Hyperpolarized Functional Magnetic Resonance of Murine Skeletal Muscle Enabled by Multiple Tracer-Paradigm Synchronizations

Measuring metabolism's time- and space-dependent responses upon stimulation lies at the core of functional magnetic resonance imaging. While focusing on water's sole resonance, further insight could arise from monitoring the temporal responses arising from the metabolites themselves, in what is known as functional magnetic resonance spectroscopy. Performing these measurements in real time, however, is severely challenged by the short functional timescales and low concentrations of natural metabolites. Dissolution dynamic nuclear polarization is an emerging technique that can potentially alleviate this, as it provides a massive sensitivity enhancement allowing one to probe low-concentration tracers and products in a single-scan. Still, conventional implementations of this hyperpolarization approach are not immediately amenable to the repeated acquisitions needed in real-time functional settings. This work proposes a strategy for functional magnetic resonance of hyperpolarized metabolites that bypasses this limitation, and enables the observation of real-time metabolic changes through the synchronization of stimuli-triggered, multiple-bolus injections of the metabolic tracer 13C1-pyruvate. This new approach is demonstrated with paradigms tailored to reveal in vivo thresholds of murine hind-limb skeletal muscle activation, involving the conversion of 13C1-pyruvate to 13C1-lactate and 13C1-alanine. These functional hind-limb studies revealed that graded skeletal muscle stimulation causes commensurate increases in glycolytic metabolism in a frequency- and amplitude-dependent fashion, that can be monitored on the seconds/minutes timescale using dissolution dynamic nuclear polarization. Spectroscopic imaging further allowed the in vivo visualization of uptake, transformation and distribution of the tracer and products, in fast-twitch glycolytic and in slow-twitch oxidative muscle fiber groups. While these studies open vistas in time and sensitivity for metabolic functional magnetic resonance studies in muscle, the simplicity of our approach makes this technique amenable to a wide range of functional metabolic tracer studies.


Introduction
Functional magnetic resonance imaging (fMRI) is an established technology mapping regions of physiological activations and their responses to well-defined stimuli [1]. This mapping is enabled by the changes that physiological processes -and blood oxygenation in particular -bring about in the water's relaxation properties [2,3]. An alternative, potentially more insightful method to monitor real-time physiology is provided by functional magnetic resonance spectroscopy (fMRS). Instead of focusing on the solvent's signature, fMRS reveals changes in molecular concentrations by monitoring the event-related responses of their spectral peak intensities [4,5]. Although clearly more closely related to physiological function than water, these metabolite-based observations are considerably challenged by the low concentrations being targeted and by the difficulties involved in reliably and steadily suppressing the H 2 O resonance. Dissolution dynamic nuclear polarization (dDNP) of 13 C nuclei, is an emerging technology that could provide a potential answer to these challenges [6,7]. When executed at high fields under cryogenic conditions, DNP can endow stable isotope tracers with upwards of 10 4 signal enhancements, making up for the low concentration metabolic imbalance. Moreover, 13 C observations are free from solvent background complications. Dissolution DNP could therefore provide an avenue to monitor real-time metabolic events in vivo, with a sensitivity and temporal resolution that are unreachable otherwise.
Limiting this potential are a number of factors, including finite hyperpolarization lifetimes that restrict the in vivo observation window to a few minutes at the most, and lengthy sample preparation times requiring hours for hyperpolarizing common tracers such as 13 C 1 -pyruvic acid [8]. At the conclusion of this process, a dDNP experiment generates a few milliliters of hyperpolarized solution, from which a single bolus with maximal volume defined by the animal being analyzed, is usually administered. For normal mice experiments under conventional infusion conditions, this bolus contains ca. 20-25% of the tracer solution generated by the hyperpolarizer's dissolution process. This administration leads to a ''first-pass'' kinetic experiment, whose overall duration will be determined by the in vivo signal decay time (T 2 ) and which can be carried out up to delays given by the hyperpolarized relaxation time (T 1 ) [9,10]. Repeating such hyperpolarized experiment multiple times as needed if attempting to follow stimulation, would require recreating multiple comparable hyperpolarization/reinjection processes -for commonly used substrates this would take several hours, and cease being practical in functional studies.
The present work describes a strategy that enables one to work around this basic problem, by departing from the idea of devoting a full individual DNP dissolution to the monitoring of a single metabolic measurement. Instead use is made of the relatively long T 1 lifetimes that hyperpolarized tracers can often support at highfields in vitro, to explore the possibilities arising upon injecting the original hyperpolarized solution in multiple boluses associated with independent MRS acquisitions. In particular it is shown that by storing the hyperpolarized solution at high fields and subdividing the total dissolution volume into reduced aliquots, one can collect a series of stimulus-synchronized fMRS and functional magnetic resonance spectroscopic imaging (fMRSI) experiments within an interval bound roughly by the lifetime of the hyperpolarized substrate in the external reservoir where it is kept. This undemanding modification of the usual tracer delivery strategy is broadly applicable to many metabolic studies, and could facilitate new applications in emerging areas including cancer [10], brain [11], cardiac [12], and hepatic [13] research. In the present work, we demonstrate its potential with studies of muscle activation.
Understanding muscle metabolism is an important goal that could benefit from magnetic resonance strategies enabling spectrally and spatially functional investigations of rapidly varying metabolic concentrations. While a large body of research exists on muscle fiber types possessing markedly different phenotypes, molecular-level characterizations of realtime metabolic changes under stimulated in vivo conditions remain a challenge. Moreover, because muscle tissue is one of the largest consumers of metabolic fuel, extensive efforts are made to uncover how energetics changes in inherited and acquired diseases such as diabetes [14], muscular dystrophies [15], and myopathies [16]. In view of these challenges and features, and guided by our interest in applying dDNP to monitor stimulated muscle metabolism in vivo [17], we chose to focus on the discrimination of different muscle groups to overall physiology upon activation, as a first instance on the potential of dDNP-aided functional MRS and MRSI. To implement such studies a variety of paradigms mimicking muscular exercise were set, and MR measurements were performed in mice in synchrony with both electrical stimuli and with deliveries of hyperpolarized 13 C 1 -pyruvate into the animals. The in vivo conversion of this tracer into lactate was then followed in skeletal muscle. Judging by monitoring this glycolytic response in a purely spectroscopic mode, these studies show that muscle activation involves a graded summation of both intensity-and frequency-driven effects. In combination with spatial localization, these studies showed that stimulation brings about a recruitment of primarily fast-twitch glycolytic muscle fibers, reflecting both transient perfusion and metabolic changes.

Results
Conventional hyperpolarized MRS seeks to monitor metabolism by following the signals that arise from a single injection of a hyperpolarized precursor. During the measurement window initiated by this bolus injection, the observed kinetics will comprise a buildup and decay of the tracer -in the present case 13 C 1pyruvate-followed by subsequent buildups and decays of metabolic by-products such as 13 C 1 -lactate and 13 C 1 -alanine ( Figure 1a). An example of such hyperpolarized measurement is shown in Figure 1b, for a single bolus injection of hyperpolarized 13 C 1 -pyruvate into a mouse's tail vein. The detection in this case involved monitoring the bulk 13 C signals arising from the hindlimb skeletal muscles, using a single-pulse sequence replayed with 1 s repetition times and detecting the ensuing amplitudes with a suitably positioned surface coil. The spectral peaks that can then be resolved exhibit characteristic buildup and decay times, from which metabolic rates can be derived [9,18,19]. It has been recently shown that these fluxes characterizing muscle metabolism can exhibit significant changes upon subjecting the animal to a variety of external stimuli [17]. To determine how such external events change the metabolic system as a function of the stimulus duration and/or intensity would require preparing and monitoring a consistent array of hyperpolarized samples for each measurement; with each such process taking approximately 1 hour, applications to monitor real-time changes of in vivo metabolism in such settings would be severely limited. Figure 1c illustrates an alternative tracer delivery strategy that allows one to alleviate this limitation. In it a single milliliter-sized hyperpolarized sample has been prepared, and fractions of it (100 mL/2s injection) have been injected into an animal to monitor its metabolism ca. 30 s apart, while keeping the rest of the sample at ,1 T fields to preserve its nuclear hyperpolarization. Notice how multiple metabolic events can be monitored in such fashion; notice as well ( Figure 1d) the good correspondence between a conventional experiment involving a single 400 mL/8 s tracer injection, and the spectral sum arising from the multi-bolus experiment. It follows from this that the number of events that can be monitored in this fashion will be ultimately limited by the duration of the MRS/MRSI acquisition sequence and by the polarization lifetime of the tracer in its highfield reservoir; the volume of initial hyperpolarized solution prepared is usually in excess for mice experiments, and hence of secondary importance in defining this number.
In order to validate the metabolic relevance of this technique, a series of multi-bolus tests were conducted under fixed metabolic conditions, and compared against conventional, single-injection benchmark results. These comparisons relied on monitoring the time-dependencies of normalized metaboliteto-total-carbon (MtoC) ratios for hyperpolarized 13 C 1 -pyruvate, 13 C 1 -lactate, and 13 C 1 -alanine, a simple calculation [17] which frees the ensuing results from relaxation-derived effects -both ex and in situat the expense of assuming that these are equal for all metabolites. Figure 2a shows the time-dependent ratios then arising from conventional and multi-bolus injection approaches. The ensuing results can be modeled by a single kinetic event comprising the catabolism of 13 C 1 -pyruvate and ensuing anabolism of 13 C 1 -lactate and 13 C 1 -alanine, each characterized by a single exponential depending on rates k Pyr, k Lac and k Ala (Fig. 1a) [17]; these effective 13 C 1 -label exchange rates vary in turn, according to the metabolites' pool sizes and the enzymatic activity at the instant of the injection [20]. The multi-bolus MtoC trajectory reveals four sharply delineated events reflecting each of the individual injections; these epochs are labeled as I-IV and quantitatively analyzed for each injection in Figure 2b, whose fits confirm that all injections report on an identical metabolic status. Figure 2c expands this by presenting the exponential rates extracted from repeated multi-bolus and single bolus measurements in hind-limb skeletal muscle experiments on mice (n = 4). The various multi-bolus rates are statistically identical for each repeated measurement, even if these exceed by approximately two-fold their single-bolus measured counterparts. This systematic deviation probably reflects the fact that upon injecting a larger bolus of pyruvate at supra-physiological concentrations, the hyperpolarized tracer exceeds the metabolic capacity and thereby displays reduced reaction rates [21,22].
With this corroboration as background, the hyperpolarized multi-bolus MRS experiments were synchronized with a functional model. The activation paradigm chosen mimics the effects of strenuous exercise, by exploiting the response of skeletal muscle to the electrical stimulation of the hind limb sciatic nerve [23]. Figure 3a illustrates the timing and results of these single-pulse/ acquire experiments, whereby four 100 mL boluses were injected every ca. 30 s, and a series of 13 C MR spectra were acquired with a 1 s time resolution. The first of these boluses (epoch I) was administered as control prior to any stimulation; thereafter, each remaining MRS observation was preceded by 10 s periods of electrical stimulation. This resulted in the functional responses labeled as II-IV in Figures 3a, 3b. A first feature evidenced by these functional tests is an increased uptake of hyperpolarized pyruvate, as witnessed by an overall increase in the absolute signals of all metabolites upon activation. Translation of the 13 C MRS data into MtoC plots also indicates that the 13 C 1 -lactate ratio increases notably more than their 13 C 1 -pyruvate and 13 C 1 -alanine counterparts, confirming the onset of glycolytic activation. Figures 3b and 3c quantify these changes elicited by the functional stimulation; notice how rates in the Epoch I run resemble the nonstimulated controls shown in Figure 2c, while stimulation causes a definite change in the quantified metabolic rate coefficients kevidencing an increase of the label exchange due to the augmented metabolite pools present in the tissue under such stimulus conditions [24][25][26][27]. Figure 3c in particular reveals the statistically significant treppe, or staircase, effects in the metabolic response of the 13 C 1 -pyruvate and 13 C 1 -lactate tracer in the hind limb skeletal muscle, from the repeated application of this functional stimulation paradigm. From a physiological standpoint, these steps are hallmark of the early period of stimulus action where substances such as lactate, potassium, and carbon dioxide exert an augmenting affect on tissue activation as their concentration increases, while for extended stimulation periods such substances diminish tissue function [28].
In order to clarify whether the stimulation-dependent metabolic measurements summarized in Figure 3 exhibit a response that is dictated by a frequency-dependent and/or by an amplitudedependent recruitment of the muscle fibers responsible for the contraction, the experimental fMRS approach was modified as illustrated in Figure 4a. By contrast to what is shown in Figure 3, this paradigm incorporates now different variable stimuli preceding each epoch. These changes included stimulation blocks that varied either the frequency or the applied voltage of the electrical impulse trains. Metabolite-to-total carbon trajectories arising for  representative cases as a function of electrical stimulation are shown in Figure 4b. Analysis of these data leads to the summary in Figure 4c, summarizing the rates of lactate appearance and pyruvate consumption, for n = 4 animals and for an array of experiments where the frequencies of the stimulation paradigm were varied between 1 and 100 Hz, and the applied voltages varied between 1 and 10 V. This panel reveals a graded response whereby metabolic fluxes vary in proportion to -but non-linearly with-the activation's amplitude. This response exhibits for all voltages an inflection when the stimuli reach 50 Hz, corresponding to the onset of tetanic impulse summation maximizing muscle fiber contraction [29]. At sub-tetanic frequencies Figure 4c also evidences a response whereby graded metabolism -and by definition, the number of involved motor fibers-increases as a function of the applied voltage.
All fMRS experiments described so far involved non-discriminate spatial observations, whereby disk-like regions ca. 8 mm in diameter and 6 mm in depth were monitored from mice hind limbs via suitable positioning of an external surface coil. Skeletal muscle, however, consists of multiple distinct fiber types that can be discriminated on the basis of their metabolism as fast-twitchoxidative/glycolytic (FOG), fast-twitch-glycolytic (FG) and slowtwitch-oxidative (SO) fibers [30]. The degree of recruitment of these muscles is determined by the amplitude and frequency of the effort being requested [31], and hence in principle different fibers should be distinguishable by our stimulation paradigm. In order to implement such discrimination, it is necessary to endow the kind of experiments described above with an ability to discriminate the spatial origin of the metabolic responses. To this effect the multibolus hyperpolarized paradigm was modified into an MRSI experiment, as shown in Fig. 5a. The experiment involved a first bolus injection (133 mL/4s) followed by a 10 s delay to allow for metabolic evolution [32] and by a 7 s long hyperpolarized 13 C 2D MRSI acquisition; this was followed by 10 s of functional stimulation and by a second bolus injection (133 mL/4s) and 13 C MRSI collection; the relaxation of the muscle from an activated to a relaxed state was monitored in epoch III with a final bolus injection (133 mL/4s) and MRSI acquisition. As is customary in both conventional fMRI and hyperpolarized MRSI experiments, these 13 C acquisitions were complemented with anatomical 1 H multi-scan MRI images that enabled a clearer identification of the various fiber types, by overlay display on top of the fMRSI 13 C data. On the basis of these anatomical reference images and of literature comparisons [33,34], the hyperpolarized 13 C 1 -pyruvate and 13 C 1 -lactate resonances were mapped onto major hind-lib muscle groups including the (TA) tibialis anterior, (E) extensor digitorum longus, (F) flexor digitorum longus, (G m ) medial gastrocnemius, (G l ) lateral gastrocnemius, and (S) the soleus muscle (Figure 5b). Despite extensive efforts, epoch I experiments revealed only a minor presence of 13 C 1 -pyruvate and no 13 C 1lactate altogether. This reflects the combined effects of MRSI's reduced overall sensitivity vis-à-vis MRS, coupled to the weak uptake of the hyperpolarized tracer in muscle prior to functional  activation (e.g., Fig. 1c). By contrast, the metabolic stimulation and higher rates of transport brought about by the functional paradigm enabled the acquisition of high-resolution maps for both 13 C 1pyruvate and 13 C 1 -lactate in epoch II. A similar activated poststimulation metabolic state was also observed in epoch III -despite the fact that no actual stimuli preceded this acquisition. Metabolic map detections in subsequent non-stimulated epochs, acquired using an overall smaller multiple bolus volume reflected reduced sensitivity to smaller bolus volumes, and losses in the polarization of the external tracer in intervals longer than T 1 of the tracer reservoir.
It follows from these fMRSI maps, that the 13 C tracer influx is primarily registered with the most glycolytic, outer muscle fibers -in particular the gastrocnemius and extensor muscles. In order to better quantify these spatial metabolic variations, Figure 5c presents the summed 13 C frequency spectra arising from each of the segmented regions of interest identified in panel 5b. The frequency spectra are arranged from left to right according to the percentage of fast-glycolytic muscle fibers as previously determined in rodents [30,31]. Here G tot (total gastrocnemius), E and F muscles contain greater than 50% FG fibers and less than 10% SO fibers, TA contains less than 40% FG and is mostly FOG, and S contains approximately no FG fibers and is almost 90% SO [30]. In epoch I only small amounts of 13 C 1 -pyruvate are detected, predominantly in FG muscles. Epoch II reveals substantial increases in 13 C-pyruvate and 13 C-lactate in FG gastrocnemius muscles, yielding 2-and 10-fold integrated intensity increases, respectively, over those observed in epoch I. The soleus exhibited a ,2-fold increase in 13 C 1 -pyruvate upon stimulation, while the 13 C 1 -lactate signal increased 5-fold. The overall increases of 13 C 1 -pyruvate in all muscles indicate that stimulation leads to enhanced tracer perfusion, as expected from increases in blood flow previously measured in rodents [35]. The ensuing increase in 13 C 1 -lactate then reflects both a higher tracer perfusion, as well as an enhanced metabolism. In order to focus on metabolic acceleration and normalize out the effects of T 1 relaxation over the multiple epochs, the lactate/pyruvate ratios were calculated in pre-stimulation, post-stimulation and refractory periods. Taking the gastrocnemius and soleus as exemplary FG and SO fibers, the pre-stimulus period (epoch I) evidenced noise/pyruvate ratios of ,0.35 for both muscles. Following 10 s of applied stimulus (epoch II) both FG and SO fibers exhibited similar increases in their pyruvate peaks but distinct changes in their lactates, which rose ,5-and 3.5-fold over the noise, respectively. This difference in the hyperpolarized lactate signal in FG and SO fibers mirrors the increases in tissue lactate that has been determined ex vivo under similar stimulation conditions [25,26]. The lactate/pyruvate ratio in the refractory period (epoch III), measured approximately 35 s after the end of the stimulus, reveals lactate and pyruvate reductions for both FG and SO muscle fibers -but these remain ca. 150% higher for the former than the latter, vis-à-vis their pre-stimulation baseline values suggesting that FG and SO fibers remain in metabolically stimulated states in proportion to their initial glycolytic activation. Interestingly, in the refractory period, 13 C-pyruvate signal intensities remain as in epoch II, while 50% reductions in the 13 C lactate peaks suggest specific metabolic changes. This could be reflecting an oxidation of lactate via the lactatepyruvate shuttle [36,37], which will reduce both the intra-and extra-cellular lactate pools generated during exercise. Another possibility is that these fibers are reflecting an early intravasation of muscle lactate, known to occur over longer intervals poststimulation [38]. However, complementary 13 C MRS experiments whereby thermally polarized 13 C 3 -pyruvate was injected under similar stimulus and timing paradigms as in Figure 5's fMRSI experiments, failed to evidence such increases of 13 Clactate signals in aliquots of extracted plasma that would result from perfusion-assisted intravasation, in accord with previous measurements under similar stimulation conditions [27].

Discussion
Hyperpolarized 13 C tracers can detect in vivo, real-time metabolic responses for specific tissues using paradigms and protocols akin to those employed in functional magnetic resonance investigations. This requires modifying the conventional dissolution DNP into a multi-bolus operation; under suitable conditions this can provide unidirectional initial metabolic rates for enzymemediated conversions for multiple molecular species, reaction-time dependencies, correlations between metabolism and the intensity of the applied stimulus, and metabolic information discriminated according to position in space. The eventual limit to the amount and the quality of the information that will become amenable by this route, will be given by the number of boluses that can be delivered, by the volume administered in each injection, by the rate of the metabolic process being targeted, by the acquisition strategy used, and ultimately by the lifetime of the hyperpolarized reservoir. In our studies the number of boluses was varied between three and four, but the overall volume administered was kept bound at 400 mL. This is substantially smaller than the overall volume delivered by the hyperpolarizer and it was dictated by physiological considerations; if working with bigger animals, larger boluses could surely be administered. Alternatively, it is possible to use an increasing the number of smaller injections delivered at various intervals while keeping the overall injected volume bound.
In unpublished experiments we did in fact successfully use volumes ,100 mL, and were able to deliver them in both shorter and longer inter-bolus time intervals in this study. However, signal-tonoise plays an increasingly limiting role at these lower effective concentrations and longer intervals, while short time intervals were not ideal for allowing tracer label exchange to appreciably proceed for our kinetic analysis. Moreover, improvements in experimental efficiency based on more sensitive scanners or reliance on automatic injections [39], could provide needed signal-to-noise for delivering more aliquots possessing smaller volumes and administered over longer durations. Additionally, given the emergence of a new generation of hardware capable of simultaneously polarizing and delivering multiple samples minutes apart [40], hyphenation with a multi-bolus technique could in principle enable literally dozens of real-time measurements collected on a single suitable subject. This would make the method much more akin to conventional fMRI measurements. The tracer reservoir used in our studies was placed in a 1 T field straying from the magnet; under these conditions 13 C 1 -pyruvate in vitro T 1 exceeds 60 s, enabling us to follow functional variations reliable over the course of 2-3 minutes. Over this duration optimized fast and ultra-fast spectroscopic imaging methods [41][42][43] could prove highly advantageous for implementing in fMRSI modes the kind of kinetic analyses illustrated in Figures 2 and 3 for single-pulse fMRS. Overall, we believe that these hyperpolarized spectroscopy and imaging methods together with multiple-bolus techniques can be realized in widespread applications, including in vitro and cellular settings, and in vivo; particularly if targeting wellperfused organs such as kidney, liver, and heart, and brain.
In this first demonstration, hyperpolarized multi-bolus functional techniques were applied to examine skeletal muscle activation in mice. Although tracer transport limited the signalto-noise that even hyperpolarized MR could deliver in these tissues at rest, electrical stimulation enabled first demonstrations of 13 C fMRS and fMRSI. This led to an increase in signal-to-noise; the rates determined in this manner exhibited a dependence on both stimulation frequency and amplitude, providing a novel perspective into graded muscular responses; it would be hard to envision how the short-time kinetic information provided by hyperpolarization could become available using standard in vivo stable isotope tracers or fMRI measurements in exercising muscles. It was also found that metabolic response depended on the type of muscle fiber examined, with primary contributions to the fMRS signal arising from fast-twitch glycolytic muscles supporting rapid anaerobic glycolysis upon stimulation. Fundamentally, the regulation of such metabolic responses are attributed to an enhanced metabolite transport into the tissue thanks to increased blood flow, to the enhanced action of monocarboxylate transporters facilitating the cellular fluxes [44,45], and to an upregulation of metabolic regulatory pathways [16] that preferentially route the metabolic fuel pyruvate through lactate dehydrogenase reactions under the metabolic challenge presented by our stimulation paradigms [23]. Overall, the multi-bolus assays hereby introduced yield robust kinetic information, in a new real-time kind of measurement monitoring diverse tissue responses in vivo. While these protocols were implemented in healthy mice they can be readily extended to discriminate metabolism on muscle disorders. DNP-enhanced fMRS and fMRSI protocols could also have broad potential for studying processes involving a large array of other tissues, and can also be readily extended to in vitro and in-cell applications.

Animal Care and Maintenance
Animal protocols and maintenance were in accord with the guidelines of the Committee on Animals of the Weizmann Institute of Science and were approved by this committee (Permit Application Number: 07771212-3). Female 20 week-old ICR mice were maintained in non-reversed light conditions and were provided with standard chow and water ad libitum prior to the experiments. Animal respiration was continually monitored and body temperature maintained at 37uC by circulating warm water through the animal holder during magnetic resonance experiments.

Dynamic Nuclear Polarization
Hyperpolarization of neat 13 C 1 -pyruvic acid (Sigma Isotec) and 15 mM OX-063 Trityl radical (Oxford Instruments) was conducted at 95 GHz with 50 mW microwave powers in a Hypersense polarizer (Oxford Instruments) operating at 1.4 K. In the multi-bolus experiments the solution was stored at ,1 T in the fringe field; signal lifetimes measured from the decay of the multi-bolus envelope revealed for this in vitro sample a T 1 = 62.8966.71 s. In vivo hyperpolarized experiments were conducted by injecting 60 mM 13 C 1 -pyruvate neutralized to pH<7.6, either in single or multi-bolus volumes as indicated in the text.

Magnetic Resonance Experiments
All experiments were conducted on a 4.7 T, 30 cm bore scanner (Biospec, Bruker), using an 8 mm 1 H/ 13 C surface coil (Doty Scientific). 13 C MRS acquisitions were began upon initiating the hyperpolarizer's dissolution sequence. A total of 256 acquisitions (2048 time domain points per acquisition, 4 kHz spectral bandwidths) were acquired in each data set using an inter-scan repetition of 1 s and broadband radio-frequency pulse angles set at 15u in conventional injections and at 30u in the multi-bolus experiments. Each time trace was zero-filled to 4096 points, Fourier transformed, and processed with a 20 Hz Gaussian apodization; kinetics were analyzed using Matlab (Mathworks) routines as described previously [17]. MRSI experiments were conducted using a centric 868 phase-encoded matrix spanning a 1.2561.25 cm 2 field of view, beginning 10 s after hyperpolarized bolus injections. Ramped-flip angle [46] slice-selective Gaussian pulses were used to obtain free induction decays of 512 time points over 100 ms acquisition times (4 kHz spectral bandwidth); as the acquisition time equaled the phase-encode repetition time, total scan times were 6.7 s. MRSI data sets were reconstructed on Matlab and jMRUI-5 [47] by spatial zero-filling to 16616 and time domain zero filling to 1024 points followed by 15 Hz Lorentzian apodization. The nominal in-plane resolution of the 13 C images was 0.7860.78 mm 2 . Metabolite peaks were quantified using AMARES in the jMRUI-5 software to generate hyperpolarized 13 C-pyruvate and 13 C-lactate maps, and quantification error surfaces were used to threshold the maps shown. The metabolic maps are normalized to 5-times the noise level of the acquisition. Reference 1 H gradient echo images were obtained using TR/TE 5.38 ms/1 s for 1.2561.25 cm 2 field, with a 1286128 phase encode matrix.

Functional Stimulation Protocol
Animals were anesthetized with sodium pentobarbital and electrodes were surgically fastened to the left sciatic nerve of the animal as we described previously [17]. The tail vein was cannulated and the animal fixed in its position inside the magnet and maintained with 1-2% isoflurane in O 2 at 1 L/min. The electrical stimulation paradigm consisted of variable amplitude (1 V-10 V) 200 ms square pulses played either with a repetition frequency ranging from 1 Hz to 100 Hz, or as 10 ms trains repeated at frequency of 10 Hz.