In this study we used cellular magnetic resonance imaging (MRI) to detect mesenchymal stem cells (MSC) labeled with a Fluorine-19 (19F) agent. 19F-MRI offers unambiguous detection and in vivo quantification of labeled cells.
We investigated two common stem cell transplant mouse models: an immune competent, syngeneic transplant model and an immune compromised, xenograft transplant model. 19F labelled stem cells were implanted intramuscularly into the hindlimb of healthy mice. The transplant was then monitored for up to 17 days using 19F-MRI, after which the tissue was excised for fluorescence microscopy and immunohistochemisty.
Immediately following transplantation, 19F-MRI quantification correlated very well with the expected cell number in both models. The 19F signal decreased over time in both models, with a more rapid decrease in the syngeneic model. By endpoint, only 2/7 syngeneic mice had any detectable 19F signal. In the xenograft model, all mice had detectable signal at endpoint. Fluorescence microscopy and immunohistochemistry were used to show that the 19F signal was related to the presence of bystander labeled macrophages, and not original MSC.
Our results show that 19F-MRI is an excellent tool for verifying the delivery of therapeutic cells early after transplantation. However, in certain circumstances the transfer of cellular label to other bystander cells may confuse interpretation of the long-term fate of the transplanted cells.
Citation: Gaudet JM, Ribot EJ, Chen Y, Gilbert KM, Foster PJ (2015) Tracking the Fate of Stem Cell Implants with Fluorine-19 MRI. PLoS ONE 10(3): e0118544. https://doi.org/10.1371/journal.pone.0118544
Academic Editor: Gary L. Dunbar, Central Michigan University, UNITED STATES
Received: August 14, 2014; Accepted: January 20, 2015; Published: March 13, 2015
Copyright: © 2015 Gaudet et al. This is an open access article distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited
Data Availability: All image files are available from the Dryad database (http://dx.doi.org/10.5061/dryad.2g9k2).
Funding: This study was supported by R4174A17 Ontario Preclinical Imaging Consortium, Ontario Research Fund, PF (URL: https://www.ontario.ca/business-and-economy/ontario-research-fund). The funders had no role in study design, data collection and analysis, decision to publish, or preparation of the manuscript.
Competing interests: The authors have declared that no competing interests exist.
Stem cell therapy has the potential to play an important role in regenerative medicine. Mesenchymal stromal/stem cells (MSC) have been extensively investigated for clinical application over the past decade.[1,2] MSC are capable of differentiating into a variety of important tissues, such as: bone, cartilage and adipose. They also display immunomodulatory properties.[4–6] Their presence in adult tissue, and ease of expansion in vitro has made MSC good candidate cells for clinical translation.[7,8]
In order to advance stem cell therapy, tools must be developed to monitor the survival of implanted stem cells non-invasively after administration to the patient. Magnetic resonance imaging (MRI) cell tracking is an effective method to visualize and monitor cells non-invasively after implantation due to the high spatial resolution and lack of ionizing radiation.
The majority of MRI cell tracking studies have used iron oxide nanoparticles to label the cells of interest.[9–15] When imaged with MRI, the iron nanoparticles produce a dark signal void in T2/T2* weighted proton images. This technique is highly sensitive, permitting the imaging of single cells.[16,17] Limitations with tracking iron-labeled cells arise from low specificity, due to other regions in the image with low signal, and from complicated in vivo quantification of the signal loss. Our group and others have shown that degree of signal loss produced by iron labeled cells is only linear at low iron concentrations.[16,18] Furthermore the high sensitivity to iron can produce ambiguity due to the strong false-positive signal produced when even a small number of bystander cells become labeled inadvertantly.[19,20]
As an alternative to iron cell tracking, fluorine-19 (19F) MRI with perfluorocarbon (PFC) nanoemulsions has been used for cell tracking. 19F MRI is able to image implanted cells with high specificity due to the lack of detectable fluorine in biological tissue.[22,23] Quantification of implanted cells is possible since the 19F MRI signal intensity is linearly related to the number of 19F-labeled cells. Unlike PET/SPECT probes, 19F does not undergo radioactive decay allowing for longitudinal studies without radiation-induced toxicity to the implanted cells or surrounding tissue. Furthermore, the first clinical application of 19F-MRI cell tracking for DC immunotherapy was recently reported, showing the technique is both feasible and safe for human application.
In this paper, we investigated the feasibility of quantifying MSC survival in two different immune system environments. This was performed by comparing the change in 19F-MRI signal strength over time using two popular transplantation models. A syngeneic transplant model, with mouse MSC (mMSC) implanted in an immune-competent mouse host, was compared to a xenograft model produced from human MSC (hMSC) implanted in an immune-compromised mouse. Our goals were: i) to quantify the apparent cell number non-invasively for 2.5 weeks and ii) to validate in vivo 19F-MRI quantification results with fluorescence microscopy and immunohistochemistry.
MSC culture and labeling
hMSC came from bone marrow donated by healthy young adult volunteers after written informed consent according to a protocol approved by University Health Network Research Ethics Board (Toronto, Canada). hMSC were cultured as described by Ribot et al. mMSC derived from the bone marrow of C57Bl/6 mice and expressing green fluorescence protein (GFP+) were purchased from Cyagen Bioscience Inc. (Catalog # MUBMX-01101). The cells were cultured in OriCell Mouse MSC Growth Medium until 90% confluent. The mMSC were passaged once before labeling and implantation.
All MSC were labeled with the red fluorescent perfluoropolyether agent, Cell Sense (CS-ATM-DM Red; CelSense Inc. Pittsburg, USA). Labeling took place over 24 hours at a concentration of 2.5mg/mL. After incubation, the cells were washed 3 times with Hank’s balanced salt solution (HBSS), harvested with Trypsin, spun down and counted. At this stage the cells were tested for viability using trypan blue exclusion. Intracellular 19F content of cells was determined using NMR spectroscopy, as we have described previously.
1.5x106 Cell Sense-labeled hMSC in 100μL of HBSS were implanted intramuscularly into the right hindlimb muscle of immune-compromised, nude mice (nu/nu, Charles River Canada) to produce a xenograft model (n = 7). In a similar manner, 2.0x106 labeled mMSC in 100μL of HBSS were implanted into immune competent, C57Bl/6 mice (Jackson Laboratories) producing a syngeneic model (n = 8). In both cases, the injections were performed under 2% isoflurane anesthesia. All experiments involving human and mouse stem cells, as well as animal use, were approved by the Western University Animal Use Committee (AUP 2009–042).
All images were collected using a 9.4T Varian small-animal MRI scanner. A 3D balanced steady state free precession (bSSFP) sequence was used for both proton and fluorine imaging. Cell pellets containing 2x105, 4x105, 6x105, 8x105, 1x106 and 2x106 19F-labeled MSC were imaged alongside a reference tube of known fluorine concentration (7.3x1016 19F/μL). MRI was performed using a dual-tuned birdcage volume coil (diameter 2.2cm, length 5.1cm), tuned to 400.2 MHz and 376.8 MHz for proton and fluorine imaging respectively. For proton imaging of cell pellets the scan parameters were: repetition time (TR) = 3.8ms, echo time (TE) = 1.9ms, receiver bandwidth (rBW) = 125kHz, flip angle (FA) = 30°, averages = 2, resolution = 200x200x200μm3. For fluorine imaging the parameters were: TR = 3.5ms, TE = 1.8ms, rBW = 25kHz, FA = 70°, averages = 250, resolution = 1x1x2mm3. Total protocol time for both proton and fluorine imaging was under 90 minutes. The pellets were imaged on three separate occasions to test quantification variability.
Mice containing 19F-labeled MSC implantations were imaged at four time points, starting on day 0, after implantation. The scan parameters were the same for the in vivo mouse MRI as described previously. During scanning the mice were anesthetized with 2% isoflurane, with breathing rate and temperature monitored. Due to the high sensitivity of bSSFP to off-resonance frequencies, a narrow 1.5kHz sinc pulse was used to excite only the 19F agent.
Image analysis and quantification
Prior to image analysis, a signal correction was applied to the 19F datasets by subtracting a constant value (x) from all voxels within the dataset using the image program, ImageJ.[28,29] The value of x was equal to the signal of the single voxel containing the lowest signal throughout the entire dataset. This linear translation acted to left-shift the data distribution to begin at zero. Quantification was performed using Voxel Tracker software, as described by Srinivas et al. Briefly, in the 19F MR images, the signal contained within a hand drawn ROI is summed and compared to the average signal produced by the reference tube of known concentration (2.6x1016 19F spins/μL). This value (X) provides the total number of 19F spins located at the ROI. NMR spectroscopy was then performed using a known number of the same transplanted cells, along with a second 19F source containing a known number of 19F spins. By comparing the relative NMR signals, the number of 19F spins per cell (Y) is obtained. Division of X by Y yields the number of cells located at the ROI. Significance between time-points was assessed using a repeated measures, one-way ANOVA.
Mice were sacrificed and perfused with 4% paraformaldehyde following the final imaging timepoint. In addition, one mouse from each model was sacrificed and perfused on Day 0 for comparison. The hindlimb muscle was extracted and cryoprotected with increasing concentrations of sucrose (10%, 20%, 30%) before freezing in OCT medium. Tissue was sectioned with a cryostat. Fluorescence microscopy was performed to image the red fluorescent 19F-label as well as the GFP+ mMSC with a Zeiss AXIO Imager microscope (Carl Zeiss Canada Ltd). Immunohistochemistry staining was then performed on these sections. Macrophage presence was assessed using Biotin anti-mouse macrophage (F4/80) monoclonal antibody (Cedarlane Laboratories Ltd) with 3,3’-Diaminobenzidine (DAB) counterstain.
Labeling of MSC with Cell Sense
Fig. 1 shows that labeling with the 19F agent did not negatively affect the mMSC cellular viability. The viability of the hMSC was slightly decreased following labeling. Previous work by our group demonstrated that the perfluorocarbon, Cell Sense, did not negatively impact differentiation of labeled hMSC into osteogenic or adipogenic lineages. NMR revealed the cellular loading of 19F varied between experiments and cell types within the range of 8.2x1010 to 2.4x1011 atoms.
(A) Cellular viability was investigated before and after labeling with the 19F-agent, Cell Sense. Although a statistically significant difference was observed in hMSC after labeling, the viability remained high (>80%) in all experiments. There was no significant difference in mMSC viability. (B) Cellular loading was determined by performing NMR on a known number of cells alongside a reference peak with a known number of 19F atoms. We observed variation in cellular loading of both hMSC and mMSC between experiments. However, this variation does not affect in vivo 19F quantification since each transplant was only compared to its specific cellular loading.
Quantification of 19F in cell samples
Quantification of the 19F signal was tested in vitro using Cell Sense labeled mMSC pellets. Imaging was performed at 9.4T on six cell pellets ranging from 200k to 2 million cells. Fig. 2 represents the average quantification and standard deviation from imaging the cell pellets on three different occasions. We observed a strong linear relationship between the MR quantification and the real cell number, with an R2 = 0.98.
Quantification was validated in a phantom study using cell pellets ranging from 2x105 to 2x106 MSC. Pellets were imaged three times, with the error bars representing the standard deviation between scans. The 19F-MRI quantification is in very strong agreement with the true number of cells, and has a Pearson correlation coefficient of 0.99. The red line represents the ideal result of a 1:1 correlation.
In vivo detection of 19F MRI signal
19F-MRI signal was initially detectable in all mice following intramuscular injection of 2.0x106 mMSC or 1.5x106 hMSC. On day 0 quantification of the in vivo signal agreed very well with the number of implanted cells (Fig. 3). Over time the signal decreased in both models. In the immune competent model (Fig. 3A), a significant effect was observed in the decrease in 19F MRI signal over time [F(1.703,6.812) = 39.85, p<0.001]. Post hoc Tukey tests showed there was a significant difference in 19F signal between day 3 and day 9 (p<0.01), and day 9 and 16 (p<0.05). At 16 days post implantation only two mice had any detectable signal remaining. Signal in the immune-compromised mice (Fig. 3B) decreased more slowly [F(1.378,5.511) = 30.97, p<0.01], with significance from day 0 only detectable on day 17 (p<0.01). Furthermore, at this endpoint all immune-compromised mice still had detectable signal.
(A) Following implantation of 2x106 mMSC, 19F-MRI was used to quantify the number of cells remaining over 16 days. By day 16, only 2/7 mice had any detectable signal remaining. A significant difference from day 0 is denoted by +, from day 3 by ◆, and from day 9 by ■. (B) The number of detectable cells over a similar time period following a transplant of 1.5x106 hMSC. 19F signal was found to decrease at a slower rate, with observable signal in all mice at endpoint. Statistical significance is denoted in the same way as A.
Representative MR image data, fluorescence microscopy, and H&E obtained on day 0 is shown in Fig. 4. Overlays of the 19F MRI onto the proton image at day 0 are show in 4A and E for the immune competent and immune compromised mice respectively. Fig. 4B and F show that the red fluorescence signal from the 19F labeling agent can be detected on day 0 in both models. The green fluorescence associated with the GFP+ mMSC was also clearly visible at the site of their implantation on day 0 (Fig. 4C). Overlaying the two fluorescent images revealed strong co-localization, with a Pearson’s correlation coefficient of 0.80, between the red fluorescent 19F agent and the GFP+ mMSC in Fig. 4D. The corresponding H&E stained tissue sections reveal the location of the implant within the muscle (Fig. 4G,H).
(A, E) Representative MRI from mice receiving either 2x106 mMSC or 1.5x106 hMSC respectively. The day 0 in vivo 19F-MRI quantification correlates very well with the number of implanted cells. The reference tube is marked by “R”. (B) The red fluorescent fluorine agent is clearly visible in the tissue of the immune competent model, (F) as well as in the immune-compromised model. (C) Furthermore, the GFP+ mMSC are observable within the tissue section. (D) Overlaying the two fluorescent images, reveals the 19F agent colocalized with the GFP+ mMSC, as expected. (G, H) H&E stained tissue sections corresponding to the fluorescence microscopy clearly show the implant site of the mMSC and hMSC respectively. Scale bars in all images represent 250μm.
Fig. 5 shows representative MR image data, H&E, F4/80 immunohistochemistry and fluorescence microscopy obtained at the experimental endpoint. By day 16 post implantation no 19F signal from the mMSC was detectable in 5/7 of the immune competent mice. One of these mice is shown in Fig. 5A where the only 19F signal comes from the reference tube. In contrast, 19F signal was still detectable in all of the immune compromised mice at day 17, an example is shown in Fig. 5E.
(A) By day 16, 5/7 immune competent mice had no 19F signal remaining as shown by the representative MRI. The reference tube is marked by “R”. (B) Fluorescence microscopy of the muscle tissue revealed little red fluorescence remaining in the immune competent mice. No GFP+ mMSC were detectable by fluorescence microscopy, suggesting the original mMSC are no longer present. (C) H&E staining reveals the presence of cells at the implant site which correlate well with the remaining 19F red fluorescence. (D) Immunohistochemistry staining of adjacent tissue sections with the anti-F4/80 antibody reveals the presence of a few macrophages at this location in the immune competent model. (E) At endpoint, all immune compromised mice had detectable 19F-MRI signal remaining. (F) We observed more red fluorescence from the 19F-label at the transplant site in the immune compromised mice. (G) Once again, H&E staining in the immune compromised model correlates well with the regions of red fluorescence. (H) Macrophage staining of the immune compromised model reveals many more F4/80 positive cells at the site of implantation. Furthermore, the fluorescence microscopy of neighboring tissue sections reveals that the red fluorescence from the 19F agent is in the same location as the macrophages. Once again, scale bars represent 250μm.
Fluorescence microscopy revealed only a small area of red fluorescence from the 19F agent in the immune competent model (Fig. 5B) compared to the immune compromised (Fig. 5F). In addition, no GFP+ mMSC were detectable in ex vivo samples at endpoint. H&E staining of the same tissue sections clearly showed cells at the site of the implant, which strongly corresponded with the 19F agent’s red fluorescence (Fig. 5C,G). Neighboring tissue sections corresponding to high red fluorescence were stained for the presence of macrophages using F4/80. Fig. 5D shows that relatively few macrophages were detected in the immune competent model at endpoint. In contrast, the F4/80 stain revealed large numbers of macrophages (Fig. 5H) in the same region as the red fluorescence from the 19F agent in the immune compromised model. The number of macrophages shows very strong correspondence to the amount of remaining red fluorescence in both cases.
An important additional finding worth noting was that 19F signal due to the use of inhalational isoflurane anesthesia could be eliminated by using a narrow 1.5 kHz sinc excitation pulse. S1 Fig. shows that a broader 3kHz RF pulse led to substantial background 19F signal in the mouse body. Isoflurane becomes concentrated within fat pads during imaging and these high levels of 19F signal can lead to false-positive detection and incorrect quantification. Isoflurane anesthesia is preferred for the ease of use and the relatively long imaging times required for 19F MRI. Another option is ketamine/xylazine but this requires the use of an intravenous or intraperitoneal catheter and infusion pump in order to maintain effectiveness over the time period required which can be challenging in mice.[32–34] Pentobarbital is also capable of providing anesthetic for over 2 hours, but its use leads to a high mortality rate in experimental animals.
In vivo quantification of MSC
This study demonstrates the ability to use 19F-MRI cell tracking to detect and, most importantly, to measure the number of transplanted stem cells in vivo. Cell number cannot be quantified using other MRI cell tracking techniques. Numerous studies have reported on the challenges associated with quantification of signal loss due to iron-labeled cells.[19,20,35] This has, so far, narrowed the implementation of cell tracking for monitoring the fate of transplanted cells. In this study we show excellent correlation between the number of labeled cells implanted and the number of cells counted on day 0 by 19F-MRI. This capability will pave the way for MRI to be used for to confirm the delivery of therapeutic cell transplants.
The importance of accurate delivery of cells to a target tissue cannot be overstated. In preclinical investigations often stem cells will be transplanted then a set time allowed to lapse before the transplanted tissue is removed and processed for microscopy, to determine whether stem cells remain in the tissue. In many cases only a very small sample of the transplanted tissue is evaluated. In a previous study we used MRI to track iron-labeled MSC in a mouse model of spinal cord injury. Our in vivo imaging revealed that the challenging intrathecal injections of MSC were imprecise approximately 25% of the time; injected cells were often being deposited in tissue above the cord or leaking out of the cord. The histological assessment in this study involved the analysis of 1cm of cord tissue on either side of the transplant site, six weeks after transplantation. Without MRI, a negative observation of MSC by microscopy would have been taken as failure to engraft rather than due to a missed injection. Injection confirmation with 19F MRI would have the additional advantage of determining how many cells were properly injected and remain at the site.
In a first-in-man study, MRI and scintigraphy were used to assess the success of intranodal injections consisting of a 1:1 mixture of iron- or indium-labeled dendritic cell (DC) for cancer therapy in melanoma patients. Despite these cell injections being performed under ultrasound guidance the MRI of iron-labeled DC revealed that in 3/8 cases DC were injected near, but not in, the target lymph nodes. These findings make it clear that the outcome of this cell therapy on these patients would not be properly evaluated without knowledge of proper delivery of DC to the nodes. For DC therapy knowledge of the number of cells delivered to a lymph node is especially critical since DC migration to nodes correlates with effective stimulation of T cells. 19F-MRI therefore presents a promising solution to the clinical problem of verifying both the location and number of cells within the region of interest immediately following administration of treatment.
In these experiments the hMSC and the mMSC were both capable of taking up sufficient 19F label for in vivo detection, without decreasing viability below 80%. We observed some variation in the number of 19F atoms loaded per cell between experiments, although the average loading was not significantly different for mouse versus human MSC. The cell size is one of the more important factors influencing the labeling with Cell Sense and mouse and human MSC are approximately 30 microns in diameter. The fact that it is possible to obtain robust measurements of the number of cells detected by MRI, despite inter-experiment variation in the number of 19F atoms per cell, is another positive feature of this type of cell tracking. Variation in 19F/cell is not a confounding factor in MRI quantification since the unique cellular loading is determined for each transplantation. This is particularly important when considering clinical translation, since 19F uptake is expected to vary between cell donors.
Monitoring the fate of MSC over time
This study also revealed some interesting information about tracking cell fate over time with 19F MRI. We studied the fate of MSC in two different models: mMSC implanted into healthy wild type C57Bl/6 mice (immune competent model) and hMSC implanted into healthy nude mice (immune compromised model). The MSC underwent clearance from the sites of implantation in muscle at different rates, which is not unexpected since the two different mouse strains have very different immune systems.
In the immune competent model, 5/7 mice had no MRI detectable 19F signal remaining at the site of injection by the endpoint. The other 2 mice had just 4% and 10% of the original signal remaining. There were no GFP+ cells detected by fluorescence microscopy but there was some red fluorescence, indicating that some of the 19F label persisted at the site but that it was not within GFP+ mMSC. The small amount of residual red fluorescent signal corresponded with F4/80 staining suggesting that some transfer of 19F label from mMSC to macrophages has occurred. The decline in the signal is likely the result of a number of different things happening at the transplant site. First, a large number of MSC will die early after their direct transplantation into a tissue. Second, the label may be diluted by MSC proliferation, or degradation of the label within MSC. Third, MSC may have migrated away from the implant site; although we did not detect 19F signal in other nearby locations.
The fact that for 5/7 mice no MRI signal was detected, even though red fluorescence was still observed in the tissues (as for the example shown in Fig. 5A-D) is most likely because the number of cells containing the red fluorescent 19F label is very small and this small amount of 19F signal is below the in vivo detection limits of the MRI protocols used in this study.
In the immune compromised model the 19F signal persisted in all mice until the experimental endpoint. Much more red fluorescence was observed in these tissues at the implant site and this corresponded well with F4/80 staining, again suggesting that the persistent 19F signal was related to transfer of label from hMSC to macrophages. A limitation of this study was that our hMSC were not also GFP+. This would have allowed us to say with more confidence that the 19F label was associated with macrophages and not the implanted hMSC. Clearance of label and macrophages may have been slower in these mice because of the inhibited immune system and lack of rejection response.
Our observation of bystander cell uptake of 19F cell label is supported by a study by Boehm-Sturm et al. In their study in vivo imaging of the location, density, and survival of neural stem cells implanted in the brain in a stroke model was performed using 19F MRI in combination with bioluminescence imaging. The signal from 19F labeled stem cells persisted for more than 4 weeks after implantation while, over the same time period, the bioluminescence declined, indicating stem cell death. Immunohistochemistry staining also revealed the presence of microglia/macrophages at the site of implantation.
Terrovitis et al. looked at the retention of iron labeled stem cells implanted into immune competent rats. Either rat or human cardiac-derived stem cells were injected intramyocardially. In both cases MRI signal loss due to iron was detected for 3 weeks post cell injection and correlated with the presence of iron containing macrophages in histology. Although the area of signal void decreased over time substantial signal void persisted at the injection site in all mice. Since proton MRI is sensitive to even small numbers of iron-labeled cells this form of cell tracking is most susceptible to the misinterpretation of cell fate. Previous studies performed in our lab using iron labeled syngeneic MSC also revealed the persistence of an iron signal void past 21 days in immune competent mice.
In summary, 19F MRI can be used to provide immediate assessment of implanted cells with excellent correlation between implanted cell number and in vivo quantification. Over time, as the cells are cleared from the transplantation site, transfer of the 19F label to bystander cells may confuse interpretation of the change in 19F signal. With the first-in-man studies of 19F MRI recently completed, this result will be particularly relevant when translating this technique into the clinic.
This work was supported by a research grant from the Ontario Institute for Cancer Research, Smarter Imaging Program. J.M.G. is jointly funded by the Translational Breast Cancer Research Unit and the Cancer Research and Technology Transfer training program. The funders had no role in study design, data collection and analysis, decision to publish, or preparation of the manuscript.
S1 Fig. Influence of excitation pulse width and shape on isoflurane detection.
(A) Strong isoflurane signal (red arrow) is detectable following accumulation in the fat pads of mice after excitation with the standard Gaussian filtered sinc pulse. This signal is affected by a chemical shift from the fat pad (blue arrow), the fluorine signal in the reference tube experiences does not shift. By applying a Gaussian filter to the sinc a more rectangular waveform is achieved after Fourier transform, but at the cost of broadening the pulse in frequency space. (C) The mouse was then scanned with a non-filtered sinc pulse. Fourier transform of this pulse produces a narrower excitation that did not excite isoflurane 19F atoms, preventing background signal. Both images have been windowed to the same level, and brightened to show the noise distribution. (B) The filtered pulse shape in time space is shown, with a width of 0.66ms. (D) The non-filtered sinc pulse width is much broader with a FWHM of 1.32ms in time space. This produces a narrower pulse in frequency space, preventing the excitation of isoflurane signal.
Conceived and designed the experiments: JG ER KG PF. Performed the experiments: JG ER YC. Analyzed the data: JG ER. Contributed reagents/materials/analysis tools: KG PF. Wrote the paper: JG ER YC KG PF. Designed hardware RF coil for data acquisition: KG.
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