Evaluating regional blood spinal cord barrier dysfunction following spinal cord injury using longitudinal dynamic contrast-enhanced MRI
© Tatar et al; licensee BioMed Central Ltd. 2009
Received: 07 December 2008
Accepted: 11 June 2009
Published: 11 June 2009
In vivo preclinical imaging of spinal cord injury (SCI) in rodent models provides clinically relevant information in translational research. This paper uses multimodal magnetic resonance imaging (MRI) to investigate neurovascular pathology and changes in blood spinal cord barrier (BSCB) permeability following SCI in a mouse model of SCI.
C57BL/6 female mice (n = 5) were subjected to contusive injury at the thoracic T11 level and scanned on post injury days 1 and 3 using anatomical, dynamic contrast-enhanced (DCE-MRI) and diffusion tensor imaging (DTI). The injured cords were evaluated postmortem with histopathological stains specific to neurovascular changes. A computational model was implemented to map local changes in barrier function from the contrast enhancement. The area and volume of spinal cord tissue with dysfunctional barrier were determined using semi-automatic segmentation.
Quantitative maps derived from the acquired DCE-MRI data depicted the degree of BSCB permeability variations in injured spinal cords. At the injury sites, the damaged barriers occupied about 70% of the total cross section and 48% of the total volume on day 1, but the corresponding measurements were reduced to 55% and 25%, respectively on day 3. These changes implied spatio-temporal remodeling of microvasculature and its architecture in injured SC. Diffusion computations included longitudinal and transverse diffusivities and fractional anisotropy index. Comparison of permeability and diffusion measurements indicated regions of injured cords with dysfunctional barriers had structural changes in the form of greater axonal loss and demyelination, as supported by histopathologic assessments.
The results from this study collectively demonstrated the feasibility of quantitatively mapping regional BSCB dysfunction in injured cord in mouse and obtaining complementary information about its structural integrity using in vivo DCE-MRI and DTI protocols. This capability is expected to play an important role in characterizing the neurovascular changes and reorganization following SCI in longitudinal preclinical experiments, but with potential clinical implications.
Damage to blood-spinal cord barrier (BSCB) occurs as a consequence of mechanical insult to spinal cord (SC) . The damaged barrier becomes permeable to blood constituents, inflammatory cells and other large molecules, which collectively activate a cascade of secondary processes harmful to the underlying tissue. With time, vascular bed of the injured SC goes through repair and remodeling . Providing nutrition and preventing extravasation of destructive biochemical compounds in blood protect the remaining neurons and maintain the existing substrate from further degeneration. At the same time, knowledge of barrier properties and its status is essential if potential intravascular drugs with capabilities to improve neurovascular protection and to promote repair and recovery will be administered. Such treatment is possible provided that the drugs can pass through the open barriers to reach the destined regions in the SC parenchyma. Therefore, a complete understanding of the vascular response to spinal cord injury (SCI) is required for developing intervention strategies aimed at rapidly restoring the barrier integrity as well as blood supply to the ischemic areas of the traumatized cord.
So far, BSCB permeability changes in injured SC have been evaluated using a range of tracers and laborious postmortem tissue analysis . Alternatively, in vivo dynamic contrast-enhanced MRI (DCE-MRI) was proposed to noninvasively visualize and quantify the changes in BSCB permeability in a relatively more efficient way [4–6]. The initial DCE-MRI studies were performed using a rat animal model of SCI. Lately, the availability of diverse strains and transgenic varieties has made the mouse a more attractive model [7–10]. But, to date, DCE-MRI studies on mouse are lacking. The first goal of this paper is to demonstrate the feasibility of performing DCE-MRI on mouse with SCI.
The contrast enhanced data in previous rat studies were acquired dynamically over an extended period of time and processed using a pharmacokinetic model with complicated numerical computation routine. The end results from the computation included quantitative measurements that represented the overall exchange of contrast agent between plasma and lesion. Such representation was useful, but yielded limited information, since in practice, rather than global evaluation, more detailed local variations in BSCB permeability was sought after. In this previous approach, the DCE-MRI data acquisition time was long since it required covering both the wash-in and wash-out phases of the contrast agent. Another weakness was that the parameters were estimated using a time-inefficient computation algorithm. Thus, the second goal of this study is to provide an improved method in terms of data collection, post processing and spatial representation of the BSCB permeability variations in injured SC.
Histological studies have demonstrated that, in injured SC, the areas with damaged vasculature overlap with the areas of intense neuronal loss [11, 12]. Noninvasive diffusion tensor imaging (DTI) provides information about the neuronal integrity in underlying SC tissue [13, 14]. Combining these, it is likely that in vivo BSCB permeability and DTI-based measurements, both obtained from the same region of the injured SC, can provide relevant information about the viability of underlying neurovasculature, which has so far only been available by performing ex vivo histological analysis. Therefore, the third goal of this study is to compare the BSCB permeability and DTI measurements and investigate the nature of their association while assessing the neurovascular response in SCI.
Studies based on postmortem tissue analysis suggest that the first 72 hours following SCI are the most critical, offering a window of opportunity for potential treatments [15–18]. In order to develop effective therapeutic strategies in experimental studies, it is important to employ a SCI model that sensitively responds to the treatment at the acute phase of the injury and is also capable of producing measurable vascular and neuropathological changes within the first 72 hr time frame. Therefore, this study focused on the acute phase (postinjury days 1 and 3) of the injury with the above pathological properties and investigated the injured cords using multimodal neuroimaging (anatomical, DCE-MRI and DTI) noninvasively. In the following, we first describe our imaging protocols, and then give details of our implementation and basis of our data processing algorithm and strategies. Next, using these developments, we present results from neuropathological evaluations and generate reliable BSCB permeability maps to show the spatiotemporal course of the alterations in vascular permeability within the SC lesion and its surroundings. We characterize the area and volume of the regions with dysfunctional BSCB. We also test the BSCB permeability estimates against the DTI measurements from the corresponding regions to establish the level of association as determined from statistical analysis.
All experiments were carried out with twelve-week old female C57BL/6 mice (n = 5) in accordance with a protocol approved by the Institutional Animal Care and Use Committee. All of the mice were subjected to SCI and participated in the MRI scans using DCE-MRI and DTI protocols on postinjury days 1 and 3.
Procedures for surgeries and spinal cord injury
All surgeries were performed in sterile conditions. The mouse was initially anesthetized by a spontaneous inhalation of 4% isoflurane in an induction chamber and then moved to a surgery mat. The anesthesia level was reduced to 2% isoflurane delivered in a mixture of 40% oxygen and 58% air through a nose mask. Further adjustments in small increments were made on the percentage of the isoflurane level during the surgery. For intravascular delivery of the paramagnetic contrast agent with MW = 938 Da (Magnevist, Berlex Imaging, Wayne, NJ) in DCE-MRI studies, animals underwent additional jugular vein catheterization with PE-10 tubing . The catheter ran subcutaneously and exited the skin at the back between shoulder blades, then was kept folded behind the animal. The catheter was flushed with heparin daily to prevent clotting. The surgical procedures for inducing SCI involved a midline incision posterior from the thoracic levels T10 to T12, followed by dissection of the bilateral vertebral muscles to expose the dorsal laminae and spinous processes. Laminectomy was performed at the T11 level to expose the SC by exercising special care not to damage the dura mater. The spinous processes at T10 and T12 adjacent to the laminectomy were stabilized using two hemostatic forceps. A 1-mm diameter injury bit, that was attached to a generic central nervous system injury device described earlier , was positioned perpendicular to the dorsal surface of the SC. The device consists of electromechanical components – a linear motor connected to a controller. The controller communicated with a personal computer through a software program developed in our laboratory to input biomechanical parameter values for inducing a contusion-type SCI. The injury parameters used in these experiments were: impact velocity of 0.75 m/s; surface displacement depth of 0.5 mm; and compression duration of 85 ms. After the injury, the overlying muscle layers were sutured and skin was closed tightly. Then, the injured mouse was left to recover in a heated cage and received postoperative care.
Each injured mouse was scanned on days 1 and 3 using a 9.4 T horizontal INOVA Varian system (Varian, Palo Alto, CA) and an inductively coupled surface coil . The scan was performed when the mouse was under a general anesthesia which was delivered as a mixture of 2% isoflurane, 40% oxygen and 58% air through a nose mask. Vital signs (respiration, heart rate and body temperature) of the anesthetized animal were monitored using a MRI-compatible monitoring and gating system (Model 1025, SA Instruments Inc., Stony Brook, NY). Respiratory-gated acquisition was used to increase the image quality by minimizing breathing related image artifacts.
High-resolution anatomical images on all animals were first acquired in sagittal and axial views using a spin-echo sequence in multislice and interleaved fashion. The scan parameters for the sagittal or horizontal images were TR/TE = 2500/12 ms, field-of-view (FOV) = 26 × 8 mm2, matrix = 256 × 128, in-plane pixel resolution = 100 × 63 μm, slice thickness = 0.5 mm, number of excitations (NEX) = 2. The corresponding parameters for the axial images were TR/TE = 2500/12 ms, FOV = 12 × 8 mm2, matrix = 128 × 128, in-plane pixel resolution = 94 × 63 μm, slice thickness = 1 mm, number of slices = 14 and NEX = 2. These data constituted the proton density (PD) weighted images.
Then, for microstructural imaging, diffusion weighted images were acquired using diffusion gradient strength = 80 mT/m, width (δ) = 6.5 ms and separation (Δ) = 11 ms to produce a b-value of 534 s/mm2. The imaging parameters for these scans were TR/TE = 2000/26 ms, FOV = 12 × 8 mm2, image matrix = 128 × 128, in-plane pixel resolution = 94 × 63 μm, slice thickness = 1 mm and NEX = 2 [20–22]. Baseline data acquired in the absence of the diffusion weighting constituted the T2-weighted images.
Next, for evaluating microvascular response and imaging BSCB permeability to the contrast agent in the injured animal, a DCE-MRI protocol was applied . The contrast agent was delivered as a bolus (< 5 s) at a dose of 0.1 mmol/kg while the animal was still in the scanner. To detect the contrast enhancement, T1-weighted axial images were acquired precontrast and repetitively for up to 2 hr postcontrast using the same parameters as the PD weighted images but with TR = 1000 ms and NEX = 4. The temporal resolution between these acquisitions was 10 min.
Quantitative MRI data analysis
The MRI data were acquired and visualized using the scanner's control software VNMRJ (Varian, Palo Alto, CA).
The DCE-MRI data were analyzed off-line using custom-written software in Matlab (The Mathworks, Inc., Natick, MA). Axial images acquired before and after the contrast enhancement in a given scanning session were loaded into computer and processed interactively using a graphical user interface. The details of the performed numerical analysis are described in Appendix. The results are 2-D maps that quantitatively describe the BSCB permeability (denoted by the parameter K p-sc ) throughout the injured SC.
Area and volume of dysfunctional BSCB in injured SC
By analyzing the spatial distribution of the permeability changes on K p-sc maps, we measured the area and volume of the injured SC tissue with damaged BSCB. To perform the area measurements, a threshold value was required to differentiate the elevated K p-sc values from the background noise. The value of this threshold was determined while postprocessing the data. To accomplish this task, an algorithm was implemented using the theory of signal detection in the presence of additive noise. The procedure involved first computing histograms of K p-sc maps from two normal sections of the injured cord, but within the masks of the corresponding slices at 4 mm caudal and rostral to the injury epicenter. Because BSCB in these regions were intact, the contrast agent was retained within the SC vasculature and no detectable leakage took place. These histograms depicted K p-sc estimates that were normally distributed around zero, which could be fitted to zero mean Gaussian profiles (please see the results section). The larger standard deviation σ from the two Gaussian fits (from a caudal and a rostral slice) was used to set a threshold value for K p-sc at +2σ . This selection was based on the property that the Gaussian distribution between -2σ and +2σ equals to nearly 95% of the total area beneath the curve. This meant that nearly 97.5% of the pixels in the K p-sc map from a normal SC were below the threshold and therefore considered to have intact BSCB. The same threshold value was employed for analyzing the K p-sc maps produced for all the remaining slices. The histograms from slices near the injury epicenter were observed to be shifted towards higher K p-sc values, as expected, reflecting the presence of compromised BSCB. These histograms had wider spread but still followed the profile of Gaussian distribution.
The number of pixels whose intensity values on the K p-sc maps remained above the threshold was counted to determine the area of the SC with compromised BSCB in a given slice. This number was further divided by the total cross sectional area of the cord in that slice to obtain a measure of normalized area (NA). The slice with largest pixel count was considered as representing the injury epicenter. The volume of the compromised BSCB was determined by summing the areas (prior to normalization) in six neighboring slices covering the epicenter. Total cord volume was similarly calculated from the total cord area in each slice. The total volume with compromised BSCB was scaled by the total SC volume to obtain normalized volume (NV). This normalization of the area and volume measurements compensated for the variations from slice to slice and animal to animal, as well as other spatial scales, such as changes in slice thickness and pixel dimensions.
In addition, K p-sc measurements remaining above threshold within the total area at the epicenter slice were averaged for each animal. The resulting averages for day 1 and day 3 were then correlated with the corresponding mean DTI measurements within the same area, as explained below.
Diffusion-weighted images were processed and the elements of diffusion tensor were estimated for each image voxel using the scanner software VNMRJ (Varian Inc., Palo Alto, CA). The diffusion tensor represents the statistical distribution of microscopic motion of water molecules, and its three eigenvalues (λ1, λ2 and λ3) characterize the principal water diffusivities along its three orthogonal eigenvectors [21, 23, 24]. To be consistent with the nomenclature used in previous reports, we denoted λ1 = λ|| as an expression of longitudinal diffusivity of water molecules along the axonal fibers, and λ⊥ = (λ2+λ3)/2 as an expression of transverse diffusivity for water moving perpendicular to the direction of neuronal fibers in SC. The fractional anisotropy (FA) index was computed algebraically by combining the eigenvalues. FA index is a rotationally invariant scalar and quantitatively characterizes the degree of anisotropy in the diffusion properties of the underlying tissue within the voxel. The parameters λ1, λ⊥ and FA were estimated for each voxel throughout the slice at the epicenter and the corresponding maps were generated in 2-D. Similar to computing mean K p-sc values described above, λ||, λ⊥ and FA measurements from the areas with compromised BSCB at the epicenter were averaged and the resulting mean values for each animal were recorded in a database along with the corresponding mean K p-sc . Group mean and standard deviation of these measurements were again computed for days 1 and 3 separately.
Postmortem tissue analysis
Neurovascular histopathologies of selected injured SCs were examined postmortem following MRI scan on day 3. Each mouse was euthanized by intracardiac perfusion with 50 mL of phosphate buffered saline (PBS) solution, followed by 50 mL of 4% formaldehyde PBS solution that were delivered through a 23-gauge needle connected to a perfusion pump. The SC was excised and fixed in 4% formaldehyde. Segments from the injury epicenter or normal levels were embedded in paraffin and cut serially in 10 μm thick sections. Representative samples were stained with standard hematoxylin and eosin (H&E), luxol fast blue (LFB), vascular endothelial marker (CD34) or neuron specific enolase (NSE) for histopathological assessment of the neurovascular pathological changes. Immunohistochemistry (IHC) was carried out with CD34 (MY 10 clone, BD Bioscience, Franklin Lakes, NJ) (1:100 dilution) and NSE (BBS/NC/VI-H14 clone, Dako Cytomation, Carpinteria, CA) antibodies using a Dako cytomation autostainer . Briefly, the slides were de-paraffinized by incubation in xylene and ascending grades of alcohol. Antigen retrieval for CD34 was done by incubation with proteinase Kinase at room temperature for 5 minutes. Antigen retrieval for NSE was done by heating in ethylene diamine tetraacetic acid (EDTA), PH 9.0 buffer (Lab vision, Fremont, CA) at 95°C for 20 min. Both sections were loaded in the autostainer programmed as follows: 3% hydrogen peroxide for 10 minutes, blocked with 5% skimmed milk for 5 min, incubated with primary antibody for 30 min, followed by incubation with Envision+ system HRP (Dako Cytomation, Carpinteria, CA) for 30 minutes. Color was developed by incubating samples with diaminobenzidine (DAB)+chromogin for 10 min followed by Dako DAB enhancer for 5 min. Hematoxylin was used as counter stain. The sections were examined using a BX 50 Olympus microscope and the photographs were taken with an attached Olympus DP 70 camera operated with DP Controller software (Olympus Corporation, Center Valley, PA). One section was also incubated with secondary antibody only to check nonspecific binding.
The quantitative data collected from the measurements were analyzed statistically. The NA, NV, K p-sc , λ||, λ⊥ and FA values gathered from each animal were listed in two groups as day 1 and day 3, and the means and standard deviations within each group were computed for each parameter to understand the intra-group variations. The measurements between day 1 and 3 were compared using the paired Student's t test. This analysis allowed examination of inter-group variations and the determination of the statistical significance of the differences. Statistical significance was defined at P < 0.05. Also, statistical dependencies between K p-sc , and measurements λ||, λ⊥ and FA were determined using Pearson's correlation analysis and the resulting correlation coefficients were reported.
The surgical procedures, injuries, and prolonged anesthesia during MRI scans were well tolerated by all mice. For imaging, each mouse was carefully placed supine over an inductively coupled radio frequency coil system to achieve an optimal tuning and matching condition as observed in the frequency response of the coil impedance. When the animal was placed in the magnet, the catheter attached to it was extended outside at the front end of the magnet bore. The injured cord was then imaged in transverse and rostral-caudal planes. Acquiring data from different orientations allowed better evaluation of the lesion's spatial extent.
The postcontrast sagittal images in the figure were acquired 130 min and those in the horizontal views were acquired 140 min after the delivery of the contrast agent. Following its delivery, the contrast agent diffuses passively in the extravascular spaces of the injured SC parenchyma. This leads to the brightness enhancement spreading along the cord in both rostral and caudal directions, as evident in the figure.
For the data analysis, images (precontrast and first postcontrast) from a given slice location were displayed simultaneously. Image alignment was verified visually by zooming in on anatomical landmarks. Two out of the ten DCE-MRI scans exhibited spatial misalignment between the axial postcontrast and the corresponding precontrast images. In these cases, the sedated mouse reacts to the contrast agent, causing its body to move slightly. From the evaluation of the images, it was evident that the image motions in the misaligned data sets were translational in both cases, but a slight rotation was present in one of them. Neither of the motions was of deformation type. The two misaligned images were registered using a simple postprocessing technique with Matlab's "circshift" and "rotate" functions. A more complicated automated algorithm for image registration chould have been used for the registration. But this required complex implementation, which was beyond the scope of the study.
Figure 9 shows LFB, NSE and CD34 stained slices showing the injury and a normal cord section. At the injury, the LFB and NSE stains depicted diffuse demyelination and completely disorganized neurons and processes. The CD34 stain from the same areas showed damaged vasculature with leaky barrier. In the rostral segment, however, LFB and NSE stains indicated normal myelination and intact neurons, and CD34 stain showed vasculature with intact barrier.
BSCB permeability and microstructural measurements on day 1 and day 3 (mean ± standard deviation). P values for the measurements between day 1 and 3 are given in the last row.
K p-sc (min-1)
λ|| (×10-3 mm2/s)
λ⊥ (×10-3 mm2/s)
0.123 ± 0.008
0.788 ± 0.022
0.579 ± 0.016
0.183 ± 0.025
0.076 ± 0.006
0.694 ± 0.026
0.604 ± 0.015
0.097 ± 0.021
Pearson's correlation coefficient results between the BSCB permeability and microstructural measurements on day 1 and day 3.
ρ(K p-sc , λ||)
ρ(K p-sc ,λ⊥)
ρ(K p-sc , FA)
Our MRI-based data, as in Figures 3, 4 and 5, and histological analysis, as in Figures 7, 8 and 9, demonstrated the dynamic remodeling of the BSCB as part of the ongoing repair and recovery processes in the injured SC tissue. Using postmortem analysis in mouse, Whetstone et al.  reported that SCI results in a biphasic, temporal pattern of barrier leakage to tracer – luciferase. In their study, the barrier leakage was shown to extend beyond the epicenter into segments that were within 6 mm rostral and caudal to the epicenter. The leakage was seen to be mostly pronounced within the first 35 min after the injury followed by a gradual decline within the first 24 hr. A second peak of abnormal barrier permeability was reported at 3 days after the injury, which significantly exceeded that observed at 24 hr. Regarding the barrier permeability to the contrast agent, we obtained comparable results that showed stronger intensity enhancement on day 3 than day 1. This agreement is encouraging and warrants further exploration, such as investigation of the loss of blood vessels and revascularization in injured mouse SC using DCE-MRI in conjunction with MR angiography modality [5, 32, 40].
Requiring only the initial portion of the intensity enhancement to assess barrier function offers benefits in terms of reducing the imaging time substantially. In the current study, we acquired T1-weighted images using a spin-echo sequence which required relatively long acquisition time. This is one limitation of the approach. Higher temporal resolution can be achieved between the precontrast and postconrast acquisitions by employing faster imaging sequences. Such ability should further improve the time and accuracy of estimating the barrier permeability. For this purpose, echo-planar imaging appears promising .
From the application point of view, providing information about the barrier function should be useful in at least three circumstances. One situation is in characterizing the SCI model where the resulting barrier leakage in a particular SCI model may be another parameter to be defined, and referred back when needed to check against the consistency of the newly induced injuries. This would enable the confirmation of whether later injuries have similar properties in terms of the vascular response. Traditional histological analysis was employed to understand the sensitivity and specificity of the barrier damage to graded mechanical perturbations . Our approach offers an efficient alternative and may become a preferred choice for such purpose. In the second case, quantitatively evaluating the severity of the barrier damage as soon as possible after the injury may provide early indications of the significance and level of the expected secondary processes that are likely to increase neuronal loss. Such capability can have significant prognostic value. Figure 13 and comparative analysis in Tables 1 and 2 clearly provided evidence that correlations exist between DCE-MRI and DTI based measurements. This has important implications in practice, especially when the examined SCI produces poor quality of DTI acquisition or the analysis of the resulting data is not feasible. In such challenging situations, including the DCE-MRI protocol in the scan may supply information on the condition of the vasculature, which may indirectly help to determine the level of neuronal damage in the underlying SC tissue by using the close associations demonstrated in Table 2. Lastly, monitoring the barrier function may have important implications in predicting the efficacy of targeted drug or gene delivery through the permeable barriers when potential therapeutic interventions are considered. While this aspect is foreseeably achievable if the drug or transfection vector has molecular weight comparable to that of the contrast agent used in this study, it remains to be seen if the approach would be viable in cases when the drug or gene has significantly larger size.
This study has demonstrated the potential of DCE-MRI method to assess the BSCB dysfunction in injured spinal cord noninvasively. The method involved acquiring only two T1-weighted images; precontrast and postcontrast, acquired with a minimum time delay following the injection of contrast agent. This simple data acquisition strategy provides sufficient temporal information on the contrast-enhancement that was necessary to map the spatial distribution of BSCB permeability. The BSCB dysfunction correlated strongly with the degree of axonal loss and demyelination. The relationship between the vascular damage and neuronal loss in injured SC has been well-established previously, but by using histological techniques. Reconfirming this association using DCE-MRI and DTI data acquired from living animals has important implications in translational research. Preclinical efforts are currently focused on developing BSCB permeable drugs for improving neurovascular function by repairing vascular network, delaying neurodegenerative processes or promoting neuronal recovery. Research efforts are also underway for understanding the role of specific genes in vascular reorganization, neuronal repair and recovery from an injury on experimental test systems involving different strains of "transgenic" or gene knock-out mice. On the basis of multiple neuroimaging methodologies developed in this study, scanning the same animal model with anatomical, DCE-MRI and DTI protocols provides measurable parameters that can serve as sensitive and specific in vivo neurovascular biomarkers for comprehensively evaluating the pathological state of the injured SC, may offer a prognostic value for functional recovery from SCI and potentially serve as a monitoring tool for evaluating the efficacy of a treatment efficacy.
Here, I(t = 0, x, y, z) and I(t, x, y, z) represent intensities in the precontrast and t th postcontrast images of a given slice z, respectively. The mask Mask(z) was obtained by using manual segmentation applied on the postcontrast images where the SC was delineated best. The mask covered the cord but excluded cerebrospinal fluid, which also exhibited postcontrast enhancement. The total cross-sectional area of the SC at that particular slice was measured by the area covered by the mask.
Here, T 10 denotes relaxation time in second (s) before administering the contrast agent and r 1 is relaxivity introduced by the contrast agent to that of the underlying SC tissue and expressed in mM -1 s -1. For mice scanned at 9.4 T, T 10 was reported to be 1730 ms for the gray and 1690 ms for the white matters of the SC , but r 1 associated with the contrast agent for these tissue types has yet to be determined.
This equation indicates that the initial slope of REI provides a measurable quantity representing the BSCB permeability at a spatial location (x, y, z). Specifically, numerical computation of Eq.  involves discrete derivative operation for t = 0 and ΔT = 10 min – the temporal resolution in our DCE-MRI acquisitions. By noticing that RIE (t = 0, x, y, z) = 0, the derivative operation can be simplified further. In this study, was calculated for each x, y ∈ Mask(z) and the results were put together to form a 2-D quantitative K p-sc map delineating the regions of the injured SC with compromised BSCB permeability for each slice.
This work was funded in part by NIH grants NS052610 and NS054019. The authors thank Dr. Fan Yang for helping with animal surgeries and care.
- Tator CH, Koyanagi I: Vascular mechanisms in the pathophysiology of human spinal cord injury. J Neurosurg. 1997, 86: 483-492. 10.3171/jns.1997.86.3.0483.View ArticlePubMedGoogle Scholar
- Whetstone WD, Hsu JY, Eisenberg M, Werb Z, Noble-Haeusslein LJ: Blood-spinal cord barrier after spinal cord injury: relation to revascularization and wound healing. J Neurosci Res. 2003, 74: 227-239. 10.1002/jnr.10759.View ArticlePubMedPubMed CentralGoogle Scholar
- Maikos JT, Shreiber DI: Immediate damage to the blood-spinal cord barrier due to mechanical trauma. J Neurotrauma. 2007, 24: 492-507. 10.1089/neu.2006.0149.View ArticlePubMedGoogle Scholar
- Bilgen M, Narayana PA: A pharmacokinetic model for quantitative evaluation of spinal cord injury with dynamic contrast-enhanced magnetic resonance imaging. Magn Reson Med. 2001, 46: 1099-1106. 10.1002/mrm.1305.View ArticlePubMedGoogle Scholar
- Bilgen M, Abbe R, Narayana PA: Dynamic contrast-enhanced MRI of experimental spinal cord injury: in vivo serial studies. Magn Reson Med. 2001, 45: 614-622. 10.1002/mrm.1083.View ArticlePubMedGoogle Scholar
- Bilgen M, Dogan B, Narayana P: In vivo assessment of blood-spinal cord barrier permeability: serial dynamic contrast enhanced MRI of spinal cord injury. Magn Reson Imaging. 2002, 20: 337-10.1016/S0730-725X(02)00504-0.View ArticlePubMedGoogle Scholar
- Guertin PA: Paraplegic mice are leading to new advances in spinal cord injury research. Spinal Cord. 2005, 43: 459-461. 10.1038/sj.sc.3101701.View ArticlePubMedGoogle Scholar
- Rosenzweig ES, McDonald JW: Rodent models for treatment of spinal cord injury: research trends and progress toward useful repair. Curr Opin Neurol. 2004, 17: 121-131. 10.1097/00019052-200404000-00007.View ArticlePubMedGoogle Scholar
- Steward O, Schauwecker PE, Guth L, Zhang Z, Fujiki M, Inman D, Wrathall J, Kempermann G, Gage FH, Saatman KE, et al: Genetic approaches to neurotrauma research: opportunities and potential pitfalls of murine models. Exp Neurol. 1999, 157: 19-42. 10.1006/exnr.1999.7040.View ArticlePubMedGoogle Scholar
- Kigerl KA, McGaughy VM, Popovich PG: Comparative analysis of lesion development and intraspinal inflammation in four strains of mice following spinal contusion injury. J Comp Neurol. 2006, 494: 578-594. 10.1002/cne.20827.View ArticlePubMedPubMed CentralGoogle Scholar
- Pannu R, Christie DK, Barbosa E, Singh I, Singh AK: Post-trauma Lipitor treatment prevents endothelial dysfunction, facilitates neuroprotection, and promotes locomotor recovery following spinal cord injury. J Neurochem. 2007, 101: 182-200. 10.1111/j.1471-4159.2006.04354.x.View ArticlePubMedGoogle Scholar
- Pearse DD, Chatzipanteli K, Marcillo AE, Bunge MB, Dietrich WD: Comparison of iNOS inhibition by antisense and pharmacological inhibitors after spinal cord injury. J Neuropathol Exp Neurol. 2003, 62: 1096-1107.View ArticlePubMedGoogle Scholar
- Elshafiey I, Bilgen M, He R, Narayana PA: In vivo diffusion tensor imaging of rat spinal cord at 7 T. Magn Reson Imaging. 2002, 20: 243-247. 10.1016/S0730-725X(02)00493-9.View ArticlePubMedGoogle Scholar
- Kim JH, Loy DN, Liang HF, Trinkaus K, Schmidt RE, Song SK: Noninvasive diffusion tensor imaging of evolving white matter pathology in a mouse model of acute spinal cord injury. Magn Reson Med. 2007, 58: 253-260. 10.1002/mrm.21316.View ArticlePubMedGoogle Scholar
- Aimone JB, Leasure JL, Perreau VM, Thallmair M: Spatial and temporal gene expression profiling of the contused rat spinal cord. Exp Neurol. 2004, 189: 204-221. 10.1016/j.expneurol.2004.05.042.View ArticlePubMedGoogle Scholar
- Ousman SS, David S: MIP-1alpha, MCP-1, GM-CSF, and TNF-alpha control the immune cell response that mediates rapid phagocytosis of myelin from the adult mouse spinal cord. J Neurosci. 2001, 21: 4649-4656.PubMedGoogle Scholar
- Parker D: Pharmacological approaches to functional recovery after spinal injury. Curr Drug Targets CNS Neurol Disord. 2005, 4: 195-210. 10.2174/1568007053544192.View ArticlePubMedGoogle Scholar
- Pearse DD, Bunge MB: Designing cell- and gene-based regeneration strategies to repair the injured spinal cord. J Neurotrauma. 2006, 23: 437-452. 10.1089/neu.2006.23.437.View ArticleGoogle Scholar
- Bilgen M: A new device for experimental modeling of central nervous system injuries. Neurorehabil Neural Repair. 2005, 19: 219-226. 10.1177/1545968305278635.View ArticlePubMedGoogle Scholar
- Bilgen M: Simple, low-cost multipurpose RF coil for MR microscopy at 9.4 T. Magn Reson Med. 2004, 52: 937-940. 10.1002/mrm.20228.View ArticlePubMedGoogle Scholar
- Bilgen M, Al-Hafez B, Berman NE, Festoff BW: Magnetic resonance imaging of mouse spinal cord. Magn Reson Med. 2005, 54: 1226-1231. 10.1002/mrm.20672.View ArticlePubMedGoogle Scholar
- Bilgen M: Imaging corticospinal tract connectivity in injured rat spinal cord using manganese-enhanced MRI. BMC Medical Imaging. 2006, 6: 15-10.1186/1471-2342-6-15.View ArticlePubMedPubMed CentralGoogle Scholar
- Bilgen M, Elshafiey I, Narayana PA: Mohr diagram representation of anisotropic diffusion tensor in MRI. Magn Reson Med. 2002, 47: 823-827. 10.1002/mrm.10119.View ArticlePubMedGoogle Scholar
- Bilgen M, Narayana PA: Mohr diagram interpretation of anisotropic diffusion indices in MRI. Magn Reson Imaging. 2003, 21: 567-572. 10.1016/S0730-725X(03)00071-7.View ArticlePubMedGoogle Scholar
- Wei H, Desouki MM, Lin S, Xiao D, Franklin RB, Feng P: Differential expression of metallothioneins (MTs) 1, 2, and 3 in response to zinc treatment in human prostate normal and malignant cells and tissues. Mol Cancer. 2008, 7: 7-10.1186/1476-4598-7-7.View ArticlePubMedPubMed CentralGoogle Scholar
- Bilgen M, Rumboldt Z: Neuronal and vascular biomarkers in Syringomyelia: investigations using longitudinal MRI. Biomarkers in Medicine. 2008, 2: 113-124. 10.2217/175203184.108.40.206.View ArticlePubMedGoogle Scholar
- Inman D, Guth L, Steward O: Genetic influences on secondary degeneration and wound healing following spinal cord injury in various strains of mice. J Comp Neurol. 2002, 451: 225-235. 10.1002/cne.10340.View ArticlePubMedGoogle Scholar
- Inman DM, Steward O: Physical size does not determine the unique histopathological response seen in the injured mouse spinal cord. J Neurotrauma. 2003, 20: 33-42. 10.1089/08977150360517164.View ArticlePubMedGoogle Scholar
- Wamil AW, Wamil BD, Hellerqvist CG: CM101-mediated recovery of walking ability in adult mice paralyzed by spinal cord injury. Proc Natl Acad Sci USA. 1998, 95: 13188-13193. 10.1073/pnas.95.22.13188.View ArticlePubMedPubMed CentralGoogle Scholar
- Bonny JM, Gaviria M, Donnat JP, Jean B, Privat A, Renou JP: Nuclear magnetic resonance microimaging of mouse spinal cord in vivo. Neurobiol Dis. 2004, 15: 474-482. 10.1016/j.nbd.2003.11.026.View ArticlePubMedGoogle Scholar
- Stieltjes B, Klussmann S, Bock M, Umathum R, Mangalathu J, Letellier E, Rittgen W, Edler L, Krammer PH, Kauczor HU, et al: Manganese-enhanced magnetic resonance imaging for in vivo assessment of damage and functional improvement following spinal cord injury in mice. Magn Reson Med. 2006, 55: 1124-1131. 10.1002/mrm.20888.View ArticlePubMedGoogle Scholar
- Bilgen M, Al-Hafez B: Comparison of spinal vasculature in mouse and rat: investigations using MR angiography. Neuroanatomy. 2006, 5: 12-18.Google Scholar
- Gaviria M, Bonny JM, Haton H, Jean B, Teigell M, Renou JP, Privat A: Time course of acute phase in mouse spinal cord injury monitored by ex vivo quantitative MRI. Neurobiol Dis. 2006, 22: 694-701. 10.1016/j.nbd.2006.01.011.View ArticlePubMedGoogle Scholar
- Kim JH, Trinkaus K, Ozcan A, Budde MD, Song SK: Postmortem delay does not change regional diffusion anisotropy characteristics in mouse spinal cord white matter. NMR Biomed. 2007, 20: 352-359. 10.1002/nbm.1138.View ArticlePubMedGoogle Scholar
- Huang ZL, He YY, Bilgen M: In vivo tracing of corticospinal tract in mouse using manganese-enhanced contrast. J Neurol Sci [Turk]. 2007, 24: 38-44.Google Scholar
- Loy DN, Kim JH, Xie M, Schmidt RE, Trinkaus K, Song SK: Diffusion tensor imaging predicts hyperacute spinal cord injury severity. J Neurotrauma. 2007, 24: 979-990. 10.1089/neu.2006.0253.View ArticlePubMedGoogle Scholar
- Bilgen M: Magnetic resonance microscopy of spinal cord injury in mouse using a miniaturized implantable RF coil. J Neurosci Methods. 2007, 159: 93-97. 10.1016/j.jneumeth.2006.06.024.View ArticlePubMedGoogle Scholar
- Bilgen M, Al-Hafez B, Alrefae T, He YY, Smirnova IV, Aldur MM, Festoff BW: Longitudinal magnetic resonance imaging of spinal cord injury in mouse: changes in signal patterns associated with the inflammatory response. Magn Reson Imaging. 2007, 25: 657-664. 10.1016/j.mri.2006.10.009.View ArticlePubMedGoogle Scholar
- Clark CA, Werring DJ, Miller DH: Diffusion imaging of the spinal cord in vivo: estimation of the principal diffusivities and application to multiple sclerosis. Magn Reson Med. 2000, 43: 133-138. 10.1002/(SICI)1522-2594(200001)43:1<133::AID-MRM16>3.0.CO;2-X.View ArticlePubMedGoogle Scholar
- Bilgen M, Al-Hafez B, He YY, Brooks WM: Magnetic resonance angiography of rat spinal cord at 9.4 T: a feasibility study. Magn Reson Med. 2005, 53: 1459-1461. 10.1002/mrm.20471.View ArticlePubMedGoogle Scholar
- Callot V, Duhamel G, Cozzone PJ: In vivo mouse spinal cord imaging using echo-planar imaging at 11.75 T. Magma. 2007, 20: 169-173. 10.1007/s10334-007-0079-x.View ArticlePubMedPubMed CentralGoogle Scholar
- The pre-publication history for this paper can be accessed here:http://www.biomedcentral.com/1471-2342/9/10/prepub
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