundation of Korea (NRF), the Ministry
of Health and Welfare of Korea, and Korea Institute of Radiological and Medical
Sciences (KIRAMS) grants funded by the Korea Government (2018R1D1A1B07046619,
2019R1A2C2088573, HI18C2435, and 50461-2019).
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