Functional MRI in Mice Lacking IP 3 -Dependent Calcium Signaling in Astrocytes

Animals

All animal procedures were approved by the corresponding ethical committee (IN-CSIC) and were performed in accordance with Spanish (law 32/2007) and European regulations (EU directive 86/609, EU decree 2001–486) and with the ARRIVE guidelines.

Four-month C57BI6/J male mice were housed in cages of four animals, with a 12-hour diurnal light cycle with food and water ad libitum. The IP₃R2 KO mice were generously donated by Dr J Chen. ¹¹

Electrophysiology

Mice (~35 g) were anesthetized with 1% to 1.5% isoflurane in oxygen at 0.4 L per minute. Temperature, oxygen saturation, heart, and breathing rates were continuously monitored (MouseOx, PanLab—Harvard Apparatus, Barcelone, Spain). Bupivacaine (0.5%, B. Braun) was injected subcutaneously under the scalp 15 minutes before the surgery. Two craniotomies were performed over the hippocampus (from bregma: −2 mm antero-posterior, 1.2 mm medio-lateral) and perforant pathway (from lambda: antero-posterior 0 mm, medio-lateral 2.6 mm) to implant recording and stimulating electrodes, respectively. Local field potentials were recorded using a 32 channel electrode (NeuroNexus, Ann Arbor, MI, USA) located across the CA1 and dentate gyrus (DG) fields of the hippocampus. Stimulating electrodes were made of platinum-iridium wire (A-M Systems, Sequim, WA, USA) as before. Excitatory postsynaptic potentials (EPSPs) were recorded in the molecular layer of the DG and population spikes (PSs) in the hilus of the DG.

Stimulation Protocols

The entorhinal cortex input to the hippocampus was stimulated using three different protocols. Single pulse stimulus to build intensity/response curves was delivered to the perforant pathway from 50 to 1,200 μA, at a frequency of 0.05 Hz (5 repetitions per intensity in total). Trains of pulses at 10 Hz were also delivered to the perforant pathway with stimulus intensities producing half maximal PS in the hilus (300 to 500 μA). Two train durations, 4 and 20 seconds, were used in both electrophysiologic and fMRI experiments. Each train was repeated in a block design with resting periods of 60 seconds between stimulation epochs. Stimulation pulses were always biphasic and charge balanced, with the cathodal pulse leading and a pulse duration of 0.2 ms. Electrical stimulation was delivered using a current source and pulse generator STG 2004 (Multichannel Systems, Reutlingen, Germany).

Functional Magnetic Resonance Imaging Study

After electrophysiologic recordings were completed, the multichannel recording electrode was removed and the stimulating electrode secured to the skull with dental cement. Animals were fixed in an MRI compatible cradle with ear and bite bars. Functional MRI data were acquired under dexmedetomidine anesthesia since it has been reported to preserve reliable and high amplitude BOLD responses compared with isoflurane. ¹² After an initial bolus of 0.4 mg/kg subcutaneously, isoflurane was progressively discontinued and substituted by a continuous infusion of dexmedetomidine (subcutaneously 0.8 mg/kg per hour). ¹² In our hands, the above regime of dexmedetomidine induces a stable anesthetic plane with constant physiologic parameters (oxygen saturation, pulse distension, breathing, and heart rate) during no more than 2 hours. Since the completion of the electrophysiologic recordings together with fMRI measurements requires longer times, we performed the electrophysiology under isoflurane and then switch to dexmedetomidine for fMRI. In a set of preliminary experiments, we first recorded and compared the evoked electrophysiologic potentials in the DG under both anesthetic regimes (data not shown). No statistically significant differences between both anesthetics were found in the electrophysiologic response (PS amplitude) to a 10-Hz, 4-secondslong stimulation train (40 pulses) as the ones used for fMRI (two-way analysis of variance for anesthesia and pulse number in the train, P > 0.05 for both factors, n = 3).

Functional MRI experiments were performed in a horizontal 7-Tesla scanner with a 30-cm diameter bore (Biospec 70/30v, Bruker Medical, Ettlingen, Germany). Functional MRI was done in 12 coronal slices using a Gradient Echo Echo-Planar Imaging sequence with the following parameters: field of view 20 × 20 mm, slice thickness 1 mm, matrix 96 × 96, segments 1, flip angle 60°, echo time 15 ms, and repetition time 2,000 ms. As anatomic reference for the functional maps, T₂-weighted anatomic images were collected using a rapid acquisition relaxation enhanced sequence: field of view 20 × 20 mm, 12 slices, slice thickness 1 mm, matrix 192 × 192, effective echo time 56 ms, repetition time 2,000 ms, and a rapid acquisition relaxation enhanced sequence factor of 8.

Data Analysis

The EPSPs were quantified as the maximal slope of the negative-going potential recorded in the molecular layer and the PS as the amplitude between the negative peak and its preceding positivity of the potential recorded in the center of the hilus. Functional MRI data were analyzed offline using custom-made software developed in MATLAB and with the statistical parametric mapping packages (SPM8, www.fil.ion.ucl.ac.uk/spm). Functional maps were generated from voxels that have a significant component for the model and are clustered together in space (P < 0.01 corrected). The propagation of functional activity was computed as the number of statistically significant voxels in a region of interest containing the hippocampal formation. The intensity of activation was computed as the average BOLD signal increase in the hippocampal region of interest (no statistical threshold applied) during stimulation and expressed as percentage of the prestimulation epochs.

RESULTS AND DISCUSSION

In the present study, we compare the electrophysiologic signature and fMRI responses in the hippocampus to direct electrical stimulation of the perforant pathway in IP₃R2 KO mice and their background strain C57BL7/6J mice (wild type, WT).

Single pulses at different intensities delivered to the perforant pathway produced the characteristic field potentials in the molecular layer (EPSP) and hilus (PS) of the DG. The waveforms, slope of the EPSP and PS amplitude and thus the input/output curves were undistinguishable in both WT and KO mice (Figures 1A to 1D). The latencies of the EPSP and PS were also identical in both genotypes (Figures 1A and 1B, insets). These results indicate that loss of IP₃R2-dependent calcium signaling in hippocampal astrocytes does not affect neuronal excitability or evoked synaptic activity of DG granule cells to perforant pathway stimulation, in good agreement with previous results for CA1 pyramidal neurons. ⁸ Since alterations in cholinergic-induced synaptic plasticity have been reported in IP₃R2 KO animals,^9,13,14 the results also suggest that neuronal modulation and synaptic plasticity may rely on diverse neuronal and astrocytic mechanisms (a recent review and discussion of this issue can be found in Araque et al ¹⁵ ). Next, we tested whether the response to trains of stimuli, as those required for eliciting robust fMRI signals, ¹⁶ was altered. The averaged EPSP slope and PS amplitude evoked by short (4 seconds, Figure 1E) as well as long (20 seconds, Figure 1F) trains of stimuli delivered to the perforant pathway were not statistically different in WT and KO mice. The dynamic evolution of evoked potentials inside the trains was also comparable in both genotypes (Supplementary Figures 1 and 2), with a tendency toward smaller activations in the last pulses of the long stimulus protocol in the KO animals (Supplementary Figure 1B).

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Figure 1.

Electrophysiologic responses in the dentate gyrus (DG) of inositol trisphosphate receptor type 2 (IP₃R2) knockout (KO) mice to perforant path stimulation. (A) Excitatory postsynaptic potential (EPSP) slope in response to single pulse stimulation delivered to the perforant pathway (PP) at increasing intensities from 0.05 to 1.2 mA. Insets show representative evoked potentials recorded in the molecular layer for different stimulation intensities. Black tracings are used for wild-type control animals and gray tracings for IP₃R2 KO mice. (B) Same as (A) but for the population spike (PS) recorded in the center of the hilus of the DG. (C) Input/output curves (EPSP/PS) of one control and one KO animal over the whole range of stimulations. (D) Input/Output curves for the linear range of stimulations averaged across the population of control (n = 18) and KO animals (n = 11). Data are fitted using linear regression with slopes and elevations showing no statistically significant differences (P = 0.879 and 0.449, respectively). (E) Average local field potentials (LFPs) recorded during a brief 4-second train stimulation of the PP at 10 Hz. No statistically significant differences (two-tail T-test) were found neither for the EPSP (P = 0.58) nor for the PS (P = 0.10) between control and KO animals (n = 18 and n = 11, respectively). (F) Average of LFPs recorded during the long 20-second train stimulation of the PP at 10 Hz. No statistically significant differences (two-tail T-test) were found neither for the EPSP (P = 0.16) nor for the PS (P = 0.37) between control and KO animals (n = 5 and n = 3, respectively).

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Figure 2.

Initiation and maintenance of blood oxygenated level-dependent functional magnetic resonance imaging (BOLD fMRI) signals in the hippocampus of inositol trisphosphate receptor type 2 (IP₃R2) knockout (KO) mice. (A) Representative example of BOLD fMRI maps in the hippocampus of wild-type control (left) and KO (right) mice upon stimulation of the perforant pathway (PP) at 10 Hz. Functional maps are color coded and overlaid on T2-anatomic scans. The color code represents the correlation (R value) of the BOLD signal with the stimulation paradigm. (B) Left, BOLD activation during the brief 4-second stimulation in the ipsilateral (ipsi) and contralateral hippocampus (contra) and over the whole brain (two-tail t-test; P = 0.44, P = 0.14, and P = 0.23, respectively) (wild type, WT n = 11; KO n = 9); Right, Number of voxels activated during the brief 4-second stimulation in the ipsilateral hippocampus (ipsi HP), contralateral HP (contra) and in total (P = 0.051, P = 0.49, and P = 0.15 respectively). (C) Global BOLD signal kinetics during 4-second stimulation, the stimulation period is marked in blue. It represents the average of 3 repetitions of 10 stimulations per animal (WT n = 11; KO n = 9). (D) Representative example of a BOLD time course during a short stimulation in WT (upper panel) and KO (lower panel). (E–G) Same as (B–D) but for the long 20-second stimulation protocol. No statistically significant differences were found for any of the measured parameters (two-tail t-test, WT n = 3, KO n = 3).

Having recorded comparable baseline electrophysiologic response in IP₃R2 KO and WT mice, we then tested in the same animals the short- and long-lasting stimulation protocols for eliciting BOLD signals in the hippocampus. Neither the extension of the activity maps across ipsilateral and contralateral hippocampal subfields (Figures 2A and 2B) nor the amplitude of the signals (Figures 2B and 2C) or the kinetics of the BOLD response (Figures 2C and 2D) were significantly altered in the absence of IP₃R2-dependent Ca²⁺ surges in astrocytes. It has been proposed that astrocytes may contribute primarily to the maintenance of hemodynamic response rather than its initiation. ¹⁷ Our results comparing 4- and 20-second stimulation protocols (Figures 2E and 2F) show that the kinetic of the BOLD signals are virtually identical at the initiation phase and maintenance, in WT and IP₃R2 KO mice. Overall, these results discard an IP₃R2-mediated contribution of astrocytes to the fMRI signal generation or the evoked neurotransmission.

Our findings complement and extend recent reports showing intact vasodilatory responses in IP₃R2 KO mice. Devor and colleagues using brief stimulations (2 seconds) of the forelimb and two-photon imaging showed in WT animals that Ca²⁺ signals in astrocytes in the sensory cortex lag behind the vascular responses and these ones are indistinguishable from those in the KO animals. ¹⁸ The result was consistent with a previous report showing that blocking mGluR type 5 upstream of the IP₃-dependent calcium release from intracellular stores did not affect the hemodynamic response in the barrel cortex to a brief sensory stimulus. ¹⁹ In a different study ²⁰ the authors used laser doppler flowmetry and direct stimulation of the largely cholinergic nucleus basalis of Meynert to increase CBF and show intact hemodynamic responses in the cortex of IP₃R2 KO animals. The authors also show intact CBF responses in barrel cortex to 20 seconds stimulation of the vibrissa. Our results build on these findings to show that the amplitude and kinetic of the BOLD fMRI signals upon stimulation of the perforant pathway are not altered in IP₃R2 KO mice, in the presence of normal neurotransmission. This result holds true for both, short and long stimulation epochs discarding a role of IP₃R2 in the maintenance, as well as the initiation, of the functional response. Furthermore, by using fMRI we show that the extension of the activity map in the brain is also preserved, discarding a role of IP₃R2-dependent calcium waves in propagating functional hyperemic responses through the astrocytes syncytium.

Collectively, these results challenge the view of IP₃-mediated Ca²⁺ changes in astrocytes as the link between the increase in local neuronal activity and vascular responses. Compensatory effects after a constitutive genetic deletion, as in the IP₃R2 KO animal, cannot be fully discarded. However, previous experiments using these animals have importantly showed a loss of Ca²⁺ activity in astrocytic cell bodies and perivascular endfeet (both spontaneous activity and evoked by neuronal stimulation or pharmacological manipulations of G_q-linked G-protein-coupled receptors) without any apparent compensation, and in the presence of an intact Ca²⁺ activity in neurons.^9,13,14 Different cell types and physiologic and metabolic compartments have been proposed to contribute to the generation of functional hemodynamic responses. ² Our results, however, do not discard the potential contribution of astrocytes to CBF regulation through different molecular mechanisms not requiring IP₃R2-mediated Ca²⁺ surges. For instance, pericytes have recently been shown to be largely involved in vasodilation ²¹ and their activation could be in part mediated through astrocytes. While further investigation is required to elucidate the mechanisms supporting neurovascular coupling, an important consideration is the potential contribution of cell types and signaling pathways independently of neuronal activation. It has been hypothesized that astroglial function unrelated to neuronal activity could be reflected in fMRI measurements. ¹⁰ The evidence discussed here indicates that the modulation of Ca²⁺ signals in astrocytes is not likely contributing to functional brain imaging.