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The neonatal rabbit brain shows prolonged postnatal development both structurally and physiologically. We use noninvasive near-IR frequency-domain optical spectroscopy (NIRS) and magnetic resonance imaging (MRI) to follow early developmental changes in cerebral oxygenation and anatomy, respectively. Four groups of animals are measured: NIRS in normals, MRI in normals, and both NIRS and MRI with hypoxia-ischemia (HI) (diffusion MRI staging). NIRS and/or MRI are performed from P3 (postnatal day=P) up to P76. NIRS is performed on awake animals with a frequency-domain tissue photometer. Absolute values of oxyhemoglobin concentration ([HbO2]), deoxyhemoglobin concentration ([HbR]), total hemoglobin concentration (HbT), and hemoglobin saturation (StO2) are calculated. The brains of all animals appeared to be maturing as shown in the diffusion tensor MRI. Mean optical coefficients (reduced scattering) remained unchanged in all animals throughout. StO2 increased in all animals (40% at P9 to 65% at P43) and there are no differences between normal, HI controls, and HI brains. The measured increase in StO2 is in agreement with the reported increase in blood flow during the first 2 months of life in rabbits. HbT, which reflects blood volume, peaked at postnatal day P17, as expected since the capillary density increases up to P17 when the microvasculature matures.
The brain of the newborn human is immature at birth and it continues to mature postnatally both structurally and physiologically. In premature infants (24 to 32 weeks gestation), the brain undergoes the following changes: cortical layering (all six layers of the cortex are formed), myelination and myelin maturation, neural organization (neuronal alignment, orientation, layering), proliferation of dendrites, and formation of synapses.1 The cortical vascularity is developed before the subcortical vascularity and the cortical vessels have abundant anastomotic channels supplying the cortex.
Currently there is no technology that enables easy, continuous, safe, and noninvasive monitoring of human brain development and that provides functional and metabolic information. Near-IR spectroscopy (NIRS) can acquire measures of cerebral oxygenation in real time, which is especially suitable for measurements in all neonates. Positron emission tomography (PET) studies in humans have shown regional changes of glucose utilization, oxygen consumption, and blood flow with brain maturation.2–7 However, because these studies require intravenous injection of radioactive tracers, this methodology, even though noninvasive, can be justified for use in human neonates only in a diagnostic capacity where the benefit to be gained from its diagnostic ability outweighs the inherrent risk to the patient from using this technology. PET studies are not ethically justified in normal human neonates. NIRS and magnetic resonance imaging (MRI) both hold appeal for brain development studies because they are safe and noninvasive. In the past 2 decades, NIRS has been tested as a means to monitor the brain’s cerebral oxygenation status8–11 and to investigate brain function12–15 in neonates. MRI has been used to assess brain maturation in preterm infants.16–23 Also, a handful of functional MRI (fMRI) studies of neonates have shown an age-dependent change in the functional signal response to visual stimulation.24–29
Longitudinal MRI studies of human neonates are rare.30 While human newborns within the first 2 postnatal weeks can be fed, swaddled, and put to sleep then into the MR scanner, older neonates are usually scanned at night or during their nap time. The scans on the older neonates are therefore more labor intensive and less successful and more often involve sedation of the infants to prevent motion artifacts in the images. Because of the need for anesthesia, frequent MRI measurements on human neonates and infants are less desirable unless there is a diagnostic or prognostic need.
To investigate the sensitivity of NIRS to hemoglobin changes due to brain development, a large number of measurements on several subjects over a long period of time is required. To our knowledge, there are no optical studies that have tested the reproducibility of optical measurements in such an extensive way as has been done in this study. Brain maturation in the neonatal rabbit was an ideal in vivo system to interrogate to verify that our optical measurements were reproducible and to investigate hemoglobin changes during brain development from birth to adolescence.
As stated, the neonatal rabbit’s brain is immature at birth and is comparable to a preterm human fetus of approximately 26 to 34-weeks gestation. The neonatal rabbit’s brain also shows prolonged postnatal development and mimics some aspects of the human preterm brain in the way it reacts to various brain insults such as hypoxia and hypoxia ischemia.31–33 Structurally, myelination continues in the corpus callosum, internal capsule, and the centrum semiovale up to the fourth postpartum week. In addition, physiological changes such as increases in local cerebral blood flow,31 capillary density,34,35 oxidative metabolism, and glucose utilization36 occur in tandem with these structural changes.
In our study, we used both NIRS and MRI to investigate cerebral vascular maturation and microstructural development in the normal and pathological neonatal rabbit brain. NIRS was used to follow changes in postnatal cerebral hemoglobin concentration and oxygenation. MRI was used to follow changes with age in surface-to-brain and cortical thickness, myelination progression, and brain water content as well as to stage the ischemic brain injury due to hypoxia ischemia.
NIRS measurements were performed with a frequency-domain tissue spectrometer37 (Model No. 96208, ISS, Inc., Champaign, Illinois). This instrument uses two parallel photomultiplier tube detectors (PMTs) and 16 time-shared laser diodes (eight emitting at 690 nm and eight emitting at 830 nm). The frequency of intensity modulation is 110 MHz, and heterodyne detection was performed with a cross-correlation frequency of 5 kHz. Laser diodes and PMTs are coupled to fiber optics. The optical fibers are arranged in two identical flexible plastic probes. Each probe consists of one fiber bundle (made of five 400-µm multimode glass fibers) connected to a PMT detector and four fiber bundles (each made of two 400-µm multimode glass fiber) connected to eight lasers. The tips of the illuminating and collecting fiber bundles in each probe are arranged along a line, with the source fibers at distances of 0.5, 0.8, 1.1, and 1.5 cm from the collecting bundle. The lasers are multiplexed at a rate of 100 Hz, so that an entire cycle over the eight sources is completed in 80 ms. We used the frequency-domain multidistance method for the quantitative measurement of the absorption (μa) and reduced scattering () coefficients of brain tissue.38 From the absorption coefficient measured at two wavelengths, the absolute values of the oxy-hemoglobin concentration ([HbO2]), deoxy-hemoglobin concentration ([HbR]), total hemoglobin concentration ([HbT]), and hemoglobin saturation ([StO2]) were calculated. The numeric values found for HbO2 , HbR, HbT, and StO2 using the NIRS method reflect blood found in the microvasculature, i.e., chiefly in the capillaries, with some contribution from the venules and arterioles.39
MRI was performed on a 4.7-T small-bore GE Omega scanner using two different gradient sets depending on the animal age [8 cm i.d., 80 G/cm for ages up to post natal day 21 (P21) and 22 cm i.d., 7 G/cm for age P46). A transmit/receive surface rf coil was used to acquire MRI scans according to the protocols described in Sect. 3.2. Animals were anesthetized during scanning, and were positioned in a purpose-built plastic holder that supported the animal’s body in a prone position. The head was held within a contoured thermoplastic head holder under the receiver coil. Temperature was maintained within the magnet using a circulating warm water pad, and rectal temperature, heart rate, and oxygen saturation SaO2 (by pulse oximetry) were measured and recorded continuously throughout scanning.
Four groups of animals were used in this study: (1) normal control animals whose brains were scanned using NIRS, (2) normal control animals whose brains were scanned using MRI, (3) hypoxia-ischemia (HI) and HI control animals (surgical ligation of one common carotid artery only) whose brains were scanned using both NIRS and MRI, and (4) normal control animals from which blood was drawn at different time points to measure the hemoglobin spectrum.
Optical measurements were performed on eight normal control rabbits, from the same litter, every 2 to 3 days from 3 days (P3, i.e., postnatal day 3) to 60 days (P60) of age. Before the optical measurements the animals were shaved and weighed. Data were acquired at two wavelengths and from four source-detector separation distances with two identical probes. Each probe was calibrated against a silicon phantom of known optical properties to calibrate the light emitted by the eight laser sources. The probe consisted of a small piece of rubber to which the fibers were permanently fixed with epoxy. To mark the probe’s position for easy day-to-day repositioning, within the initial test area of the rabbit’s head, during subsequent experiments a rectangular area of fur (of the same dimension of the probe) was shaved at the start of the study and this area was shaved again before every subsequent measurement. The measurements were performed while the animals were awake and one experimenter held each rabbit to keep it still. A second experimenter placed the optical probe in contact with the rabbit’s scalp. This experimenter made sure the probe was in good contact with the skin, holding it in position and applying slight pressure. The probe was randomly positioned to the left and right of the midline taking care to avoid the saggital sinus. Data collection did not begin until the animal was relaxed and still. Data were acquired for 8 s, and then the probe was lifted and repositioned over the shaved area of the head. The procedure was repeated 10 times with each probe. The optical measurements lasted about 3 to 5 min for each animal. Immediately after the measurements, the animals were returned to their mother’s care. Optical measurements of the brain were taken on these animals three times per week from P3 to P60 days (2 months). The rabbits’ arterial oxygenation saturation and heart rate were measured using a commercial pulse oximeter fitted with a neonatal sensor.
A second litter of animals (n = 3) was used to measure normal brain development. MRI measurements of the brains were taken using the following imaging parameter, in all cases in the coronal plane: spin-echo, echo-planar imaging (EPI) diffusion-weighted images (images show areas of tissue undergoing membrane depolarization, i.e., acute cell swelling, see also next section) were acquired in six noncollinear directions (diffusion tensor, DTI): field of view (FOV), 30 mm; 1-mm slice thickness; 64×64 pixels; echo time (TE), 45 ms; repetition time (TR), 8 s; and b value= 1450 in six directions. The T2 mapping using EPI was also performed, with the same parameters as previously but with TE varied from 21 to 101 ms. The T2-weighted spin-echo images were also acquired: TE, 70 ms; TR, 4 s; FOV, 30 mm; 256 × 128 pixels; and 1-mm slice, eight slices. These animals were measured at the following time points: P9, P14, P21, and P31.
A third litter of six rabbits was used for the HI experiments as described by D’Arceuil et al.40 and were studied using both NIRS and MRI. Briefly, on day 9, all animals were anesthetized with 3% Isoflurane, and the right common carotid artery (CCA) was surgically isolated and ligated with 4.0 silk suture. Right CCA ligation results in the right brain hemisphere being more susceptible to suffer ischemia when the animal is subjected to hypoxia. The brains of CCA ligation or HI control animals have been shown in previous MRI studies to be the same as normal control animals and were measured with NIRS to ensure that there were no measureable differences in cerebral oxygenation as a result of the surgical CCA ligation. On P10, four of these animals were then anesthetized and received baseline MRI scans, as already described. Following baseline MRI scans, the HI insult was staged by using diffusion MRI to determine the duration of hypoxia as follows: serial dynamic diffusion weighted EPI scanning (TR, 3.2 s; TE, 45 ms; and 4 b values 0, 1450, 0, and 1450 along the Z axis) was started approximately 5 min before initiation of hypoxia and continued for up to 3 h. Image data were stored to disk and then reconstructed in near real time, and the diffusion-weighted images were viewed on an offline computer screen which was updated approximately every 30 s.
Hypoxia was induced by reducing the fraction of inspired oxygen (FiO2) by nitrogen dilution (the breathing gas mixture was switched to 60% nitrogen and 40% air, i.e., 8.4% FiO2) and the anesthesia level maintained at between 0.65 and 1.0%. Arterial oxygen saturation was monitored carefully using a pulse oximeter. The extent of cellular depolarization within the brain was determined using diffusion weighted magnetic resonance (DWI) imaging, which is acutely sensitive to cell swelling.41,42 Acute cell swelling results in areas of hyperintensity in the DWI images or hypointensity in the fitted apparent diffusion coefficient (ADC) maps.43 Images were acquired before, during, and after the hypoxic interval. Hypoxia was continued until diffusion hyperintensity was observed. At this point, hypoxia was reversed and scanning continued until the diffusion changes resolved completely. In this way, we define the duration of hypoxia not as a fixed time period but rather as the time required to achieve critical energy failure in the cells (and subsequently widespread membrane depolarization leading to reduced ADC, and hyperintensity on diffusion-weighted images). After recovery, follow-up scans were acquired (as for the normal animals) at P17, P31 and P43.
Optical measurements of the brain were also taken on these animals once a week from P3 to P76 days (2.5 months). To investigate any differences in brain development due to preferential right brain hemisphere insult, the optical probes were positioned within both the right and left cerebral hemispheres and the measurements already described (in the normal control group) were repeated and data from each hemisphere were stored separately.
A group of six animals (five neonates plus one adult) was used to measure maturational changes in the hemoglobin spectrum. Blood was drawn from P3 (n=1), P3 (n=2), P10 (n=1), P17 (n=1), and an adult. Blood taken from the neonates was a terminal procedure performed under deep anesthesia. Whole blood was heparinized and diluted with normal saline 1:100. These blood samples were 100% oxygenated having been exposed to the oxygen in the air as well as in the water used for dilution. In one case (P17), we added yeast to the diluted blood, sealed the cuvette, and obtained a hemoglobin spectrum of the deoxygenated blood sample.44–46 The spectral measurements were made using a fiberoptic spectrometer (S2000, Ocean Optics, Inc.) with a 100-µm slit and 600 lines/mm grating coupled with a 400-µm optical fiber. The light source used was a tungsten halogen lamp (LS-1, Ocean Optics, Inc.), coupled with another 400-µm optical fiber to deliver light to the sample. Absorption spectra of the blood samples contained in a 1-cm plastic cuvette were measured in the 530- to 1100-nm spectral range with an optical resolution of 4 nm.
The amplitude (ac) and phase (ph) data from four source-detector distances (ranging from 0.5 to 1.5 cm) were analyzed using the frequency-domain (FD) multidistance method38 to calculate absorption and reduced scattering coefficients at two wavelengths (690 and 830 nm). Using literature values for hemoglobin extinction coefficients,47 we calculated the absolute values of oxy-, deoxy-, and total hemoglobin concentration, as well as the hemoglobin saturation. We corrected for water absorption assuming a percentage of 75% of water in the tissue. The frequency-domain multidistance method is appropriate for detecting optical properties of the underlying tissue for superficial layer thicknesses of up to 4 mm (Ref. 48). We verified that this holds for the range of distances used in this study, by performing preliminary experiments in layered phantoms, with various optical properties, and various thicknesses of the superficial layer. It takes only 80 ms to obtain a saturation measurement with the FD system in the configuration used. Because we were interested in the baseline optical properties, however, we averaged 100 points (i.e., 8 s). This reduced not only the instrumental noise, but also the contributions from physiological noise (i.e., slow and fast hemoglobin fluctuations due to arterial pulsation and respiration). We paid particular attention to the reproducibility of the optical measurements in each animal. Of the 20 measurements of 100 points each collected in each animal with two probes during every measurement session, we discarded the measurements for which (1) we had motion artifacts due to sudden movements of the animal; (2) the slopes of amplitude [ln(r2ac)] and phase versus distance were not straight lines (R2<0.95), caused by nonuniform optical coupling of the probe with the head of the animal; (3) the blood parameters calculated from a measurement differed more than one standard deviation from the average of all of the measurements, because of imprecise positioning of the probe on the head of the animal. The average of the blood parameters for each measurement session was obtained by averaging the results over each rabbit group.
MRI data fitting and handling were done using custom image data processing and display software (MRVision, MRVision Co., Winchester, Massachusetts). The serial DWI data acquired during hypoxia were processed at each scan time point. A two-point fit was performed on the signal intensity decay curves of the baseline (i.e., zero diffusion weighted) images (M0, with b=0) and diffusion weighted images (M, with b = 1450 s/mm2), where the b value is a measure of the amount of diffusion sensitization applied and is dependent on the gradient strength and timing parameters used.49 Measurements of the distance in millimeters from scalp to brain, and cortical thickness were derived from the T2-weighted images in the rostral, middle, and caudal aspect of the head at P9, P17, P31, and P43.
The diffusion tensor data were processed to generate ADC trace maps and fractional anisotropy (FA) maps.50
The rabbit weights as a function of age are shown in Fig. 1 for the normal control group. On average, from 3 to 60 days of age, the rabbit weights increased from 0.1 to 1.7 kg. The weight increased linearly from day 3 to day 20, at a rate of 11 g/day (R2=0.98). From day 21 to day 60, the growth rate increased to 37 g/day (R2=1). Arterial oxygenation ranged from 97 to 100%, and heart rate from 250 to 290 beats/minute.
Reproducibility measurements on the phantom showed that by repositioning the probe randomly on the surface of the phantom, a maximum change of about 5% in the values of μa and was seen. By repositioning the probe in the same location on the animals’ heads there was, on average (across animals and days), an SD of 15% for μa and 10 to 20% for (~20%) when the animals were very young (P3 to P30), ~10% when they were older (P30 to P60). This translates to a reproducibility of 15% for the measurement of StO2 and HbT.
For the normal group (n=8), the brain optical properties as a function of age are reported in Fig. 2. The absorption coefficient at 690 nm was significantly higher at 830 nm during the first month of life. This translates to a low tissue oxygenation during this period. The reduced coefficient was always higher at 690 than at 830 nm, as expected, and the changes in reduced scattering with age were not strongly correlated with the changes in absorption, except for the decrease at about P30.
Figure 3 shows hemoglobin concentration and oxygenation as a function of age for the control group. StO2 increased significantly (P < 002) in all animals (from about 30% at P3 to P6 to 53 to 63% at P30 to P60), while HbT also increased significantly (P< 003) from day 3, peaked between P13 and P21 (76 µM, i.e., 0.076 mM) and showed a minimum at P30 to P32 (65 µM, i.e., 0.065 mM).
Figure 4 shows images from one slice in a representative normal control animal scanned at four time points from age P0 to P31. Figure 5 shows regions of interest (ROI) plots from this data in normal gray and white matter. Quantitative T2 data were not acquired on day 0 in this animal (a T2-weighted EPI image is shown in the figure). Contrast in the diffusion anisotropy maps (FA) increased with age as the tissue became better myelinated, while ADC and T2 contrast between GM and WM decreased (possibly due to the combined effects of white matter myelination and generally decreased tissue water content).
Measurements on the HI rabbits (n=4) and the HI controls (n=2) were performed less frequently than in the normal control group, but were continued up to P76. Figure 6 shows the results for HbT and StO2 in the HI, HI control, and normal control groups. For figure clarity, the error bars (standard errors) for the HI controls are not shown. There were no apparent differences in total hemoglobin concentration and hemoglobin oxygenation between the normal, HI controls and HI groups from P9 to P76.
The ischemic tissue regions (regions of depolarization) appear as areas of hypointensity (black areas) in the ADC maps shown in Fig. 7, acquired at the peak of hypoxia. This animal showed bilateral ischemic changes throughout the cortex and some subcortical tissue bilaterally. These hypointense regions resolved back to baseline signal intensity during recovery (by approximately 30 min). All HI animals showed an area of depolarization covering essentially the entire cortex bilaterally (19.47±6.14 mm2). ADC decreased (on average to 50% of baseline) during HI and returned to baseline post HI. FA maps in this group showed that the animal brains were maturing as expected (i.e., same as in Fig. 5). Data for all animals were pooled and a paired, two-tailed, Student’s t test was done to compare the FA values from the left and right cortex (GM). There was no significant difference between the pooled value in the left cortex compared with that of the right cortex; means±SD were 0.21±0.04 and 0.22±0.02, respectively (P =0.71). An analysis of variance was performed on the data from the following timepoints to see whether the mean FA differed with age (P0, P10, P17, P31, and P43). There was no significant difference in FA with age (P0.71).
The average distances from the scalp to the brain (in millimeters) in normal and HI groups were 1.16±0.30, 1.14±0.38, and 1.16±0.38 in the rostral (front), middle, and caudal (back) aspects of the head from age P10 up to P31, and the average value did not differ among these three areas. The average distance from the scalp to the brain increased from age P31 to age P43 in the rostral, middle, and caudal aspects of the head, respectively; 2.17±0.58, 1.96±0.41, and 2.78 ±1.23. Cortical thickness (six rabbits from the HI experiment and two normals), measured from T2-weighted images, increased on average from 1.49 mm at P10 up to 2.36 mm at P43 (see Fig. 8). There were no differences between the average measurements in control and HI animals and data from both groups were pooled to generate Fig. 8.
Figure 9 shows the oxyhemoglobin spectra measured from blood samples taken from five neonatal rabbits and one adult in the 530 to 600-nm wavelength region. The characteristic HbO peaks for rabbits at different ages comparted with that of humans51 are in agreement within experimental error (±2 nm). Our data is also in agreement with that of Holter et al.52 who measured the hemoglobin spectra on neonatal (12 to 24 h old) and adult rabbits. Small differences between the spectra do not appear to be correlated to the animal age and could be due to different reduced properties of the samples. The deoxyhemoglobin spectra measured in the 17-day-old rabbit showed characteristic deoxyhemoglobin peaks at 555 and 758 nm, again within experimental error with respect to the human deoxygenated Hb spectrum (results not shown).
We have demonstrated the potential of NIRS to be used in longitudinal studies to monitor brain hemoglobin oxygenation changes with brain maturation. Our results have shown reproducible measures of brain optical properties in 14 neonatal rabbits. Currently there are no methods that can be used to measure tissue optical properties in vivo, and there are no published NIRS data of brain optical properties in rabbits. Nevertheless, our measured optical properties are consistent with optical properties measured in piglet and in human brain.53–55
In this study, we used the diffusion equation applied to the model of a semi-infinite homogeneous medium to calculate the optical properties of brain tissue. The head of the rabbit is small, curved, and layered and is not a semi-infinite homogeneous medium, for which this model is valid, and as such there are errors that are inherent in our approximation, e.g., we expect that the surface layers of the head (skin, bone) could introduce some error in the measured optical properties of the brain. However, phantom studies reported in the literature48 have shown that when the FD multidistance method is used, superficial layers of thickness, 4 mm and smaller, do not affect the measurements of the deeper layers. In addition, we performed additional experiments using layered phantoms, with similar optical properties to brain tissue (data not shown), with the range of distances used in our experiment, to further verify that our optical signals were being measured from brain tissue.
From the anatomical MRI measurements we verified that the overall thickness of the superficial layers of skin, scalp, and skull (on the rabbits’ heads) was never larger than 3 mm, and therefore sufficiently small to be neglected. Moreover, by using only two source-detector distances of the four available to calculate the optical properties in the brain, we obtained the same results. Specifically, using any of the following three source-detector distance combinations 0.5 to 0.8, 0.8 to 1.1, and 1.1 to 1.5 cm, we obtained optical measurements that were within experimental error. The 0.8- to 1.1-cm set yielded results closest to those obtained by using the combination of all the four distances. The results reported in this paper are those obtained using all source detector distances.
Loss of light laterally, due to the small size of the head of the animal, can effectively result in increased measured absorption coefficients. This problem was minimized by using a small range of source-detector distances (0.5 to 1.5 cm) and our data do not seem to be have been affected by this problem. In fact, the increasing absorption coefficients in the first few days of life, when the head size also increases, is opposite to what we would expect. The combined contribution of lateral loss of light and increased measured μa should be maxi- mum when the head is smaller, i.e., at P3 and P6, not at P13, where the absorption peaks (see Fig. 3).
The inhomogeneity of the rabbit’s head and the use of small source-detector distances can cause crosstalk between the absorption and reduced scattering coefficients. In our measurements, the crosstalk between μa and does not seem to be significant. In fact, μa and at 690 nm are not correlated (r=0.28) and μa and at 830 nm are weakly correlated (r=0.57), while, as expected, at the two different wavelengths are correlated (r=0.82). In contrast, during brain development, absorption at different wavelengths is not necessarily correlated and we found μa at 690 nm and μa at 830 nm to be weakly correlated (r=0.47). This results because the independent changes in blood volume and oxygenation influence the absorption at these two wavelengths.
The value of cerebral hemoglobin oxygenation during the first 15 days of life is lower than what is usually measured in piglets56 or term human neonates.57 At birth, the rabbit brain is immature and is comparable to the brain of a premature human infant (24 to 32 weeks gestation). In fact, the piglet brain at birth is more mature than that of a term human neonate. As such, the data measured in the term human and the piglet brains are not directly comparable to that measured in the neonatal rabbit brain. In the following paragraphs, we outline some reasons for the low optically measured StO2 within the first 30 postnatal days (Fig. 4) in neonatal rabbit brain.
One possible explanation for this low StO2 value could have been the use of the extinction coefficients of hemoglobin derived from human studies, which were used to compute the hemoglobin concentrations in rabbit brain. However, this is unlikely because our measurements of blood samples taken at various ages from P3 to adult showed no differences between the hemoglobin absorption spectra of neonatal rabbits, adult rabbits, and humans. Moreover, the values of the peripheral arterial oxygenation measured with the pulse oximeter on the neonatal rabbits were, as expected, 97 to 100%. If the neonatal hemoglobin spectra differed substantially from that of human hemoglobin, the SaO2 measured by the pulse oximeter would also be affected, possibly resulting in lower than normal readings. Another possible reason is the presence of an additional, unknown absorber in the neonatal brain that affects the quantification of the hemoglobin concentration resulting in low StO2. This issue cannot be addressed in this study and may be addressed in future in another NIRS study that uses more than two wavelengths of light.
It is also possible that at this particular stage of the brain’s development a low StO2 is perfectly normal given the immature state of the brain and the rigors of the birthing process. During the birthing process the fetus experiences “normal birth asphyxia” due to the repeated reduction in uterine blood flow as a result of uterine contractions. Hence, the fetus is born in a state of “physiological asphyxia,“ which is normally relieved after the newborn takes the first few breaths. Newborn rabbits, like other newborn animals and humans, must undergo certain essential adjustments directly after birth. The transition to extrauterine life involves the following two major events: (1) establishment of the neonatal circulation and (2) establishment of the pulmonary circulation. It has been reported in the literature that at birth there is globally decreased cerebral blood flow (CBF) and in newborn lambs, humans, and rabbits the cortex is preferentially supplied with blood. CBF is tailored to meet the energy and oxygen demands of the brain tissue.58
There is very little mylenation in the neonatal rabbit’s brain and the cortical vasculature is immature. CBF and glucose utilization (i.e., oxidative capacity) are low. Tuor31 and Tuor et al.35 using autoradiographic methods, showed that capillary density, oxidative metabolism, and local CBF change with development in the neonatal rabbit brain. Directly after birth (days 1 and 2), CBF is low and varies regionally. By day 17, there was markedly increased CBF (200 to 350%) compared to days 1 and 2, and CBF continued to increase in most brain regions up to 40 days postnatally. In these animals, capillary density increased from birth and matured to couple with cerebral metabolism at about postnatal day 17 then showed no significant change thereafter.
StO2 measured optically reflects the balance between oxygen delivery and consumption in the tissue microvasculature, i.e., chiefly in the capillaries. In neonatal rabbits, the immaturity of the brain at birth, the low cerebral blood flow and glucose utilization coupled with the adjustment to extrauterine life and the immaturity of the brain is the likely explanation for the low measured StO2 (on average 30% at P3). Thereafter, StO2 increased with postnatal age (up to P76) as the brain matures structurally and functionally and the animals become adjusted to postnatal life. This result is in keeping with data published on premature human neonates which reported low StO2 values at birth59 (StO2 values within the first 1 to 3 days of life were 50, 66, and 76% respectively).
HbT measured optically reflects blood volume in the illuminated tissue and is indirectly correlated to capillary density. In our measurements, HbT peaked at P17, consistent with an initial capillary density increase in the first 20 postnatal days reported by Tuor et al.35 After this period when the microvasculature matures, tissue volume and vasculature both increase, resulting in constant HbT. However, local cerebral blood flow autoregulation depends on the maturity of the tissue and is not optimum below P17. These maturational changes support our optical data which showed a peak HbT between 15 and 17 days with no significant change thereafter, supporting a model of evolving, i.e., increasing, resting blood flow.
From our optical measurements, there were no differences, compared to normal controls, in tissue hemoglobin oxygenation or total hemoglobin concentration in brain tissue that suffered transient HI. Similarly, the longitudinal MRI data did not show appreciable differences in these two groups. However, the serial T2 and diffusion MRI data clearly demonstrated the major structural changes going on in the maturing tissue. The deep WM structures, subcortical WM, corpus callosum, and internal capsule, showed increased FA up to P31, indicative of continuing myelination (Fig. 6). This same process is also likely the cause of a sustained reduction in free water content in both gray and white matter, resulting in the progressively decreased T2 and ADC in these tissues.
Previous work in this HI model33 showed that there are selective, bilateral ischemic changes in the CA1/CA2 and CA3 cortical brain regions and in the periventricular WM, which were significantly greater on the side of ligation. These changes were not associated with inflammatory necrotic but rather apoptotic changes. The area of tissue measured in the HI and in the normal control animals may be somewhat dif- ferent due to some selective cell loss, i.e., we were measuring a population of cells with normal oxygenation. Our method may not be able to detect such small changes in the cerebral tissue oxygenation after HI. The fact that we measured these animals directly after (P10) then 1 week later may also mean that we may have missed the window where the apoptotic cells were cleared swiftly and surgically from the surrounding brain tissue. Also, it has to be considered that this may in fact suggest that a moderate (as shown from previous histological data33) and transient ischemic insult such as this may not have resulted in permanent changes in tissue oxygenation and blood volume.
In human brain metabolism, myelination, vascularization, and neuronal and synaptic plasticity change rapidly in the first year of life. NIRS is an optimal technique to measure cerebral hemoglobin concentration and oxygenation in both animals and human neonates. Our longitudinal studies in neonatal rabbits demonstrated the feasibility of this method for safe, noninvasive measurement of cerebral oxygenation. Our results are in agreement with previous invasive studies. StO2 measured optically, which reflects the balance between oxygen delivery and consumption in the tissue microvasculature, increased steadily up to P76. O2 consumption in the maturing tissues increases in tandem with increased capillary density and blood flow. HbT reflects increasing blood volume which peaked at P17 as expected since the capillary density increases mostly during this period when the microvasculature finally matures. Thereafter, the increase in the cerebral vasculature is matched by increased cerebral tissue volume, resulting in constant blood volume. Serial MRI measurements provide complementary microstructural information to the cerebral oxygenation data acquired by NIRS. Indeed, incorporating the MRI structural data into a more complex model of light scattering may improve the analysis of the NIRS data in future. A more severe HI insult that results in secondary energy failure 24 to 72 h after recovery may lend some new insights into the dynamics of pathological cerebral hemodynamics during brain maturation in this model. Future work will concentrate on more severe insults with more frequent NIRS and MRI measurements.
We would like to thank René Michels and Felipe Jain for technical assistance during the measurements and David Boas and Enrico Gratton for helpful discussions. This research was supported by the U.S. National Institutes of Health (NIH) Grant No. RO1-HD42908. This work was also made possible through the inspiration and generous support of George Cowan.
H. E. D’Arceuil, Neuroradiology Section, Martinos Center for Biomedical Imaging, Room 2301, Building 149, 13th Street, Charlestown, Massachusetts 02129, E-mail: ude.dravrah.hgm.rmn@neleh.
M. P. Hotakainen, Martinos Center for Biomedical Imaging, Department of Radiology, Massachusetts General Hospital, Charlestown, Massachusetts and Cognitive Brain Research Unit, Department of Psychology, University of Helsinki, Finland.
C. Liu, Martinos Center for Biomedical Imaging, Department of Radiology, Massachusetts General Hospital, Charlestown, Massachusetts.
G. Themelis, Martinos Center for Biomedical Imaging, Department of Radiology, Massachusetts General Hospital, Charlestown, Massachusetts.
A. J. de Crespigny, Neuroradiology Section, Martinos Center for Biomedical Imaging, Department of Radiology, Massachusetts General Hospital, Charlestown, Massachusetts.
M. A. Franceschini, Martinos Center for Biomedical Imaging, Department of Radiology, Massachusetts General Hospital, Charlestown, Massachusetts.