real-time monitoring of mitochondrial nadh and microcirculatory blood flow in the spinal cord
TRANSCRIPT
1 In vivo spinal cord monitoring
Real Time Monitoring of Mitochondrial NADH and
Microcirculatory Blood Flow in the Spinal Cord
Maryana Simonovich M.Sc., Efrat Barbiro-Michaely Ph.D.,
Avraham Mayevsky Ph.D.
The Mina & Everard Goodman Faculty of Life Sciences
and the Leslie and Susan Gonda Multidisciplinary Brain Research Center,
Bar-Ilan University, Ramat-Gan 52900, Israel
Running title: In vivo spinal cord monitoring
Corresponding Author:
Prof. Avraham Mayevsky
The Mina & Everard Goodman Faculty of Life Sciences, Bar-Ilan University
The Leslie and Susan Gonda Multidisciplinary Brain Research Center
Ramat-Gan 52900, Israel
Tel: 972-3-5318218
Fax: 972-3-6354459
E-mail: [email protected]
2 In vivo spinal cord monitoring
Introduction
Postoperative spinal cord injuries following abdominal aortic aneurysm repair and
surgeries under sclerosis of spinal cord blood vessels, are common and usually result
from ischemia, reperfusion injury, and postoperative hemodynamic damage.1;2
The
patients whose postoperative complications include paraplegia or paresis not only suffer
severe physical disability, but their long-term survival is also known to be shorter.2 To
learn more about the pathology of spinal cord injury following abrupt SCBF changes,
several animal models were developed. The most common methods include the occlusion
of the abdominal aorta, first introduced by Niels Stensen in 1667,3 balloon inflation in the
spinal extradural space 4 and photochemical injury of the spinal cord's vascular
endothelium with or without laminectomy.5;6
In the past two decades, spinal cord monitoring during surgery has been a desirable
tool for preventing potential intra-operative neurological injury, leading to a considerable
increase in its use. Traditional intraoperative neurophysiological assessment methods,
such as Direct Motor Pathway Stimulation Technique (DMPST) and Somatosensory
Evoked Potential (SSEP) monitoring, have been used to evaluate proximal nerve activity.
However, it is clear that neurological injury following operation of the spinal cord or
thoracic and abdominal operations is mostly due to intraoperative aortic cross-clamping,
or due to an abrupt (change or decrease) of blood flow in the blood vessels which are
critical to spinal cord function and not a direct impact of the spinal cord 7. Furthermore,
false monitoring outcomes, such as in cases of definite neurologic deficits despite stable
SEP, can occur during surgery Hence, the ability to early detect changes in the
3 In vivo spinal cord monitoring
hemodynamic and metabolic state of the tissue is extremely important and may contribute
to the reliability of monitoring in clinical practice.8
In the present study, we offer a new approach for spinal cord monitoring which
includes the simultaneous monitoring of spinal cord blood flow and mitochondrial
NADH level. NADH, a major component of the respiratory chain, is one of the most
sensitive indicators of oxygen deficiency.9 A decrease in oxygen supply to the spinal cord
tissue is followed by a decrease in ATP levels, a decrease in Na+/K
+ ATPase activity and
an increase in extracellular K+ levels.
10 Only a few studies measured energy metabolism
after spinal cord injury, demonstrating a rapid decrease in high-energy phosphates.1
Moreover, the monitoring of mitochondrial NADH in the spinal cord is rare in animal
experiments and apparently never performed in patients.
In view of these limitations of the available monitoring techniques, our new approach
for the evaluation of the spinal cord tissue integrity, if used clinically, will provide
essential complementary information that may improve the patients’ outcome. Up to date,
monitoring of the spinal cord energy metabolism in patients during surgical procedures is
not available.
The aim of the present study is to evaluate in real-time the spinal cord hemodynamic
and mitochondrial redox state using laser Doppler flowmetry and NADH fluorometry
simultaneously, during transient global ischemia in a rat model and during local ischemia.
4 In vivo spinal cord monitoring
Methods
The Tissue Vitality Monitoring System (TVMS)
In order to achieve real time monitoring of the metabolic and hemodynamic state of
the spinal cord, we used the Tissue Vitality Monitoring System (TVMS), developed in
our laboratory and previously applied in other studies 11
. The TVMS includes optical
fibers for the measurements of spinal cord blood flow (SCBF) and mitochondrial NADH
redox state as demonstrated in Figure 1. The inner diameter of the monitoring probe was
2mm and the depth of monitoring was 0.5-1mm for NADH and 1-1.5mm for SCBF.
Spinal cord blood flow (SCBF)
Spinal cord blood flow (SCBF) was monitored by the laser Doppler flowmetery (LDF)
approach (Perimed Inc.)12;13
applied in the TVMS. The laser Doppler flowmetry is
principally based on the Doppler shift which results from the amount and velocity of red
blood cells movement. The tissue is illuminated by red light at 632.8nm wavelength, to
the depth of 1-1.5mm. This light is shifted by moving red blood cells. The number of
shifted waves is affected by tissue blood volume and the degree of the shift is influenced
by the blood flow velocity. These two parameters (volume and velocity) are used for the
calculation of the relative blood flow level in which 0% is measured at death and the
basal level is presented as 100%. The LDF is significantly correlated to other two
quantitative monitoring approaches: the micro-sphere method and H2 clearance.14-16
NADH Surface Fluorometry
The principle of NADH monitoring from the surface of the spinal cord is that
excitation light (366nm) is passed from the fluorometer to the spinal cord surface (to a
5 In vivo spinal cord monitoring
depth of 0.5-1mm) via a bundle of quartz optical fibers. The emitted light (450 nm),
together with the reflected light at the excitation wavelength, are transferred to the
fluorometer via another bundle of fibers and appropriate filters. The changes in the
reflected light are correlated to changes in tissue blood volume in such a way that an
increase in tissue blood volume decreases the reflected light, due to an increase in tissue
light absorption, and vice versa. Since these changes in the reflectance affects also the
fluorescent light emitted from NADH molecules a correction of the signal is made by
subtracting the reflectance from the fluorescence value at a 1:1 ratio yielding the
corrected fluorescence which express the mitochondrial NADH redox state.17;18
.
Animal Preparation and Protocols
All experiments were carried out according to the NIH guidelines for the care and use
of laboratory animals and approved by the Institutional animal care review board. Adult
male Wistar rats (250-350gr) were anesthetized by intraperitoneal (IP) injection of
Equithesin solution (each ml contains: Chloral Hydrate 42.51mg, Propylene Glycol
44.34%, Pentobarbital 9.72 mg, Magnesium Sulphate 21.25 mg, Alcohol 11.5% water)
0.3 ml/100g body weight. The right femoral artery was cannulated using polyethylene
tubes (PE-50) for arterial blood pressure (MAP) monitoring. The animals' body
temperature was kept at 37±0.5°C during the entire experimental period.
Laminectomy was performed at L3 vertebra, and a 3mm hole was gradually drilled in
the vertebra until the dura was revealed. Than the TVMS was located above the spinal
cord tissue (leaving the dura matter intact) using a micromanipulator, avoiding extra
pressure on the monitored tissue, as was ensured by the initial level of SCBF which
remained stable throughout the entire procedure of placing the TVMS on it. In the
6 In vivo spinal cord monitoring
abdominal aorta occlusion model, the probe was fixated to the monitoring site by acryl
cement, whereas in the compression model no fixation was used. At the end of the
experiments, the rats were sacrificed by pure N2 (100%) inhalation.
Experimental protocols
The following animal groups were used:
A) Control group (n=8): Following laminectomy and probe fixation, the rats were
exposed to pure N2 to induce short (15 sec) anoxia, and then the animals were re-
exposed to room air and continuously monitored for approximately 1.5 hours to
ensure steady monitoring through the entire experimental period.
Short anoxia was also induced in each animal in the study, as this is a routine
procedure used for the assessment of spinal cord tissue viability at the beginning of
each experiment, as well as for the verification of proper probe fixation to the
monitored site.
B) Ischemic group (n=11): Thirty minutes after a short anoxia, animals underwent
transient spinal cord ischemia, which was induced by a 5 min occlusion of the
abdominal aorta, just distal to the left kidney, followed by a reperfusion and a
recovery period of 1.5 hours.
C) Compression model group (n=6): Following laminectomy, the fiber optic probe
was placed on the monitoring site (with no fixation) using a micromanipulator.
SCBF was continuously monitored through this procedure making sure that blood
flow remains intact through the entire procedure of probe placement on the spinal
cord tissue. Compression was induced by lowering the probe on the spinal cord
7 In vivo spinal cord monitoring
tissue using a micromanipulator and compressing the spinal cord tissue until SCBF
was completely abolished (0%). The spinal cord tissue remained compressed for a
period of 5 min, followed by elevation of the probe back to its initial height.
Monitoring continued for another 1.5 hours to evaluate tissue recovery. This
protocol included two sessions of spinal cord compression with an interval of 90
min.
Statistical Analysis:
The Student paired two-tailed t test was used to examine the significance of changes in
the various parameters as related to the initial level. The Student unpaired two-tailed t test
was used to examine the effects of the transient ischemia or compression model on the
physiological parameters measured from the rat’s spinal cord and the systemic blood
pressure in each minute. A value of p<0.05 was considered to be significant. In each
experiment, values were obtained at intervals of 60 sec and mean ± SE values were
calculated for each parameter. Correlation tests were used to determine the relation
between mean SCBF and NADH monitored by the TVMS.
8 In vivo spinal cord monitoring
Results
In order to ensure proper fixation of the TVMS probe on the spinal cord surface, as
well as validate spinal cord tissue integrity, all animals were subjected to short anoxia for
15 seconds while the parameters were recorded. Figure 2 presents the mean ± SE levels
of the various parameters monitored by the TVMS during short anoxia (N2 100%). The
significance of each value was examined as compared to the basal level. At the start of
anoxia, SCBF decreased to 84.4±0.37% and MAP reached the level of 67±0.3 mmHg.
These changes were associated with a significant (p<0.001) increase in the fluorometric
parameters, namely, the Reflectance (5.6±0.2%), Fluorescence (12.5±0.2%) and NADH
(7.1±0.2%). Following exposure to room air, SCBF hyperemia was noted (100-170sec
post N2, p<0.001), which was followed by full recovery. All the recorded metabolic
parameters (SCBF and NADH) returned to the basal levels. However, MAP remained
elevated (p<0.01) for 280 sec.
Eleven rats underwent lumbar spinal cord ischemia, induced by 5 min abdominal
aortic occlusion just distal to the renal arteries, as described in Zivin’s work.19
As
demonstrated in Figure 3, abdominal aortic occlusion resulted in a significant MAP
decline to extremely low levels (10.8±0.5 mmHg, p<0.001), which served as an
indication for the efficacy of the abdominal aorta occlusion (since MAP was monitored in
the Femoral artery). In addition, SCBF levels dropped to 19.9±6.1% and remained low
through the entire ischemia period. These changes were associated with a significant
increase of NADH components to maximum levels, namely: Reflectance (25±9.3%),
Fluorescence (70±17.2%) and NADH (39±11.1%). These changes were significantly
9 In vivo spinal cord monitoring
higher than the basal level, as well as compared to the levels measured at the same time
points in the control group (p<0.01).
With the release of the occlusion (open) MAP was restored (114.8±6.5 mmHg) and
SCBF reached hyperemic levels (p<0.01) in the first 10 min of reperfusion. The
Reflectance, Fluorescence and NADH also gradually returned to their initial levels.
The effects of spinal cord compression are presented in Figure 4. As seen, the
compression of the spine (comp. on) yielded a primary decrease of SCBF to 0%,
followed by a partial recovery, within the compression phases, up to the levels of
24.0±6.4% (1st compression) and 19±3.3% (2
nd compression). In association with the
SCBF changes, there was a significant rise (p<0.001) in the reflectance (196±27.5%),
fluorescence (265.6±43.0%) and NADH (64.4±26.9%) during the first compression
session. Similarly, the second compression caused an increase (p<0.001) of the
parameters to the levels of 115.7±25.1%, 219.4±32.8% and 69.6±18%, respectively.
There were no significant differences between the responses of the parameters during the
two compression periods.
As the TVMS probe was elevated back to the initial height, a short hyperemia of
160.4±16.6% and 199.3±25.9% was observed in the two compression sessions
respectively, after which SCBF returned to the initial levels. Consistently with the SCBF
responses, the reflectance, fluorescence and mitochondrial NADH returned to their basal
levels.
MAP levels monitored in the first two minutes of compression, were significantly
lower
10 In vivo spinal cord monitoring
(59.3±2.5 mmHg and 56.4±3.9 mmHg in the first and second compression, respectively)
than initial MAP levels (77.1±2.4 mmHg and 72.6±4.1 mmHg, respectively). At 7-9 min,
there were observed significant differences (p<0.05) between MAP levels during the two
compression periods. Nevertheless, during the rest of the experiment, MAP recovered
and stabilized at the basal levels. To better understand the relationship between the
various parameters monitored by the TVMS, during treatments where the SCBF
dramatically changed, we performed several correlation tests. The relationship between
SCBF and the mitochondrial redox state (NADH) was described as a polynomic
regression line (p<0.05), shown in Figure 5. Under low SCBF levels, mitochondrial
NADH increased, while under SCBF elevation NADH became oxidized. The correlation
coefficients between NADH and SCBF in all the three experimental groups were
significantly high: R = 0.95 for anoxia, R = 0.94 for ischemia, R = 0.95 for the 1st
compression and R = 0.98 for the 2nd
compression.
Discussion
Although intraoperative monitoring has been increasingly used during the past
decades, there is still a great need for devices that enable not only an early warning for
complications but can also evaluate spinal cord integrity during the procedure in order to
improve the recovery. In the current study, we present a new real-time monitoring
approach for the evaluation of spinal cord vitality. Although the monitoring portion of the
spinal cord by our probe is relatively small (a diameter of 2mm and a depth of
approximately 1mm) we are sure that this area supplies reliable information on the cord
viability. This statement is based on our vast experience in real time monitoring of the
brain showing that even when monitoring takes place simultaneously in different
11 In vivo spinal cord monitoring
locations of the brain under a specific perturbation, using even smaller probes (1mm in
diameter), the responses of all monitored parameters are very similar. Hence the
monitoring of tissue blood flow and mitochondrial NADH level, even in a small area
provides reliable information on the tissue metabolic state 18
.
Spinal cord monitoring technology must include a number of important characteristics:
accuracy, an optimal monitoring site and minimal complication risks. Over the years,
wide experience has been gathered in the intraoperative neurophysiological monitoring of
somatosensory or motor evoked potential, however, there is no consensus among the
physicians as to the reliability and efficiency of these methods during surgeries.14;20-24
During the last years, the new monitoring technique of Near Infrared Spectroscopy
(NIRS) has begun to be implemented. This technique enables a continuous monitoring of
oxy/deoxy hemoglobin levels and cytochrome aa3 in the tissue. When used during spinal
surgeries 25;26
it may allow an early detection of spinal ischemia. However, even though
desirable for its non-invasive features, this technique has not yet been accepted into
routine clinical practice, due to its low spatial resolution,27
namely, the monitored volume
includes a variety of tissue types,28;29
decreasing its accuracy. In addition, the monitoring
is influenced by age, hemoglobin concentration at the measured site, and sensor
location.30
In view of these facts, it is extremely important to suggest an alternative monitoring
approach for the real time assessment of the spine during surgical procedures that may
carry a risk of ischemic injury.
The first step was to develop a monitoring model which would enable the induction of
spinal cord ischemia concomitantly with its monitoring. For this purpose, we chose two
12 In vivo spinal cord monitoring
animal models, inducing a decrease of blood supply: transient abdominal aortic occlusion
and spinal cord compression. In addition, since the decrease in tissue blood supply mainly
involves oxygen deficiency, we also tested the effect of complete oxygen deficit induced
by exposing the animals to pure N2 (anoxia). The anoxia model was selected also in order
to verify the reliability of the monitoring technique, insofar as our vast experience in
brain monitoring using the same techniques has shown its effects on tissue blood flow
and mitochondrial NADH.17;31
As expected, short anoxia caused a rapid oxygen level
drop, triggering wide systemic vasodilation resulting in a blood pressure drop as well as a
decrease in SCBF. This apparently decreased the tissue blood volume, leading to an
elevation in the reflectance level. Moreover, the lack of oxygen led to an interruption of
mitochondrial electron flow and an elevation in NADH levels. When the animals
resumed breathing air, all the parameters returned to their basal levels, indicating that no
irreversible damage to the spinal cord tissue occurred.
The global ischemia model, used in the present study, corresponded to the rat model
reported by Kanellopoulos, Ueno et al, and described by Marsala as “low flow.”32
As
presented in Figure 3, MAP dropped immediately, indicating a complete abdominal
artery occlusion. Additionally, aortic occlusion caused a drastic reduction in SCBF, but
did not completely block it. This was presumably due to additional blood supply sources,
such as posterior spinal arteries and other intercostal branches, namely arteria radicularis
magna (the artery of Adamkiewicz). At the same time, the blood volume in the spinal
cord tissue decreased, changing the absorption characteristics of the tissue and leading to
an increase in the reflectance levels. Simultaneously, the levels of Fluorescence and
NADH rose, indicating tissue metabolic stress and mitochondrial dysfunction due to the
13 In vivo spinal cord monitoring
deficit of oxygen, glucose and other metabolites, shifting the energy equilibrium towards
anaerobic metabolism, as was previously reported.22;33
Once the reperfusion started, all of
the fluorometric parameters fully recovered. The observed hyperemia was probably
produced by auto-regulation mechanisms activated by the sympathetic nervous system, as
was previously reported for ischemia models in pigs and mice.32;34;35
Concerning the focal ischemia model induced by the compression of the spinal tissue,
we had the advantage of directly monitoring the site of primary injury. Indeed, in this
model, SCBF fully decreased to the "no flow" status, which was followed by a partial
recovery towards “low flow” perfusion within the compression phase, and fully
recovered during reperfusion. These changes were inversely correlated to changes in the
mitochondrial NADH levels, indicating that focal ischemia of the spinal cord, during 5
minutes, caused no irreversible damage to the spinal tissue.
The fact that the correlation between the blood supply and the metabolic state of the
spinal cord is not linear can be explained by the action of autoregulatory mechanisms that
are activated when SCBF exceeds its limits of autoregulation. The lower limit of SCBF
seems to be below 30%, yielding an increase of 50% in the mitochondrial NADH level.
The TVMS monitors relative hemodynamic and metabolic changes in a restricted
tissue volume within the posterior area of the spinal cord and is not influenced by the
various layers of the spinal cord. Therefore, the superiority of the present technique lies
in its high spatial and temporal resolution36
as opposed to NIRS which is characterized by
a low spatial resolution.27
Nevertheless, the use of the TVMS in the clinic is suggested
only as a monitoring tool complementary to other neurophysiological monitoring
techniques.
14 In vivo spinal cord monitoring
During the past decade, the connection between the mitochondria and neuronal
survival has become apparent in many pathophysiological processes and clinical
conditions.37
However, in vivo NADH monitoring has not been implicated. It is well
known that mitochondrial NADH is the most stable and representative parameter of
tissue energy metabolism. It is affected by substrate and O2 availability and ATP
turnover, determined by the metabolic activity of the tissue. Nevertheless, very little has
been done to monitor mitochondrial function in vivo in clinical environments. The
monitoring of microcirculatory tissue blood flow (TBF) together with mitochondrial
NADH, reveals that, with the greater number of parameters, a better interpretation can be
given to the very complex pathophysiological situations.38
In conclusion, the use of the TVMS has a great advantage for spinal cord tissue
monitoring during surgical procedures, as it allows an immediate detection of
hemodynamic and metabolic deteriorations of the tissue and, when applied together with
other currently used methods, may help prevent secondary damage to the spinal tissue
and improve the final outcome.
15 In vivo spinal cord monitoring
References
1. Girardi FP, Khan SN, Cammisa FPJ et al. Advances and strategies for spinal cord
regeneration. Orthop.Clin.North Am. 2000;31:465-72.
2. Tabayashi K. Spinal cord protection during thoracoabdominal aneurysm repair.
Surg.Today. 2005;35:1-6.
3. Scherz G. Steno. Geological papers. Odense: Odense University Press, 1969:88-91.
4. Tarlov IM, Klinger H. Spinal cord compression studies. II. Time limits for recovery
after acute compression in dogs. AMA.Arch.Neurol.Psychiatry. 1954;71:271-90.
5. Hao JX, Herregodts P, Lind G et al. Photochemically induced spinal cord ischaemia
in rats: assessment of blood flow by laser Doppler flowmetry. Acta Physiol Scand.
1994;151:209-15.
6. Hao JX, Xu XJ, Aldskogius H et al. Photochemically induced transient spinal
ischemia induces behavioral hypersensitivity to mechanical and cold stimuli, but
not to noxious-heat stimuli, in the rat. Exp Neurol. 1992;118:187-94.
7. Etz CD, Homann TM, Luehr M et al. Spinal cord blood flow and ischemic injury
after experimental sacrifice of thoracic and abdominal segmental arteries. Eur.J
Cardiothorac.Surg. 2008;..
8. Nuwer MR, Dawson EG, Carlson LG et al. Somatosensory evoked potential spinal
cord monitoring reduces neurologic deficits after scoliosis surgery: results of a large
multicenter survey. Electroencephalogr.Clin Neurophysiol. 1995;96:6-11.
16 In vivo spinal cord monitoring
9. Mayevsky A. Biochemical and physiological activities of the brain as in vivo
markers of brain pathology. In: Bernstein EF, Callow AD, Nicolaides AN et al.,
eds. Cerebral, Revascularization.Med-Orion Pub., 1993:51-69.
10. Schwab ME, Bartholdi D. Degeneration and regeneration of axons in the lesioned
spinal cord. Physiol.Rev. 1996;76:319-70.
11. Barbiro-Michaely E, Tolmasov M, Rinkevich-Shop S et al. Can the "brain-sparing
effect" be detected in a small-animal model? Med Sci Monit 2007;13:BR211-
BR219.
12. Frerichs KU, Feuerstein GZ. Laser-Doppler flowmetry. A review of its application
for measuring cerebral and spinal cord blood flow. Mol.Chem.Neuropathol.
1990;12:55-70.
13. Lindsberg PJ, Jacobs TP, Frerichs KU et al. Laser-Doppler flowmetry in monitoring
regulation of rapid microcirculatory changes in spinal cord. Am.J.Physiol.
1992;263:H285-H292.
14. Hickey R, Albin MS, Bunegin L et al. Autoregulation of spinal cord blood flow: is
the cord a microcosm of the brain? Stroke 1986;17:1183-9.
15. Wallace MC, Tator CH. Spinal cord blood flow measured with microspheres
following spinal cord injury in the rat. Can.J.Neurol.Sci. 1986;13:91-6.
16. Werner C, Hoffman WE, Kochs E et al. The effects of propofol on cerebral and
spinal cord blood flow in rats. Anesth.Analg. 1993;76:971-5.
17. Mayevsky A, Frank K, Muck M et al. Multiparametric evaluation of brain functions
in the Mongolian gerbil in vivo. J.Basic Clin.Physiol.Pharmacol. 1992;3:323-42.
17 In vivo spinal cord monitoring
18. Mayevsky A, Chance B. Intracellular oxidation reduction state measured in situ by
a multichannel fiber-optic-surface fluorometer. Science 1982;217:537-40.
19. Zivin JA, DeGirolami U. Spinal cord infarction: a highly reproducible stroke model.
Stroke 1980;11:200-2.
20. Deletis V. The 'motor' inaccuracy in neurogenic motor evoked potentials.
Clin.Neurophysiol. 2001;112:1365-6.
21. Deletis V, Sala F. The role of intraoperative neurophysiology in the protection or
documentation of surgically induced injury to the spinal cord. Ann.N.Y.Acad.Sci.
2001;939:137-44.
22. Nagy G, Dzsinich C, Selmeci L et al. Biochemical alterations in cerebrospinal fluid
during thoracoabdominal aortic cross-clamping in dogs. Ann.Vasc.Surg.
2002;16:436-41.
23. Sala F, Niimi Y, Berenstein A et al. Neuroprotective role of neurophysiological
monitoring during endovascular procedures in the spinal cord. Ann.N.Y.Acad.Sci.
2001;939:126-36.
24. Sala F, Krzan MJ, Deletis V. Intraoperative neurophysiological monitoring in
pediatric neurosurgery: why, when, how? Childs.Nerv.Syst. 2002;18:264-87.
25. Macnab AJ, Gagnon RE, Gagnon FA. Near infrared spectroscopy for intraoperative
monitoring of the spinal cord. Spine. 2002;27:17-20.
26. LeMaire SA, Ochoa LN, Conklin LD et al. Transcutaneous near-infrared
spectroscopy for detection of regional spinal ischemia during intercostal artery
ligation: preliminary experimental results. J Thorac.Cardiovasc.Surg.
2006;132:1150-5.
18 In vivo spinal cord monitoring
27. Kaoru S. Basic principle and clinical application of optical diagnostic techniques to
brain disorders. Journal of Nihon University Medical Association 2004;63:193-200.
28. De Georgia MA, Deogaonkar A. Multimodal monitoring in the neurological
intensive care unit. Neurologist. 2005;11:45-54.
29. Kytta J, Ohman J, Tanskanen P et al. Extracranial contribution to cerebral oximetry
in brain dead patients: a report of six cases. J Neurosurg Anesthesiol. 1999;11:252-
4.
30. Kishi K, Kawaguchi M, Yoshitani K et al. Influence of patient variables and sensor
location on regional cerebral oxygen saturation measured by INVOS 4100 near-
infrared spectrophotometers. J Neurosurg Anesthesiol. 2003;15:302-6.
31. Kraut A, Barbiro-Michaely E, Zurovsky Y et al. Multiorgan monitoring of
hemodynamic and mitochondrial responses to anoxia and cardiac arrest in the rat.
Adv.Exp.Med Biol. 2003;510:299-304.:299-304.
32. Marsala M, Sorkin LS, Yaksh TL. Transient spinal ischemia in rat: characterization
of spinal cord blood flow, extracellular amino acid release, and concurrent
histopathological damage. J.CBF Metab. 1994;14:604-14.
33. Backstrom T, Saether OD, Norgren L et al. Spinal cord metabolism during thoracic
aortic cross-clamping in pigs with special reference to the effect of allopurinol.
Eur.J.Vasc.Endovasc.Surg. 2001;22:410-7.
34. Aadahl P, Saether OD, Stenseth R et al. Winner of the ESVS prize 1989.
Microcirculation of the spinal cord during proximal aortic cross-clamping.
Eur.J.Vasc.Surg. 1990;4:5-10.
19 In vivo spinal cord monitoring
35. Lang-Lazdunski L, Matsushita K, Hirt L et al. Spinal cord ischemia. Development
of a model in the mouse. Stroke 2001;31:208-13.
36. Rane K, Segerdahl M, Karlsten R. Intrathecal adenosine increases spinal cord blood
flow in the rat: measurements with the laser-Doppler flowmetry technique. Acta
Anaesthesiol.Scand. 2004;48:1249-55.
37. Chan PH. Mitochondria and neuronal death/survival signaling pathways in cerebral
ischemia. Neurochem.Res. 2004;29:1943-9.
38. Mayevsky A, Chance B. Oxidation-reduction states of NADH in vivo: From
animals to clinical use. Mitochondrion. 2007.
20 In vivo spinal cord monitoring
Figure Legends
Figure 1:
Schematic representation of the TVMS placed on the spinal cord surface (A) and a cross
section view of the fiber optic bundle tip (B). Ex - Excitation, Em - Emission optical
fibers for the monitoring of NADH redox sate. LDout/LDin – optical fibers for laser
Doppler blood flow monitoring.
Figure 2:
The effect of a short anoxia (15 sec) on the mean arterial pressure (MAP) and the
recorded metabolic and hemodynamic parameters. Anoxia was induced by N2 (100%)
inhalation. The graph presents average data ± SE (n=29). The arrows mark significant
differences between each value versus the values recorded during the first 30 sec, p<0.05-
(^), p<0.01-(^^), p<0.001(^^^).
Figure 3:
Responses of the various parameters monitored by the TVMS to a 5 minutes abdominal
aortic occlusion. The graph presents mean data ± SE. The arrows mark significant
differences between the values of the ischemic group (n=11) versus the control group
(n=8) for each minute of monitoring, p<0.01-(**), p<0.001(***).
Figure 4:
Responses of the mean arterial pressure, metabolic and hemodynamic parameters, to two
sessions of spinal cord compression (5 min). Calibration was performed 3 minutes before
each compression. The graph presents average data ± SE, n=6. The arrows mark the time
21 In vivo spinal cord monitoring
(each minute) in which the values were significantly different between the two
compression sessions, p<0.05-(*).
Figure 5:
Correlation between SCBF and NADH under short anoxia (N2), ischemia and two
sessions of compression (1st and 2nd).
22 In vivo spinal cord monitoring
3mm
Vertebral body
Spinal cord
Neuroforamen
Nerve root
Laser Doppler Laser Doppler
FlowmeterFlowmeter
Red lightRed light
(632.8nm)(632.8nm)
Spinal Cord Blood FlowSpinal Cord Blood Flow
(Doppler shift)
Back scattered lightBack scattered light
(Blood volume)
Probe
FluorometerFluorometer
UV lightUV light
(366nm)(366nm)
NADH NADH redox redox statestate
(450nm fluorescence)
366nm reflectance366nm reflectance
(Blood volume)
1
A
Figure 1:
23 In vivo spinal cord monitoring
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0 30 60 90 120 150 180 210 240 270 300 330 360 390 420 450Time (sec)
^^^ ^^
N2 Air
Ref
lect
ance
(%
) F
luo
resc
ence
(%
) N
AD
H (
%)
SC
BF
(%
) M
AP
(m
mH
g)
Figure 2:
24 In vivo spinal cord monitoring
Figure 3:
-100
-50
0
50
100ISCHEMIA CONTROL
*
-100
-50
0
50
100 **
-100
-50
0
50
100
**
0
50
100
150
200
***
0
50
100
150
200
0 10 20 30 40 50 60 70 80 90Time (min)
***
MA
P (
mm
Hg
) S
CB
F (
%)
NA
DH
(%
) F
luo
resc
ence
(%
) R
efle
ctan
ce (
%)
Occlusion
Open
25 In vivo spinal cord monitoring
Figure 4:
-100
0
100
200
300
-100
0
100
200
3001st Compression Injury 2nd Compression Injury
-100
0
100
200
300
* *
0
50
100
150
200
0
50
100
150
0 10 20 30 40 50 60 70 80 90Time (min)
MA
P (
mm
Hg
) S
CB
F (
%)
NA
DH
(%
) F
luo
resc
ence
(%
) R
efle
ctan
ce (
%)
Comp.on
Comp. off
*