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This study aimed to determine the homing potential and fate of epidermal neural crest stem cells (eNCSCs) derived from hair follicles, and bone marrow-derived stem cells (BMSCs) of mesenchymal origin, in a lipopolysaccharide (LPS)-induced inflammatory lesion model in the rat brain. Both eNCSCs and BMSCs are easily accessible from adult tissues by using minimally invasive procedures and can differentiate into a variety of neuroglial lineages. Thus, these cells have the potential to be used in autologous cell-replacement therapies, minimizing immune rejection, and engineered to secrete a variety of molecules.
Both eNCSCs and BMSCs were prelabeled with iron-oxide nanoparticles (IO-TAT-FITC) and implanted either onto the corpus callosum in healthy or LPS-lesioned animals or intravenously into lesioned animals. Both cell types were tracked longitudinally in vivo by using magnetic resonance imaging (MRI) for up to 30 days and confirmed by postmortem immunohistochemistry.
Transplanted cells in nonlesioned animals remained localized along the corpus callosum. Cells implanted distally from an LPS lesion (either intracerebrally or intravenously) migrated only toward the lesion, as seen by the localized MRI signal void. Fluorescence microscopy of the FITC tag on the nanoparticles confirmed the in vivo MRI data,
This study demonstrated that both cell types can be tracked in vivo by using noninvasive MRI and have pathotropic properties toward an inflammatory lesion in the brain. As these cells differentiate into the glial phenotype and are derived from adult tissues, they offer a viable alternative autologous stem cell source and gene-targeting potential for neurodegenerative and demyelinating pathologies.
A number of CNS injury and neurodegenerative diseases result in varying degrees of cell death and neuroinflammation. Cell-based therapies involving stem cells aim to replace these lost cells or repair damaged areas, thus providing functional recovery. However, before the potential of stem cell-based therapies can be realized, it is important to understand the behavior of these cells after implantation in vivo and the practicalities of different routes of administration. Such longitudinal studies are best performed by using noninvasive in vivo MRI cell-tracking protocols and indeed are a prerequisite for cell-replacement therapy for translation to the clinic.
An important factor in clinical translation of cell-based therapy is the selection of appropriate cell types for transplantation. Stem cells derived from adult tissues have a number of advantages, including their utility in autologous stem cell therapy, where they not only reduce the need for immunosuppression but are harvested relatively easily in the clinic. Current literature indicates the promising repair potential of two adult stem cell types: epidermal neural crest cells and bone marrow mesenchymal stem cells. Neural crest cells (NCCs) constitute a population of neuroepithelial, migratory, multipotent stem cells that give rise to most of the peripheral nervous system during development, including dorsal root ganglia (DRG) neurons, DRG satellite glia, and Schwann cells. NCCs also give rise to melanocytes and skeletal structures of the face. Until recently, NCCs were considered a transient cell population that existed only during development. However, recent work demonstrated that multipotent NCCs persist into adulthood within the stem-cell niche of hair follicles, and these adult-resident cells have been termed epidermal neural crest stem cells (eNCSC) . Because eNCSCs retain the neuroglial differentiation potential of embryonic NCCs  and can be harvested from hairy skin by using a minimally invasive procedure, they are an attractive cell type to consider for autologous cell-replacement therapies to repair the injured CNS.
The other cell type with a similar potential for autologous cell-based applications in CNS repair is mesenchymal stem cells (MSCs) derived from the bone marrow. MSCs derived from marrow stromal cells differentiate into tissues of mesodermal lineage, such as fat, bone, and cartilage , but can also differentiate along neuroglial lineages . In the uninjured rat brain, bone marrow-resident cells continuously contribute to neural populations, including neurons, microglia, and occasionally astrocytes in the dentate gyrus and periventricular zones . However, the numbers of resident MSCs homing to CNS lesions are small. By harvesting, expanding in vitro, and then re-introducing autologous cells systemically, more stem cells are likely to home to the sites of CNS injuries, where they can provide therapeutic benefit. For example, human MSCs injected intravenously into rats after spinal cord injury were found to infiltrate mainly into the ventrolateral white matter tracts, where they differentiated into oligodendrocytes ; however, the migration of the cells was assessed only at the end point instead of the longitudinal imaging used in the present study. In stroke and inflammatory-lesion models of adult brain injury in rats, as well as in human stroke studies, injected MSCs have been reported enter the brain from the circulation and stimulate host oligodendrogenesis and remyelination [6-9]. Although it must be emphasized that the differentiation of BMSCs into neural phenotypes is somewhat controversial, their homing ability may be useful in gene or growth-factor delivery.
Several studies have demonstrated the migration of stem cells after intravenous injection (Chen et al., 2001; Garbuzova-Davis et al., 2003; Jendelova et al., 2004; Takeuchi et al., 2007) in models of neurodegeneration. However, the models used in these studies involved mainly ischemia and compression injury, which give rise to more severe lesions. This study aims to assess stem cell behavior in more moderate cerebral insults. In addition, although earlier studies clearly demonstrate the potential of eNCSCs and BMSCs for neural repair, they provide only a 'snapshot,' postmortem view of what is happening to the transplanted cells. Therefore, the aims of this study were to use longitudinal in vivo MR imaging, followed by histologic analysis, to monitor the migratory potential and resulting fate of eNCSCs and BMSCs, by using two routes of administration (cerebral implantation or intravenous injection) in a lipopolysaccharide (LPS) lesion model of CNS inflammation.
All surgical procedures were carried out under a UK Home Office Project Licence in accordance with the UK (Animals) Scientific Procedures Act 1986. Healthy adult (250 to 300 g) male Sprague-Dawley rats (Harlan, UK) were acclimatized for a week on a regular diet and equal light/dark cycle.
Rat eNCSCs were obtained from the hair bulbs of vibrissa whiskers, as described previously [1,10]. In brief, 2-week-old Sprague-Dawley rat pups were killed by carbon dioxide inhalation and their whisker pads removed and placed in DMEM. Individual whiskers were isolated and trimmed to leave only the bulge region, and the covering connective tissue was removed. Dissected hair-bulge explants were then allowed to attach to collagen-coated T75 flasks for 4 hours in a minimal volume of 10% FCS-DMEM and were subsequently topped up with 5 ml 10% FCS-DMEM. Medium was changed every third day. After 4 to 5 days in culture, neural crest cells were observed migrating away from the hair-bulge explants (Figure (Figure1).1). At this stage, the hair-bulge explants were carefully removed with an 18G needle to minimize contamination with later-migrating cell types, such as keratinocytes. After 10 days in vitro, cells were prelabeled with IO-TAT-FITC nanoparticles and implanted, as described later. Immunocytochemistry at the time of injection demonstrated that more than 60% of the cells were Sox10 immunopositive eNCSCs (Figure (Figure1c).1c). Confirmation of their neuroglial lineage was confirmed by supplementing 10-day-old cultures with 10 ng/ml neuregulin for 4 days, which caused eNCSCs to differentiate into S100-positive Schwann cells (Figure (Figure1d1d).
Bone marrow-derived stem cells were harvested from adult (300 g) Sprague-Dawley rats. Animals were killed, the hindlimbs were shaved, and the femurs and tibias removed aseptically. Then 10% FCS-DMEM was used to flush the marrow shafts by using a 26G needle, and the bone marrow was harvested. After centrifugation (1,500 rpm, 3 minutes), the pellet was resuspended in 10% FCS-DMEM. Cells were then cultured in previously prepared PLL-coated dishes, in DMEM supplemented with 10% FCS and gentamicin (25 μg/ml). Flasks were incubated at 37°C and 7.5% CO2. Two days after plating, the dishes were washed 3 times with 10% FCS-DMEM to remove nonadherent hematopoietic cells. Subsequently, 100% culture medium was changed every 2 days to maintain the health of the culture. To confirm the mesenchymal phenotype of the BMSCs, cells were differentiated into osteogenic or adipogenic lineages for 14 days in culture and were fixed with 4% paraformaldehyde for 10 minutes and stained with either 40 mM Alizarin Red (Sigma) or fresh Oil Red O (Sigma) according to Zhao et al.  (Figure 1i, j). The phenotype of the cells was also confirmed by using vimentin, CD90, and CD45 immunocytochemistry (Figure 1e-g).
Dextran-coated iron oxide nanoparticles were prepared in house according to the method of Josephson et al. . The nanoparticles were conjugated with both FITC, for histologic analysis and TAT peptide as a membrane-transfection agent. Cells were prelabeled with IO-TAT-FITC nanoparticles (mean diameter, 20 nm)in vitro overnight. The final IO incubation solution comprised 10 μg Fe/ml/100,000 cells, in accordance with our previous studies [13,14].
Animals were divided into three groups for each cell type: cells implanted onto the corpus callosum of healthy animals (n = 3), cells implanted 3 mm medial to LPS injection (n = 5), and cells injected intravenously 1 week after LPS injection (n = 2).
Animals were immunosuppressed with cyclosporine A (Sandimmun, Sandoz, UK) administered intraperitoneally at a dose of 2.5 mg/kg daily from the day of cell implantation until death. Thermoregulation of the rat was monitored during surgery with a rectal probe and kept constant at 37°C with a feedback-controlled warming blanket (Harvard Apparatus, Massachusetts, USA). For the animal lesioning, 5 μl of 1-μg/μl lipopolysaccharide (LPS) (in saline) was injected onto the corpus callosum of healthy animals (250 g) by using a small-animal stereotactic frame (Kopf Instruments, Tujunga, USA) at the following coordinates derived from a rat brain atlas : A-P, + 1.0 mm; L-M, -1.0 mm; D-V, -3.2 mm. Before surgery, a single-cell suspension was prepared in DMEM supplemented with 0.04 mg/ml bovine pancreas DNase (Sigma-Aldrich) to prevent clumping of the cells. Then 50,000 cells in a volume of 5 μl were injected at a rate of 1 μl/min (Figure (Figure2).2). The needle was maintained in situ for 2 minutes before and 5 minutes after cell injection to allow intracranial pressure equalization. For implantation into the healthy animals, stereotactic coordinates were as follows (relative to the bregma); corpus callosum: A-P, + 1.0 mm; L-M, -2.4 mm; D-V, -3.2 mm. When cells were implanted into the LPS-lesioned animals, the following stereotactic coordinates were used: A-P, +1.0 mm; L-M, -4.0 mm; D-V, -4.0 mm to maintain a substantial distance between the cells and LPS.
Animals were anesthetised, and thermoregulation was monitored during the MRI. In vivo serial imaging was performed at 9.4 T (Oxford Instruments, Abingdon, UK) by using a Varian console (Varian, Palo Alto, CA, USA). The head of the animal was positioned inside a 63-mm (internal diameter) birdcage coil. To visualize the implanted cells, a spin-echo T2-weighted image was acquired by using the following parameters: TR = 3,500 msec; TE = 40 msec; matrix = 256 × 128; FOV = 40 × 40 mm; slice thickness = 0.5 mm; with four averages, 20 slices per scan. Each animal was scanned weekly (on average, 4 times in total); with each scan lasting 30 minutes.
T2 measurements were obtained by using a spin-echo sequence with a fixed repetition time (TR) and a varying echo time (TE). The following parameters were used: TR = 3,500 msec; matrix = 256 × 128; FOV = 40 × 40 mm; slice thickness = 0.5 mm; number of averages = 1, and varying TEs of 12, 20, 30, 40, 50, 60, 70, 80, and 100 msec. T2 maps were reconstructed for each slice by using an ImageJ plug in (11). Regions of interest (ROIs) were drawn on standard anatomic images and then transformed into T2 maps. Average signal intensity (SI) values for each ROI at each TE value were transferred to GraphPad Prism (GraphPad Software, La Jolla, CA, USA); T2 relaxation curves were then created for each ROI. To visualize and confirm the neuroinflammatory lesion (edema induced by LPS) in the brain, T2* fast-spin-echo sequences were used with the following parameters: TR = 3,000 msec; TEeffective = 24 msec with a train of eight echoes; FOV = 40 × 40 mm; matrix = 256 × 128; averages = 16; slice thickness = 0.5 mm; number of averages = 8.
Animals were intracardially perfused with 4% paraformaldehyde and the brains removed. Brains were cryoprotected in 20% sucrose before being snap-frozen by using precooled isopentane. The 10-μm coronal sections were cut by using a cryostat (Leica Microsystems GmbH, Wetzlar, Germany) and placed on glass slides. The iron oxide nanoparticles were visualized by using a Prussian blue staining procedure by incubating the sections overnight in a solution of 10% potassium ferrocyanide and 20% hydrochloric acid (vol/vol).
The following primary antibodies were used: rabbit anti-Sox10 (1:10, Calbiochem), rabbit anti-GFAP (1:200, Sigma), CD90 (1:100, BD), CD45 (1:100, BD), S-100β (1:300, Dako), and Vimentin (1:50, Sigma). Cultured eNCSCs and BMSCs were fixed in 4% paraformaldehyde for 20 minutes, permeabilized with 0.1% Triton X-100 in PBS for 10 minutes, blocked with 10% normal sheep serum for 1 hour, and then processed with primary antibody. BMSCs grown in the presence of the osteogenic or adipogenic media were stained with 40 mM Alizarin Red or fresh Oil Red O, respectively.
Brain cryosections were blocked in 10% serum (species of secondary antibody), 0.1% Triton-X for 1 hour and then processed with the primary antibody. Primary antibodies (described earlier) were prepared in 10% serum/PBS and incubated overnight at 4°C. The lectin, Isolectin B4, was used to detect microglia (IB4; 1:50, Sigma). The secondary antibody in 10% serum/PBS was added for 1 hour at 4°C. Secondary antibodies were Alexa 488 goat anti-rabbit and Alexa 594 goat anti-mouse (Invitrogen), both applied at a 1:200 dilution. Finally, nuclei were counterstained with DAPI for 10 minutes. Coverslips were mounted on the sections by using Vectashield (Vector Laboratories, Burlingame, USA) as an antifade mountant. Tissue in situ hybridization for Sox10 mRNA was performed on the bulge region of vibrissae whiskers, according to standard protocols .
Neural crest cells characteristically express the nuclear transcription factor Sox10 . Hair-follicle bulge explants were processed for in situ hybridization with a Sox10 antisense riboprobe, which revealed a ring of staining corresponding to the niche of adult eNCSCs (Figure (Figure1a).1a). Between 50% and 60% of cultured cells that emigrated from bulge explants within 7 days (Figure (Figure1b)1b) had Sox10-immunopositive nuclei (Figure (Figure1c).1c). None of the cultured cells was immunopositive for the glial cell marker glial fibrillary acidic protein (GFAP; not shown), consistent with previous studies . However, cells could be driven to an S-100 immunopositive glial fate by supplementing 10 day-old cultures with 10 ng/ml neuregulin for 4 days (Figure (Figure1d1d).
The phenotype of the BMSCs was confirmed with immunocytochemistry and differentiation assays. The harvested BMSCs were found to be vimentin+, CD90+, and CD45- (Figure 1e-g). The mesenchymal lineage of the rat BMSCs was confirmed by their ability to differentiate readily into adipocytes and osteoblasts  (Figure 1h-j).
Previous studies within the group showed that labeling with IO-TAT-FITC does not affect the proliferation or differentiation of BMSCs, nor did it induce apoptosis (data not shown).
Two groups of animals were stereotactically implanted with either eNCSCs or BMSCs (50,000 cells in 5 μl) onto the corpus callosum in the right hemisphere. Both implanted cell types remained visible as an MRI hypointense region for at least 30 days (Figure (Figure3).3). The cells displayed some lateral and posterior migration away from the injection site along the white-matter tract of the corpus callosum The average lateral spatial distribution measured on MR images for eNCSCs and BMSCs was 0.92 ± 0.36 mm (mean ± SEM) and 1.04 ± 0.11 mm (mean ± SEM), respectively, and this appeared to be spread equally on either side of the injection site. This indicates that the corpus callosum environment does not impose any inherent directionality on the migration of these implanted cells. Previous studies within the group have shown that either implanted labeled dead cells or free iron-oxide nanoparticles are cleared away by the local environment within 30 days, leaving little residual MRI signal void (see Supplementary data 1 in Additional file 1). This suggests that our detection of signal void, of more than 30 days after implantation in the current experiments, most likely represents surviving, live, transplanted cells.
Postmortem histology confirmed the persistence of the implanted FITC+ cells and was anatomically consistent with the MR images (Figure (Figure3a).3a). After direct implantation onto the corpus callosum, the FITC+ eNCSCs were seen to have been distributed longitudinally at a distance of approximately 450 μm (Figure (Figure3c).3c). To determine whether any of the transplanted stem cells had differentiated along the neuroglial lineage, the brain sections were immunostained with glial and neural specific antibodies. Limited GFAP+ differentiation of FITC+ cells (Figure (Figure3b)3b) was noted, but no staining for FITC+/βIII-tubulin (not shown); that is, no neuronal differentiation was detected. Moreover, the FITC + implanted eNCSCs showed no evidence of S-100 differentiation (a marker of mature Schwann cells) (Figure (Figure3d).3d). The data are therefore consistent with eNCSC differentiation along a glial pathway, but only to immature nonmyelinating Schwann cells.
The LPS lesion appeared as a hyperintense signal void on a T2*- weighted MR image and led to a demyelination confirmed by absence of Luxol Blue staining (Figure (Figure4).4). Immediately after injection of LPS, animals were stereotactically implanted with 50,000 IO-TAT-FITC labeled cells (five rats with eNCSCs, three rats with BMSCs). The site of implantation was located 3 mm distally (but a greater distance along the curve of the corpus callosum) from the LPS lesion. In vivo MRI imaging at various intervals after implantation demonstrated that both cell types migrated along the white-matter tract of the corpus callosum preferentially toward the LPS lesion, thus demonstrating pathotropic cellular behavior (Figure (Figure5).5). No evidence was found of cells continuing to migrate beyond the lesion or migrating into the contralateral hemisphere. MR signal void, due to an influx of IO-labeled cells, could be detected in the lesion site for up to 28 days with eNCSCs and for up to 94 days for the BMSCs.
To confirm the differential MR relaxation properties induced by the labeled cells at both the injection and lesion sites compared with the surrounding tissue, a number of varying T2 relaxation values were determined. The T2 values of different brain regions were determined from the T2 maps, generated by varying the echo time (TE) during the MR imaging. It was found that cells at the injection site (26.1 ± 6.3; mean ± SD) and the lesion site (27.3 ± 1.7; mean ± SD) had similar T2 values, but these were lower than either the corpus callosum (34.0 ± 1.4; mean ± SD) or the striatum (45.0 ± 3.8; mean ± SD), thus allowing the cells to be discriminated from the surrounding tissue on MR images thus further confirming migration of the cells toward the lesion from the implantation site (see Supplementary data 2 in Additional file 2).
Postmortem histology of FITC labeling confirmed the MR data that implanted cells had migrated along the corpus callosum to the lesion site (Figure (Figure5).5). Some eNCSCs were still present at the injection site, and of those cells that had migrated, some exhibited GFAP immunoreactivity, indicating glial differentiation. Around 20% of FITC+ cells were also IB4+ (a microglia/macrophage marker). However, it is unclear whether this represents: differentiation of cells into microglia, engulfment of live cells, dead cells, or of released IO-TAT-FITC nanoparticles. Nevertheless, the remaining population of FITC+ cells were not colocalized with IB4, indicating that the signal void was not from incidental labeling of microglia.
Having demonstrated that CNS-implanted stem cells migrate to a local inflammatory lesion, it was important to extend these studies to determine whether a less-invasive route for delivery of stem cells toward a central lesion site was feasible. Therefore, 50,000 cells were injected intravenously via the tail vein to assess their migrational potential from the peripheral vasculature to a LPS lesion in the brain.
Within 24 hours after intravenous administration of stem cells, a MR signal void developed at the site of the LPS injection/lesion (Figure (Figure6).6). This signal void became more defined over the following 8-day period (Figure (Figure66).
Animals were killed 10 days after administration of the IO-TAT-FITC-labeled cells. In one animal, the number of IO-TAT-FITC+ cells, on alternate tissue sections (to reduce the possibility of double counting), was counted at the LPS-lesion site. It was estimated that approximately 4,000 of 50,000 cells administered intravenously had homed to the LPS-lesioned area from the peripheral vasculature, thus representing 8% of the total eNCSCs injected. Furthermore, the cells were found to have spread along the corpus callosum (Figure (Figure66).
The FITC+ BMSCs also were found to be distributed throughout the right corpus callosum over a distance of 3.6 mm around the LPS-demyelinated lesion area. An issue with cell-implantation studies is whether the MRI reports on either nanoparticle-labeled cells or free IO-TAT-FITC nanoparticles released on cell death and subsequently engulfed by resident microglia or transient macrophages, which then migrated to the lesion. Isolectin-B4 staining indicated that a small proportion (about 20%) of the cells were double positive for both FITC and IB4. However, most FITC+ cells were IB4-, suggesting that the majority of cells within the lesion site were the peripherally transplanted stem cells that had migrated to the lesion from the circulation.
Increasing clinical interest exists in the use of transplantable stem cells as a means of repairing neurodegenerative disease or for gene delivery. The success of such approaches will be dependent on not only the source of donor stem cells and their expansion in vitro, but also their mode of delivery, where localized surgical delivery to the brain carries inherent risks of morbidity. Studies have begun to evaluate the clinical efficacy of using intravenously administered bone marrow stem cells in diseases such as spinal cord injury . This study demonstrates that MRI is a useful technique that allows longitudinal noninvasive monitoring of stem cell migration in the brains of individual animals, giving important information on cell dynamics and interactions with the host CNS.
Implanted eNCSCs or BMSCs were visible as a hypointense region in T2 MRI images, allowing them to be tracked as they migrated within the brain. Implanted cells remained visible at the lesion site by MRI for the duration of the experiment (up to 13 weeks). Stem cells implanted directly into the brain were found to migrate preferentially along the major white matter tracts in both healthy and lesioned animals. In animals with a focal inflammatory lesion, the transplanted cells displayed unidirectional pathotropic migration to the lesion, where they ceased migrating and remained visible on MRI for several months. Moreover, and of potential benefit for clinical applications, both cell types similarly displayed migration to a focal inflammatory brain lesion from the peripheral vasculature.
Several studies have demonstrated the migration of stem cells after intravenous administration in models of neurodegeneration [19-22]. However, those models involved cerebral ischemia and compression injury, which result in a more severe lesion. Our study has shown that relatively minor, focal lesions provide sufficient cues to attract stem cells from the peripheral vasculature. Our LPS-lesion model induces a focal demyelination, resulting in an influx of microglia; such lesions have been shown to stimulate the release of cytokines such as IL-1β, TNF, and IL-6 , which may have provided the chemoattractant signals for eNCSCs and BMSCs. The migration of transplanted stem cells through the brain parenchyma may also be aided by their secretion of matrix metalloproteases (MMPs), because BMSCs require MMP1 to migrate toward human gliomas . Because no donor cells could be detected in other regions of the brain, this suggests that the cells were not simply trapped within the cerebral blood vessels, but were responding specifically to chemotactic factors released from the lesion. It has been reported that eNCSCs are not migratory when transplanted into the lesioned spinal cord , whereas our work shows that eNCSCs have homing properties similar to those of BMSCs and invade brain lesion from the peripheral vasculature. This suggests that the local CNS environment may have an important effect in regulating NCSC attraction and invasion, possibly by altering the expression of NCSC chemokine receptors or proteases essential for cell migration.
Although the intravenous administration route has obvious clinical advantages, we found that one challenge of using this route will be to get sufficient cells to the lesion for therapeutic benefit. Thus, we estimate that only about 8% of the intravenously injected stem cells migrated to the LPS lesion. By contrast, more than 10 times this number of stem cells reached the lesion site after intracranial administration some 3 mm from the lesion site. It will be of interest to determine whether other vascular routes, such as the carotid artery, might increase the proportion of injected stem cells that enter the brain-lesion site. It will also be of interest to examine whether stem-cell engraftment can be maximized by changing the postlesion timing of cell delivery. Any delay in delivery, sufficient to permit the in vitro expansion of autologous stem cells, would obviously be desirable from a practical and clinical perspective.
Concerning the fate of the administered stem cells, we found that BMSCs and eNCSCs were able to adopt glial fates in the brain, although we did not detect stem cell-derived neurons. A previous study demonstrated that BMSCs have the ability to differentiate into astrocyte-like and oligodendrocyte-like cells after implantation into an ischemic lesion . A separate study, by using eNCSCs in a in rat spinal cord crush lesion model, detected limited S-100 differentiation of implanted eNCSCs, indicative of mature Schwann cells . We did not detect S-100 differentiation of the implanted eNCSCs in our focal LPS-lesion model, although several implanted cells expressed GFAP, an early marker of glial differentiation for both astrocytes and immature Schwann cells . It remains unclear whether, had the experiment been allowed to proceed for a longer period, the implanted eNCSCs in our model would eventually mature into myelinating Schwann cells.
Previous studies within the group have shown that dead cells, prelabeled with IO-TAT-FITC, are cleared away from the local area and do not contribute to a signal void (see Supplementary data 1 in Additional file 1). In addition, and consistent with this study, previous studies using live stem cells have shown that whereas a few of the cells are engulfed by IB4+ microglia, the majority remain nonphagocytosed after BMSC implantations into a rodent model of Parkinson disease .
In summary, this study has shown by using a noninvasive longitudinal in vivo imaging modality, that two stem-cell types, with the potential for autologous cell therapy and gene targeting in CNS injury and neurodegenerative diseases, have pathotropic properties in a focal demyelinating brain lesion when they are administered by either the intracerebral or the intravenous routes. Moreover, this work reinforces that intravenous delivery is a viable clinical option for the delivery of cell-based therapies, with obvious clinical advantages over direct CNS injection.
BMSC: bone marrow stem cell; DMEM: Dulbecco modified Eagle medium; DRG: dorsal root ganglion; eNCCs: epidermal neural crest cells; FCS: fetal calf serum; GFAP: glial-fibrillary acidic protein; HSC: hematopoietic stem cell; IB4: isolectin B4; IO-TAT-FITC: iron oxide transactivator of transcription fluorescein isothiocyanate; LPS: lipopolysaccharide; MRI: magnetic resonance imaging; MSC: mesenchymal stem cell; NCC: neural crest cell; TE: echo time.
The authors declare that they have no competing interests.
JJ, JG, and KB designed the study. JG and JJ carried out the in vitro cell work. JJ carried out the in vivo work. CC designed and developed the MR imaging. WJ designed and synthesized the iron oxide nanoparticles. All authors contributed to and approved the manuscript.
Signal void after cell implantation. Live (arrows) and dead (arrowheads) BMSCs were injected into the right and left striata, respectively. The signal void from the live cells remained for 53 days with little remaining signal void from the implanted dead cells.
Signal-intensity decay and map of T2 values in the rat brain. (a) Signal-intensity decay of different regions of interest (ROIs) at different TEs, showing the different MR-relaxivity properties of different brain regions at 14 days after the lesion and after cell implantation. Map of T2 values (ms) within the rat brain. (b) Because of the superparamagnetic properties of iron oxide particles, labeled cells induced a decrease of T2 value at the site of implantation (arrow 1), and at the LPS lesion site (arrow 2).
This work was funded by the Medical Research Council of Great Britain.
Thanks to Karen Evans and Tina Wardhaugh for technical assistance.