Intracerebral microvascular measurements during deep brain stimulation implantation using laser Doppler perfusion monitoring.
ABSTRACT The aim of the study was to investigate if laser Doppler perfusion monitoring (LDPM) can be used in order to differentiate between gray and white matter and to what extent microvascular perfusion can be recorded in the deep brain structures during stereotactic neurosurgery. An optical probe constructed to fit in the Leksell Stereotactic System was used for measurements along the trajectory and in the targets (globus pallidus internus, subthalamic nucleus, zona incerta, thalamus) during the implantation of deep brain stimulation leads (n = 22). The total backscattered light intensity (TLI) reflecting the grayness of the tissue, and the microvascular perfusion were captured at 128 sites. Heartbeat-synchronized pulsations were found at all perfusion recordings. In 6 sites the perfusion was more than 6 times higher than the closest neighbor indicating a possible small vessel structure. TLI was significantly higher (p < 0.005) and the perfusion significantly lower (p < 0.005) in positions identified as white matter in the respective MRI batch. The measurements imply that LDPM has the potential to be used as an intracerebral guidance tool.
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ABSTRACT: Between 1985 and 1990, the authors performed stereotactic posteroventral pallidotomies on 38 patients with Parkinson's disease whose main complaint was hypokinesia. Upon re-examination 2 to 71 months after surgery (mean 28 months), complete or almost complete relief of rigidity and hypokinesia was observed in 92% of the patients. Of the 32 patients who before surgery also suffered from tremor, 26 (81%) had complete or almost complete relief of tremor. The L-dopa-induced dyskinesias and muscle pain had greatly improved or disappeared in most patients, and gait and speech volume also showed remarkable improvement. Complications were observed in seven patients: six had a permanent partial homonymous hemianopsia (one also had transient dysphasia and facial weakness) and one developed transitory hemiparesis 1 week after pallidotomy. The results presented here confirm the 1960 findings of Svennilson, et al., that parkinsonian tremor, rigidity, and hypokinesia can be effectively abolished by posteroventral pallidotomy, an approach developed in 1956 and 1957 by Lars Leksell. The positive effect of posteroventral pallidotomy is believed to be based on the interruption of some striopallidal or subthalamopallidal pathways, which results in disinhibition of medial pallidal activity necessary for movement control.Journal of Neurosurgery 02/1992; 76(1):53-61. · 3.15 Impact Factor
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ABSTRACT: Currently much interest is focussed on the possibilities for treatment of neurodegenerative disorders by transplantation of specific transmitter releasing cells to the central nervous system. The term “neurodegenerative” is used to describe disorders characterized by cell loss in the central nervous system and includes Parkinson’s disease, Huntington’s disease, Alzheimer’s disease and amyotrophic lateral sclerosis. They all have in common that their exact etiology and pathogenesis is unknown and that they curtail both the quality and quantity of life. They often slowly progress to a state of severe incapacitation of the sufferer with neurological symptoms related to which specific cell type(s) and neurotransmitter systems are affected. Since no therapy can be offered against the basic etiologies, the treatment, if any, is directed towards symptomatic relief (for comprehensive reviews the reader is referred to Calne 1994). The exciting progress made by biomedical science during the last two decades in understanding the basic mechanisms of growth, behaviour and function of neural transplants in the mammalian central nervous system has opened the possibility for a different and, at least in theory, curative therapeutic strategy aiming at repairing the brain (Dunnett and Björklund 1994). The concept may include possibilities for either a partial or even total recovery of function by replacement of lost cell populations to restore specific neurotransmitter systems, neural circuits or to remyelinate fibers in demyelination disorders.Advances and technical standards in neurosurgery 02/1997; 23:3-46.
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ABSTRACT: The vast majority of centers use electrophysiological mapping techniques to finalize target selection during the implantation of deep brain stimulation (DBS) leads for the treatment of Parkinson's disease and tremor. This review discusses the techniques used for physiological mapping and addresses the questions of how various mapping strategies modify target selection and outcome following subthalamic nucleus (STN), globus pallidus internus (GPi), and ventralis intermedius (Vim) deep brain stimulation. Mapping strategies vary greatly across centers, but can be broadly categorized into those that use microelectrode or semimicroelectrode techniques to optimize position prior to implantation and macrostimulation through a macroelectrode or the DBS lead, and those that rely solely on macrostimulation and its threshold for clinical effects (benefits and side effects). Microelectrode criteria for implantation into the STN or GPi include length of the nucleus recorded, presence of movement-responsive neurons, and/or distance from the borders with adjacent structures. However, the threshold for the production of clinical benefits relative to side effects is, in most centers, the final, and sometimes only, determinant of DBS electrode position. Macrostimulation techniques for mapping, the utility of microelectrode mapping is reflected in its modification of electrode position in 17% to 87% of patients undergoing STN DBS, with average target adjustments of 1 to 4 mm. Nevertheless, with the absence of class I data, and in consideration of the large number of variables that impact clinical outcome, it is not possible to conclude that one technique is superior to the other in so far as motor Unified Parkinson's Disease Rating Scale outcome is concerned. Moreover, mapping technique is only one out of many variables that determine the outcome. The increase in surgical risk of intracranial hemorrhage correlated to the number of microelectrode trajectories must be considered against the risk of suboptimal benefits related to omission of this technique. © 2006 Movement Disorder SocietyMovement Disorders 06/2006; 21(S14):S259 - S283. · 4.56 Impact Factor
Intracerebral microvascular measurements
during deep brain stimulation implantation
using laser doppler perfusion monitoring
Karin Wårdell, P. Blomstedt, Johan Richter, Johan Antonsson, Ola Eriksson, Peter Zsigmond,
A.T. Bergenheim and M.I. Hariz
Linköping University Post Print
N.B.: When citing this work, cite the original article.
Karin Wårdell, P. Blomstedt, Johan Richter, Johan Antonsson, Ola Eriksson, Peter Zsigmond,
A.T. Bergenheim and M.I. Hariz, Intracerebral microvascular measurements during deep
brain stimulation implantation using laser doppler perfusion monitoring, 2007, Stereotactic
and Functional Neurosurgery, (85), 6, 279-286.
Postprint available at: Linköping University Electronic Press
Wårdell et al., 2007-01-14 1
Intracerebral microvascular measurements during deep brain stimulation
implantation using laser Doppler perfusion monitoring
Karin Wårdell1, Patric Blomstedt2, Johan Richter3, Johan Antonsson1, Ola Eriksson1,4,Peter
Zsigmond4, A.Tommy Bergenheim2, Marwan. I. Hariz2,5
1Department of Biomedical Engineering, Linköping University, Sweden
2Department of Neurosurgery, University Hospital, Umeå, Sweden
3Department of Neurosurgery, University Hospital, Linköping, Sweden
4Elekta Instrument AB, Stockholm, Sweden
5Institute of Neurology, Queens Square, University College London, UK
Department of Biomedical Engineering
S-581 85 Linköping
Keywords: laser Doppler perfusion monitoring, deep brain stimulation, microcirculation,
Short title: Laser Doppler perfusion monitoring during DBS-implantation
Wårdell et al., 2007-01-14 2
The aim of the study was to investigate if laser Doppler perfusion monitoring (LDPM) can be
used in order to differentiate between gray and white matter and to what extent microvascular
perfusion can be recorded in the deep brain structures during stereotactic neurosurgery. An
optical probe constructed to fit in the Leksell® Stereotactic System was used for
measurements along the trajectory and in the targets (GPi, STN, Zi, Thalamus) during the
implantation of DBS-leads (n = 22). The total backscattered light intensity (TLI) reflecting
the grayness of the tissue, and the microvascular perfusion was captured at 128 sites.
Heartbeat-synchronized pulsations were found at all perfusion recordings. In six sites the
perfusion was more than 6 times higher than the closest neighbor. TLI was significantly
higher (p < 0.005) and the perfusion significantly lower (p < 0.005) in positions identified as
white matter in the respective MRI-batch. The measurements imply that LDPM has the
potential to be used as an intracerebral guidance tool.
Wårdell et al., 2007-01-14 3
During intervention in the deep brain structures, by e.g. radio frequency (RF) lesioning ,
deep brain stimulation (DBS)  or neural cell grafting , safe, accurate and precise
intracerebral navigation towards the pre-calculated target is imperative. Impedance methods
can discriminate between gray matter, white matter and cerebrospinal fluid . Physiological
mapping using microelectrode recording (MER) or confirmation of anatomical targets using
macro-stimulation are methods used to confirm targeting during stereotactic neurosurgery .
MER, however, may cause an increased risk of bleeding and does not constitute a guarantee
for proper targeting ,. Furthermore, the MER signals may be difficult to interpret and
may be misleading . In order to overcome this, promising attempts have recently been
made in order to introduce automatic signal processing algorithms and visualization of
microelectrode recording signals during insertion of the electrodes towards the targets [9,10].
One possible way to increase the precision, accuracy and safety in localizing the pre-
calculated target during stereotactic procedures could be intracerebral recordings of optical
signals. Giller and co-workers [11,12] presented a system using a probe with optical fibers for
near-infrared intracranial measurements during stereotactic procedures in humans. By
analyzing the slope of the reflected light spectra in the wavelength range 700-850 nm a
separation between white and gray matter was possible. Our group recently showed that the
same result is achieved using a fixed wavelength within the suggested spectral interval .
Thus, 780 nm is a commonly applicable wavelength in laser Doppler perfusion monitors
(LDPM) which indicates that LDPM can be used to record not only microvascular blood
perfusion but also tissue boundaries during stereotactic neurosurgery.
Laser Doppler perfusion monitoring  and imaging  are optical methods based on the
detection of backscattered laser light from a small tissue volume containing both Doppler-
shifted and un-shifted scattered photons originating from the static tissue and the moving red
blood cells. A perfusion value is defined as the concentration of moving red blood cells times
their mean velocity and related to relative changes in the tissue’s microcirculation, whereas
the total backscattered light intensity (TLI) corresponds to the tissue’s reflectivity at the laser
wavelength used by the LDPM-system. Since the beginning of the 1980s, the laser Doppler
Wårdell et al., 2007-01-14 4
technique has been used in a wide range of applications e.g. for assessment of skin reactions
[16,17], burns  skin tumors , for the intra-operative monitoring of myocardial blood
perfusion during bypass surgery  and during the evaluation of cortical brain
microcirculation . A review of the laser Doppler technique and its applications has been
presented by Nilsson and co-workers .
In this study it is explored if LDPM can be used for measurements of tissue type and
microcirculation in the deep brain structures during stereotactic neurosurgery in humans. The
aim of the study was to investigate if a modified LDPM system could be used in order to
differentiate between gray and white matter and to what extent microvascular perfusion could
be recorded along the trajectory and in the target area.
Material and Methods
Seventeen patients (seven women, age 40-72, mean ± s.d. = 56 11) referred for unilateral or
bilateral DBS-implantation for the treatment of Parkinson’s disease, essential tremor,
dystonia or pain were included in the study. In total 22 leads were implanted. The study was
approved by the local ethics committees at the University Hospitals in Linköping and Umeå
(D. no. M182-04) and informed consent was received from the patients. Measurements were
performed during implantations in the subthalamic nucleus (STN, n = 11), the globus pallidus
internus (GPi, n = 4), the caudal zona incerta (Zi, n = 2), and the thalamus (Th, n = 5: ventral
intermediate nucleus [Vim, n = 2]; ventral posterolateral nucleus [VPL, n = 2]; ventral
posteromedial nucleus [VPM, n = 1]. Eleven procedures took place at Umeå University
Hospital and six at Linköping University Hospital.
Laser Doppler system and measurement probe
A system for intracerebral recordings of both microvascular perfusion and total backscattered
light intensity (TLI) was set-up. It comprises a laser Doppler perfusion monitor (Periflux
5000, Perimed AB, Sweden) a specially designed optical probe and a personal computer with
software for acquisition, data analysis and presentation. The software, developed in Labview
(National Instruments Inc., USA), made it possible to sample, store and present both the
Wårdell et al., 2007-01-14 5
perfusion and TLI signals on-line. Methods for postprocessing of the captured data were
developed in Matlab (Mathworks Inc., USA). An overview of the system is presented in
Figure 1. Overview of the laser Doppler perfusion monitoring system used for intracerebral
measurements. The probe with fiber optics is connected to the light source and the detector
unit in the Periflux. The TLI and perfusion signals are then sampled into a personal computer
for processing and presentation.
The measurement probe was constructed with dimensions similar to a standard
radiofrequency electrode. In order to fit in the Leksell® Stereotactic System (Elekta
Instrument AB, Sweden) the probe’s outer shaft was rigid, made of stainless steel and had a
functional length of 190 mm. The diameter was 2.2 mm except for the last 30 mm towards the
tip where it was 1.5 mm. Four optical fibers (step index, = 240 m) were aligned along the
interior side of the probe towards the tip. Two of the fibers were used for laser Doppler
recordings and two for reflection spectral measurements . With this probe design, the
tissue directly in front of the tip was investigated.
Wårdell et al., 2007-01-14 6
The LDPM-system uses a low power, solid state laser (1mW, = 780 nm). During recording
the laser light is guided through one of the optical fibers toward the tissue. After light
interaction with the moving red blood cells in the tissue, backscattered, Doppler-broadened
laser light is guided back through a second fiber to a detector unit in the Periflux. The light is
processed to a value scaled linearly to tissue perfusion within a bandwidth of 0.02 to 12 kHz.
In order to be able to capture fast perfusion changes, the time constant () of the system was
set to 0.03 s. The total range of the perfusion and TLI signals was 0 - 999 arbitrary units (a.u.)
and 0 - 10 a.u. respectively.
Surgical technique and stereotactic imaging
The surgical procedures differed slightly between the departments of neurosurgery in Umeå
and Linköping. In general, the procedures were performed as described below. All procedures
except for two cases of dystonia were performed under local anesthesia.
Stereotactic imaging was performed after placement of the Leksell® coordinate frame model
G (Elekta Instrument AB, Sweden). The different targets in the thalamus were identified
according to atlas-coordinates on stereotactic CT-studies. The target in the Vim was chosen
6-7 mm anterior to the posterior commissure (PC), at the level of the intercommissural line
(ICL), and 13-15 mm lateral to the midline of the 3rd ventricle. The target in the VPM and the
VPL was 2-3 mm anterior to the PC, 2-3 mm below the ICL and 10 mm lateral to the midline
of the 3rd ventricle in VPM and 15 mm in the VPL.
Direct anatomical targeting was performed in the STN, GPi and Zi on stereotactic MRI-
studies performed with a 1.5 Tesla scanner (Philips Intera, The Netherlands). Contiguous
trans-axial slices of 2 mm thickness, T2-weighted sequences for STN and Zi and T1-weighted
for GPi, were collected. The pallidal target was visually chosen 2 mm anterior to the mid-
commissural point, 2 -3 mm lateral of the pallido-capsular border on the axial slices, and
about 2 mm above the optic tract on the coronal slices. The target in the STN was visually
chosen at the line connecting the anterior borders of the nucleus Ruber, at the level of their
maximal diameter, and approximately 1.5 mm lateral to the medial border of the STN. The
depth was, when needed, corrected according to the lower border of the STN as seen on the
Wårdell et al., 2007-01-14 7
coronal slices. The target in the caudal Zi was visually chosen slightly medial to the medial
border of the STN, in the posterior part of the posterior third of the STN. The stereotactic
images were exported to the Framelink Planning Station® (Medtronic, Minneapolis, MN,
USA) or Leksell® Surgiplan (Elekta Instrument AB, Sweden) for calculation of target and
The LDPM system was calibrated (motility standard, PF1001, Perimed AB, Sweden) prior to
sterilization of the measurement probe. This certified a best-fit range of the system so both
low and high perfusion values could be recorded in the same measurement session. To
investigate the stability of the system a control measurement in motility was always carried
out immediately after finalizing the measurement procedure.
At surgery a 14 mm burr-hole was placed according to the coordinates of the target allowing
a trajectory avoiding penetration of the ventricles. Opening of the dura and a corticotomy
were performed and the optical probe was introduced towards the target. During the
introduction of the probe, measurements were performed at pre-designated points, starting at
40 or 30 mm from the target and continuing at 20, 10, 5 and 2.5 mm from the target as well as
in the pre-calculated target area. Each recording lasted for 60 seconds, the total measurement
session took about 15 minutes (in several procedures this also included diffuse reflection
spectral measurements, see ). Two sequences also included cortex data and in two
subjects the target measurement was omitted. In total 128 measurements where completed
during insertion of the probe. Along two tracks one additional measurement was also
obtained during withdrawal of the probe. During the recordings notes were taken of: recorded
heart rate from the patient monitoring system, if the patient suffered from tremor or if other
external interference with the recorded signal was present.
The optical probe was thereafter removed and replaced with the Medtronic DBS electrode
3387® or 3389® (Medtronic, Minneapolis, MN, USA) for macro-stimulation. The effect of
intra-operative stimulation on symptoms such as tremor, rigidity, hypokinesia, and eventual
induction of dyskinesias was evaluated and possible side effects, such as visual phenomena,
capsular response, speech alterations and paresthesias were sought for. After achieving a
Wårdell et al., 2007-01-14 8
satisfactory clinical response the electrode position was verified with a stereotactic CT and/or
MRI, before implantation of the neurostimulator.
All measurement sequences were visually inspected and a 30 seconds section was selected
from each recording for analysis of the perfusion and the TLI. Sections considered as external
noise caused by e.g. known fiber movement artifacts or over-bending of the fiber were
excluded in this selection. From the perfusion-signal: mean (m), standard deviation (s.d.),
peak-to-peak (p-p) and heart rate (HR) were calculated. Furthermore the signal was studied
regarding vasomotion and other types of possibly temporal variations caused by the
microcirculation. For each TLI-sequence, the mean and standard deviation were calculated
and if applicable the peak-to-peak. In order to identify the tissue type at the measurement site,
inspection of pre-operative MRI was done using the surgical planning systems. The identified
tissue was graded as white matter, gray matter or mixed. The mixed group contained
positions where no clear classification could be made. Along each trajectory, the TLI and
perfusion at the corresponding white and gray tissue sites were averaged. The identified data
were then grouped both according to white and gray tissue and the brain target aimed at. Data
were tested using the Wilcoxon paired signed rank test or the Mann Whitney U-test for
grouped samples. P values < 0.05 were considered significant.
During all 22 DBS-implantations, both the microvascular perfusion and total backscattered
light intensity were easily recorded and displayed on-line with the designed system and
probe. Post-operative measurements in motility showed that the TLI signal was stable and
varied less than 1.3%. The calibration procedure certified that the perfusion signals were
comparable from time-to-time.
An example of a trajectory with the measurement sites towards GPi superimposed on the
Schaltenbrand-Wharen +2 mm coronal image is illustrated in Fig. 2a. The corresponding
perfusion and TLI measurement sequences for respective sites are presented in Fig. 2b-c.
Pulsative variations in the perfusion signal agreed with the monitored heart rate. They were
Wårdell et al., 2007-01-14 9
visible in all captured perfusion signals, but with varying peak-to-peak. In Fig. 2d-e,
perfusion- and TLI averaged over 30 seconds are presented. The perfusion increased towards
the target whereas the TLI presented an inverse relationship with higher values at 30 and 20
mm. Recordings towards STN are exemplified on a patient in Fig. 3. Along this trajectory,
superimposed on the -3 mm coronal image, elevated perfusion with a high peak-to-peak was
found 5 mm from the target. In addition, the perfusion signal demonstrated a pronounced
vasomotion pattern with 6 cycles/min. superimposed on the pulsations originating from the
heartbeat (Fig. 3b). The existence of a blood vessel close to the measurement site was
confirmed during post-operative image inspection of both the coronal and axial T2-weighted
MRI. Average perfusion and TLI data related to respective measurement position are
presented in Fig. 3c-d.
Figure 2. Example of perfusion and TLI signals captured from a typical measurement towards
GPi: a) Probe trajectory and measurement sites superimposed on the Schaltenbrand-Wharen
atlas, + 2 mm coronal image . b) Time traces of perfusion, the pulsative variations
correspond to the monitored heartbeat. c) Time traces of the TLI. d) Averaged perfusion (m ±
s.d.) plotted against measurement site. e) Averaged TLI (m) plotted against the measurement
Wårdell et al., 2007-01-14 10
Figure 3. Example of a recording towards the STN. a) Probe trajectory and measurement
sites are superimposed on the Schaltenbrand-Wharen atlas, -3 mm coronal image . b)
Time traces of the perfusion, a highly pulsative perfusion signal was found 5 mm from the
target. Heartbeat-related pulsations are superimposed on a 6 cycle/min. vasomotion pattern.
c) Perfusion (m ± s.d.) and d) TLI (m) in relation to the measurement sites.
A summary of all the microvascular perfusion measurements (n = 128) recorded when the
probe was inserted, and grouped according to target aimed at, is presented in Fig. 4a-c (GPi,
STN, Zi) and Fig. 5a (Th). All presented values represent the average value from a
registration covering 30 seconds. In six out of 128 measurement positions the perfusion was
more than six times higher than at least one of the closest neighbors (marked with circles in
Wårdell et al., 2007-01-14 11
Fig. 4 a-b and Fig. 5a, Tab. 1). The average perfusion for these high perfusion spots was
309.8 166.0 a.u. When removing these “outliers”, the average microvascular perfusion of
all remaining recordings was 30.7 18.4 a.u. (n = 122).
Figure 4. Summary of perfusion (a-c) and TLI (d-f) recordings grouped according to target
aimed at (GPi, STN, Zi). High perfusion spots and very low TLI in relation to high perfusion
spots are marked with circles.
A summary of all captured TLI grouped according to target aimed at, is presented in Fig. 4d-f
(GPi, STN, Zi) and Fig. 5b (Th). In general the curves started with elevated TLI and leveled
out towards the target. Two of the five lowest TLI values were recorded in the cortex and
three in sites related to high perfusion spots (marked with circles in Fig. 4d, 5b). A peak-to-
peak in the TLI, with a frequency corresponding to the heartbeat, was found at two of the
high perfusion spots (Tab. 1).
Along ten of the trajectories it was possible to identify measurement positions above the
target as both white and gray tissue from respective MRI-stack. The TLI was significantly
higher (p < 0.005) and the perfusion significant lower (p < 0.005) in positions identified as
white tissue. The targets in GPi had a significant lower TLI than the STN (p < 0.005). There
was, however, no significant difference in perfusion between GPi and STN.
Wårdell et al., 2007-01-14 12
Figure 5. Summary of perfusion (a) and TLI (b) recordings along the trajectories towards
targets in the thalamus (VPL, VPM, Vim). High perfusion spots and very low TLI in relation
to high perfusion spots are marked with circles.
In this study, laser Doppler perfusion data captured along pre-calculated trajectories towards
individual nuclei in the deep brain structures have been presented. Compared to other
intracerebral methods the LDPM-technique has the added advantage of recording not only the
tissue’s total backscattered light intensity reflecting the tissue’s grayness, but also the
Wårdell et al., 2007-01-14 13
microcirculation in the vicinity of the probe tip. This implies that the technique has a potential
to detect not only gray-white boundaries but also increased blood flow along the trajectory.
Table 1. Measurement sites along the trajectory with elevated perfusion compared to
surrounding sites. Two of the recordings were repeated during withdrawal of the probe.
mean ± s.d. p-p
GPi, 20 mm
498 ± 123
228 ± 24
GPi, 10 mm 179 ± 27 130 1.3 -
STN, 30 mm 167 ± 9 52 3.0 -
STN, 5 mm 238 ± 53 125 4.6 -
VPM, 10 mm 234 ± 11 74 3.7 -
Vim, 20 mm
542 ± 86
235 ± 17
High pulsative microvascular perfusion was registered at six out of 128 measurement sites
(Fig. 4a-b, Fig. 5a, Tab. 1). In two of these (20 mm from GPi and Vim respectively) the
signal was more than 25 times higher than at the surrounding measurement positions.
Repeated recordings when the probe was withdrawn confirmed the elevated perfusion,
however, with reduced values. This is probably caused by a slightly different sampling
volume surrounding the probe tip. When the probe is inserted the tissue in front of the tip is
investigated, whereas when it is removed the tissue is disrupted. Along one of the STN-
trajectories a highly elevated perfusion with a pronounced vasomotion pattern superimposed
Wårdell et al., 2007-01-14 14
on the heartbeat was registered. Post-operative image inspection revealed the existence of a
very small vessel in the vicinity of the probe. It is very likely that also the remaining
recordings related to high perfusion were captured close to a similar vessel structure,
however, not visible with the used MRI-protocol. Several of the high perfusion spots were
accompanied by a lower TLI than could be expected (Fig. 4d, 5b, Tab. 1). These low TLIs
were most likely caused by the increased absorption from blood. While two of these low TLI
also had a heartbeat-synchronized variation it may be an additional indication that the signals
were captured close to a vessel’s structure. This was, however, not consistently valid for all
high perfusion spots. By introducing 3T-MRI-scans together with Gadolinium as contrast
medium it may be possible to elucidate the relationship between high perfusion spots along
the trajectories, and closely related vessel structures.
In general the TLI was higher at the 40 and 30 mm sites compared to in the target area,
indicating white tissue. Statistical analysis between TLI captured in white and gray tissue
based on MRI was, however, only possible for 10 out of 17 trajectories. The reduced number
of samples for comparison was caused by difficulty in judging the tissue type from the MRI
at the pre-selected measurement positions, and several sites were therefore graded as mixed.
Despite this, a significant difference between white and gray matter was found. This is in
agreement with the reflection spectral measurements performed by Antonsson et al., . In
this study, different spectral signatures and intensities were found for gray and white matter.
A high correlation (r = 0.99, p < 0.0001, n = 78) was found between the tissue’s reflectivity at
the wavelength 780 nm (the LDPM wavelength) and spectral content along a slope ranging
from 750-800 nm. Giller and colleagues [11,12] have also presented reflection spectra
captured during stereotactic neurosurgery with the ability to separate between white, and in
their case, cortex-gray matter, within the same wavelength interval.
With the used set-up, the LDPM signals were only registered at fixed pre-designated
positions along the trajectories and several high perfusion spots could have been missed. In
future studies the resolution along the trajectory can be increased by recording the perfusion
and TLI at e.g. mm-distances. For the TLI it might even be possible to perform continuous
measurements during insertion of the electrode and thus increase the spatial resolution and the