Analysis of hyperpolarized dynamic 13C lactate imaging in a transgenic mouse model of prostate cancer

doi:10.1016/j.mri.2009.07.007

Magn Reson Imaging. Author manuscript; available in PMC 2011 April 13.

Published in final edited form as:

Magn Reson Imaging. 2010 February; 28(2): 153–162.

Published online 2009 August 19. doi: 10.1016/j.mri.2009.07.007

PMCID: PMC3075841

NIHMSID: NIHMS270406

Analysis of hyperpolarized dynamic ¹³C lactate imaging in a transgenic mouse model of prostate cancer

Janine M. Lupo,^a^* Albert P. Chen,^a Matthew L. Zierhut,^a^b Robert A. Bok,^a Charles H. Cunningham,^c John Kurhanewicz,^a^d Daniel B. Vigneron,^a^d and Sarah J. Nelson^a^d

^a Department of Radiology and Biomedical Imaging, University of California San Francisco, San Francisco, CA 94158, USA

^b UCSF/UCB Joint Graduate Group in Bioengineering, University of California San Francisco, San Francisco, CA 94158, USA

^c Department of Medical Biophysics, Sunnybrook Health Sciences Centre, Toronto, Ontario, Canada M56 2M9

^d Department of Bioengineering and Therapeutic Sciences, University of California San Francisco, San Francisco, CA 94158, USA

^* Corresponding author. UCSF Radiology, Box 2532, San Francisco, CA 94158-2532, USA. Tel.: +1 415 514 4420; fax: +1 415 514 2550. Email: janinel/at/radiology.ucsf.edu (J.M. Lupo)

The publisher's final edited version of this article is available at Magn Reson Imaging

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Abstract

This study investigated the application of an acquisition that selectively excites the [1-¹³C]lactate resonance and allows dynamic tracking of the conversion of ¹³C-lactate from hyperpolarized ¹³C-pyruvate at a high spatial resolution. In order to characterize metabolic processes occurring in a mouse model of prostate cancer, 20 sequential 3D images of ¹³C-lactate were acquired 5 s apart using a pulse sequence that incorporated a spectral–spatial excitation pulse and a flyback echo-planar readout to track the time course of newly converted ¹³C-lactate after injection of prepolarized ¹³C-pyruvate. The maximum lactate signal (MLS), full-width half-maximum (FWHM), time to the peak ¹³C-lactate signal (TTP) and area under the dynamic curve were calculated from the dynamic images of 10 TRAMP mice and two wild-type controls. The regional variation in ¹³C-lactate associated with the injected pyruvate was demonstrated by the peak of the ¹³C-lactate signal occurring earlier in the kidney than in the tumor region. The intensity of the dynamic ¹³C-lactate curves also varied spatially within the tumor, illustrating the heterogeneity in metabolism that was most prominent in more advanced stages of disease development. The MLS was significantly higher in TRAMP mice that had advanced disease.

Keywords: DNP, Hyperpolarized ¹³C, Lactate imaging, TRAMP, Prostate cancer

1. Introduction

A number of recent studies have observed higher lactate levels in prostate cancer than in normal tissue [1–3]. The concentration of lactate involves a complicated interplay among hemodynamics, cellular proliferation and energetics. As the end product of nonoxidative glycolysis, elevated lactate levels may be a valuable marker of reduced cellular oxygenation and hypoxia in cancer lesions. Even in the presence of oxygen, increased glucose uptake and conversion to lactic acid, known as the Warburg effect, are often observed due to glycolytic cells adapting to withstand a hypoxic environment [1,4]. Elevated levels of lactate have been observed in prostate cancer compared to normal prostatic tissue in proton MR spectroscopic studies that were performed on extracts of transurethral resection specimens [5] and in high-resolution magic angle spinning (HR-MAS) spectroscopic studies of both biopsy and intact surgical samples from human prostate tissue [3,6].

The TRansgenic Adenocarcinoma of Mouse Prostate (TRAMP) is a well-characterized model of prostate cancer that mimics the rapid disease progression, histopathology and metabolic changes observed in human disease [7–9]. These mice are widely used in the identification of novel biomarkers and molecular mechanisms associated with disease progression, as well as in the investigation of new strategies for characterizing and treating human prostate cancers. The use of histopathology as the definitive end point in evaluating disease progression and treatment efficacy is subjective, with significant differences between individual pathologists interpretation, and prevents the serial assessment of the associated cellular bioenergetic pathways over time. TRAMP studies would therefore greatly benefit from in vivo metabolic imaging using MR spectroscopic imaging (MRSI) with ¹³C nuclei. The low natural abundance and sensitivity of ¹³C compared to the proton pose a technical challenge using conventional approaches.

The development of dynamic nuclear polarization (DNP) techniques and a rapid dissolution procedure [10–12] has recently enabled a more than 10,000-fold enhancement of ¹³C NMR signals in solution. This method not only facilitates the detection of the prepolarized agent in vivo, but also the rapid imaging of cellular metabolism, with the downstream products being differentiated from the injected ¹³C-labeled substrate based on a change in chemical shift. [1-¹³C]Pyruvate is a good substrate for these studies due to its long longitudinal relaxation time and its key role in several important energy and biosynthesis pathways that are altered in cancer and other pathologies. Preliminary DNP studies in healthy rats, rat xenograft tumors and TRAMP mice have demonstrated more than 15% polarization of ¹³C pyruvate in solution at 3 T [11–14]. This results in a greater than 50,000-fold signal enhancement in metabolic imaging of the substrate and its metabolic products.

Time-resolved MRS acquisitions employing specialized pulse sequences were initially implemented to track the dynamic uptake of hyperpolarized ¹³C-pyruvate and its conversion to ¹³C-lactate, ¹³C-alanine and ¹³C-bicarbonate using a 3-T MR scanner [13,14]. More recently, hyperpolarized ¹³C-pyruvate studies of a TRAMP model using a rapid 3D MRSI technique [15] demonstrated significantly higher levels of ¹³C-lactate in tumor voxels compared to noncancer regions [13], and a high correlation of the ¹³C-lactate/(total ¹³C) ratio with disease progression [16]. These 3D MRSI acquisitions were acquired in 10–14 s starting at 35 s after the initiation of the hyperpolarized ¹³C-pyruvate bolus and provided valuable spatially resolved information. These techniques are relatively slow compared to the kinetics of the delivery and metabolism of pyruvate and do not easily allow the acquisition of multiple volumes over time.

Another approach to analyzing the time course of changes in ¹³C metabolism is to tailor the acquisition to excite a single resonance of interest and obtain serial images with high spatial and temporal resolution. Utilizing a new pulse sequence that incorporates a spectral–spatial rf pulse to excite a single resonance in the carbon spectrum, along with a flyback echo-planar readout trajectory for rapid imaging, can allow the acquisition of high-resolution, 3D images of ¹³C-lactate in 3.5 s [17]. This strategy can be used to track the time course of ¹³C-lactate in vivo after injection of prepolarized ¹³C-pyruvate with a temporal resolution of 5 s. In the current study, we demonstrated the feasibility of using dynamic ¹³C-lactate imaging for further characterization of prostate cancer in TRAMP mice.

2. Methods

2.1. Animal preparation and polarization methods

Two B6SJL male wild-type and 10 TRAMP mice with varying disease stages were examined in this study. Four of the TRAMP mice were classified with earlier stage disease (21–28 weeks old, 0.59 cm³ median tumor volume, 44.3 median ¹³C-lac/total-¹³C ratio) and six had more advanced disease (27–40 weeks old, 2.3 cm³ median tumor volume, 59.5 median ¹³C-lac/total-¹³C ratio). The classification was based on tumor size and appearance, and verified by the ratio of ¹³C-lactate to total ¹³C signal from ¹³C hyperpolarized 3D MRSI datasets that were acquired in the same animal with a separate bolus of prepolarized [1-¹³C]pyruvate [16]. A catheter was surgically implanted in the jugular vein of each mouse prior to the MR exam for intravenous injection of the hyperpolarized agent. All experiments were performed under a protocol approved by the UCSF Institutional Animal Care and Use Committee.

The DNP and dissolution method [10] were used to achieve 17–21% polarization for [1-¹³C]pyruvate in the solution state using a commercially available DNP polarizer (Oxford Instrument, Abingdon, UK) that was situated in a room adjacent to the MR scanner. The experimental setup and method for polarization and dissolution used in this study have been described previously by Chen et al. [13]. Briefly, a sample composed of [1-¹³C]pyruvic acid and trityl radical was cooled to 1.4 K, irradiated with microwaves for over 1 h in the presence of a 3.35-T magnetic field and then rapidly dissolved to a final substrate concentration of 80 mM. The level of polarization in the liquid state was estimated from a small aliquot of the dissolved solution using a custom-designed low-field NMR spectrometer.

The polarized solution was immediately transferred to the anesthetized animal placed on a 37°C heated pad inside the scanner via an extension tubing that was connected to the jugular vein port on the catheter. A syringe containing a ¹³C-lactate reference was placed adjacent to the animal. At the start of each dynamic scan, 0.3–0.35 ml of the hyperpolarized solution was injected intravenously over a period of 12 s, resulting in a blood concentration of approximately 9 mM pyruvate. The injection was immediately followed by a 150-μl saline flush to clear the ¹³C-pyruvate solution from the tubing.

2.2. MR Imaging protocol and parameters

The mice were scanned on a 3-T GE EXCITE MR system (Waukesha, WI, USA) equipped with multinuclear spectroscopic capabilities and a broadband amplifier, using a custom-designed ¹H/¹³C dual-tuned mouse birdcage coil for signal transmission and reception. T2-weighted proton anatomical imaging was performed in axial, sagittal and coronal planes using a fast spin-echo (FSE) sequence with TE/TR=102/4000 ms, 192×192 image matrix, FOV=10 cm (12 cm for coronal), slice thickness=2 mm (1.5 mm for coronal), NEX=6 (8 for coronal) and 10-min scan time. An additional series of axial T2-FSE proton images were acquired at the same slice locations and FOV as the lactate imaging and used to manually define anatomical regions of interests (ROIs).

The dynamic ¹³C-lactate imaging employed a pulse sequence incorporating selective excitation and a flyback echo-planar readout to acquire data from a 10×10×6.4-cm FOV 3D volume in 3.5 s, with TE/TR=9.9/53.8 ms, 10° nominal flip angle and 32×32×16 spatial matrix (3.125×3.125×4 mm voxel size). The sequence incorporated a spectral–spatial excitation pulse (180 Hz pass band, 440 Hz stop band) that selectively excited ¹³C-lactate while keeping the magnetization of ¹³C-pyruvate, ¹³C-alanine and ¹³C-pyruvate hydrate along M_z [17]. The center frequency of the pass band was set on the expected frequency of lactate, based on ¹³C MRSI studies that were acquired in the same animal. The flip angle was experimentally selected to yield the maximum signal-to-noise ratio (SNR) in the lactate images while removing most of the residual lactate signal from the previous time-point image. This means that the lactate observed over time using this technique is not cumulative and primarily reflects the amount of new lactate converted since the previous time point. A baseline scan was acquired immediately before the dynamic lactate imaging studies for normalization of quantified parameters. Dynamic imaging was started at the beginning of the injection of prepolarized ¹³C-pyruvate solution. Three-dimensional lactate images were acquired with 5-s temporal resolution and 20 time points resulting in a total acquisition time of 100 s.

As part of the same hyperpolarized MR study, the mice also underwent either 1D spatially resolved dynamic MRS or 3D ¹³C MRSI. In the wild-type control mice, a 1D dynamic spectroscopic imaging scan was performed using a flyback echo-planar readout trajectory along the z-axis (without phase encoding) to attain sixteen 10-mm slabs of spectra every 3 s [18]. A 5° flip angle, TE of 35 ms and 588-Hz bandwidth for 288 points per spectrum were utilized. The 1D dynamic MRS acquisition began at the same time as the injection of 0.35 ml of prepolarized [1-¹³C]pyruvate, and each set of spectra was acquired 64 times for a total of 189 s. For the 10 TRAMP mice, 3D ¹³C MRSI studies were performed using a double spin-echo pulse sequence [15] with a small, variable flip-angle excitation pulse [19] and adiabatic refocusing pulses. An 8×8×1 phase-encoding matrix with flyback echo-planar readout trajectory on the z-axis (8×8×16 effective matrix) was employed to cover the mouse torso and abdomen in 13.76 s at a 5×5×5.4-mm (0.135 cm³) spatial resolution and a 40×40×86.4-mm FOV, with 59 points per spectrum, and a 581-Hz bandwidth [13]. A TE/TR of 140/215 ms was utilized to symmetrically acquire the second spin echo [20]. The acquisition began 35 s after initiating the pyruvate injection because the hyperpolarized lactate signal has been shown to be relatively constant from 35 to 49 s [16].

2.3. Data processing and analysis

All imaging and spectroscopic data were transferred offline to a UNIX workstation and processed using in-house programs created in C, IDL (Research Systems, Boulder, CO, USA) or Matlab 7.1 software (MathWorks, Natick, MA, USA). The 1D dynamic spectra and 3D MRSI data were postprocessed using custom software developed in our laboratory [21,22]. Each 1D dynamic spectrum was apodized with a 10-Hz Gaussian filter and zero filled from 288 to 512 points [18], while the 3D MRSI data were apodized by a 16-Hz Gaussian filter in the time domain and zero filled from 59 to 128 points prior to Fourier transformation [13,16].

The lactate images were reconstructed offline at two spatial resolutions: the acquired resolution (3.125×3.125 mm in-plane) for quantification of the dynamic curves and a 256×256-point, sinc-interpolated image (0.39×0.39 mm in-plane resolution) for display of the individual lactate images at each time point. The dynamic curves were intensity corrected and normalized on a voxel-by-voxel basis with respect to the mean and standard deviation of the baseline acquisition, respectively. The maximum lactate signal (MLS) or peak of the dynamic curve, full-width half-maximum (FWHM) and time to the peak ¹³C-lactate signal (TTP) were measured directly from the dynamic data. The area under the dynamic curve (A) was obtained by iteratively fitting the gamma-variate function

(1)

where the area under the curve is given by A, t₀ is the bolus arrival time, α defines the skewness of the function shape and β defines the time scaling. The peak regions of the dynamic curves were fitted over five intervals (each one incrementally shifted from the previous iteration) in a nonlinear least-squares sense using a trust-region reflective Newton algorithm from Matlab for minimization. The fitting was performed on each of the five intervals three times using four, five and six points surrounding the peak. The fit coefficients that yielded the best-adjusted R² value were used in calculating the final area value. The MLS and area parameters were then normalized by both the percent polarization and the amount of hyperpolarized solution injected.

ROIs outlining the kidney and tumor or kidney and prostate regions were manually defined on the axial T2-FSE anatomical scans for the TRAMP and wild-type control mice, respectively. Regions that appeared necrotic on the T2-FSE images were avoided in the tumor ROIs. Due to the small size of these anatomical regions compared to the resolution of the dynamic lactate curves, a lactate imaging voxel was only included in a given region if 10%, 20% or 50% of the voxel lay within the normal prostate, kidney and tumor region, respectively. In addition, only voxels with lactate signal greater than three times the standard deviation of the baseline noise were included in the analysis.

Median values of each parameter (as well as the 95th percentile for MLS and area) were determined for regions containing prostate/tumor and kidney voxels. Statistical significance between parameters in the tumor and kidney regions within the same animal was determined through the use of a Wilcoxon signed rank test, while testing for significance between tumor stages employed a Wilcoxon rank sum test. Spearman rank correlation coefficients were calculated to compare ¹³C-lactate values between acquisitions.

3. Results

The optimized acquisition scheme for dynamic imaging of ¹³C-lactate provided ample SNR for measuring the time course of ¹³C-lactate production in vivo. Fig. 1 shows representative images of the kidney region at three time points (15, 25 and 30 s) and corresponding dynamic curves for two control mice scanned with either a 4° or a 10° flip angle. The SNR was reduced by a factor of 2 at 4°, resulting in images of poor contrast and dynamic curves that were difficult to quantify. A 25° flip angle yielded images and dynamic curves of nearly identical appearance as the 10° flip-angle data with similar SNR values.

Fig. 1

T2-FSE image, dynamic lactate curves and lactate images at three time points (15, 25 and 30 s) of the kidney region for two control mice scanned with either a 4° (A) or a 10° (B) flip angle. For the 25° flip angle, SNR values were (more ...)

Hyperpolarized ¹³C-lactate was observed almost immediately following the injection of the labeled pyruvate and continued to be converted over time. The 1D dynamic spectroscopic data for the control mouse displayed in Fig. 2 illustrate the effect of ¹³C-pyruvate concentration on the measured ¹³C-lactate signal. From these data, it is evident that the hyperpolarized pyruvate signal consistently reached a maximum 15 s postinjection in both the kidney and prostate regions, and by 30 s the ¹³C-pyruvate levels were nearly halved. Both the 1D dynamic spectra and dynamic lactate imaging showed maximum ¹³C-lactate levels at 10–15 s postinjection within the kidney region; where there is maximum ¹³C-pyruvate for the prostate/tumor region the maximum ¹³C-lactate was observed after 27–33 s when ¹³C-pyruvate levels were lower.

Fig. 2

Comparison between data obtained from 1D dynamic ¹³C MRS acquisition (A–C) and 3D dynamic ¹³C lactate imaging acquisition (D–F) in a male wild-type mouse. (A) A coronal T2-FSE proton image with green and red boxes delineating two of the (more ...)

Fig. 3 displays dynamic ¹³C-lactate imaging and 3D ¹³C MRSI for a representative TRAMP mouse with an advanced-stage tumor. Similarly to the control mice, the maximum intensity of the ¹³C-lactate signal was observed after ~15 s in the kidney region (Fig. 3A), but the maximum intensity of lactate was observed at ~30 s postinjection in the tumor (Fig. 3B). These images were consistent with spectral data from 3D ¹³C MRSI that were acquired between ~35 and 49 s after starting injection as shown in Fig. 3C–D, when the lactate signal from the tumor was much higher than that from the kidney. Similarly, the signal intensity of the ¹³C-lactate images acquired at 45 s was nearly three times higher in the tumor than in the kidney.

Fig. 3

Interpolated lactate images at baseline, 15, 30 and 45 s after ¹³C-pyruvate injection for slices containing (A) tumor and (B) kidney regions. The corresponding T2-FSE proton image and ¹³C 3D MRSI data are shown in (C) and (D) for the tumor and kidney, (more ...)

Variations in lactate signal intensities were apparent for different stages of disease development (Table 1). Fig. 4 demonstrates the elevated lactate levels observed with more advanced disease. As expected, only trace amounts of ¹³C lactate were seen in the normal mouse prostate. TRAMP mice in earlier stages of disease development exhibited a trend towards larger MLS and area parameters compared to the wild-type controls. TRAMP mice with more advanced-stage tumors had 60% and 86% higher median and 95th percentile MLS, respectively (P<.05), and trended towards heightened areas compared to TRAMP mice in earlier stages of disease development (Fig. 4C–D). Fig. 5A depicts the range of differences in MLS values for the individual mice, while Fig. 5B shows the tight correlation (R=0.75, Spearman rank correlation coefficient with P=.01) between MLS and ¹³C-lactate SNR from the 3D MRSI for all disease states. No significant differences in TTP or FWHM parameters were observed between the early and advanced groups. Normal mice showed a trend towards slightly lower FWHM and TTP values when compared to the TRAMP mice at all disease stages, but this difference was not statistically significant. Although parameters in the kidney region were not significantly affected by the tumor, the two healthy control mice exhibited slightly lower MSL values (17.9 and 14.1).

Table 1

Summary of parameters (median±S.D.) for wild-type (n=2), early-disease (n=4) and advanced-disease (n=6) mice

Fig. 4

Variations in ¹³C-lactate production with disease progression compared to a wild-type mouse prostate (on left). (A, B) T2-FSE images of the pelvic region which contains prostatic and/or tumor tissue (A) and corresponding dynamic lactate curves (B). The (more ...)

Fig. 5

MLS values for individual TRAMP mice grouped by disease development (A) and plotted as a function of ¹³C MRSI lactate SNR (B).

The distribution of lactate in a heterogeneous, advanced tumor is illustrated in Fig. 6. The intensity of the lactate curves varied spatially within the tumor (Fig. 6A), consistent with the known heterogeneity of this disease [3,9,16,20]. From the MLS maps in Fig. 6B, it is evident that ¹³C- lactate was generated at various locations throughout the tumor, both peripherally and adjacent to what appeared to be necrotic regions based on the anatomical images. The standard deviation of MLS values within a given tumor was 1.5 times larger for more advanced disease compared to that of earlier stage disease (6.8±2.2 vs. 2.8±1.7, respectively; P<.05).

Fig. 6

Heterogeneous distribution of lactate in a TRAMP mouse with advanced disease. (A, left to right) Sagittal, coronal and axial planes of ¹³C lactate images 25 s after ¹³C pyruvate injection overlaid on T2-FSE anatomical images and corresponding dynamic (more ...)

The dynamic lactate curves also differed between regions in the tumor and kidney for these mice as exhibited in Fig. 7 and the parameters quantified in Table 2. Note that one of the mice with more advanced disease had to be excluded from this analysis because the tumor had invaded both kidneys. The kidneys demonstrated a 1.8-fold higher median MLS value compared to the tumor region with P<.005 (2.4-fold and 1.2-fold increases for the early and advanced disease groups, respectively). Median area values in the kidney region were on average 49% higher than within the tumor with P<.005 (2.6-fold and 45% increases for tumors in early and advanced disease, respectively). The MLS was observed in the kidney 10 s before the MLS in the tumor for all mice (P=.01). Trends of 25% narrower FWHM existed in the kidneys (P=.08), although this parameter did not reach statistical significance due to one outlier (P<.05 when removed).

Fig. 7

Differences in ¹³C dynamic lactate curves between kidney and tumor regions. (A, B) Axial T2-FSE anatomical images and corresponding dynamic curves of the kidneys (A) and the tumor (B) for a representative TRAMP mouse with advanced-stage disease. The gray (more ...)

Table 2

Regional analysis of parameters (median±S.D.) in TRAMP mice

4. Discussion

The serial 3D images of [1-¹³C]lactate acquired after injection of prepolarized [1-¹³C]pyruvate clearly demonstrated the feasibility of dynamically measuring real-time changes in the formation of ¹³C-lactate in a TRAMP mouse model in vivo. Through quantitative assessment of parameters obtained from the dynamic ¹³C-lactate curves that do not rely on any prior model assumptions, we were able to characterize regional, intratumoral and disease-related variations in lactate formation in the TRAMP mouse model. While the presence of such heterogeneity is not surprising based on the histological characteristics of these tumors, this strategy for noninvasive metabolic imaging, which covers the majority of the murine body at a high spatial resolution, could be useful in determining the more aggressive part of the tumor for planning and monitoring novel experimental therapies in TRAMP mice, as well as in differentiating stages of disease that are more or less likely to respond to a given treatment. Although still preliminary, these encouraging results in the TRAMP mouse model demonstrate the potential application of this technique to improve the characterization of human prostate cancers noninvasively.

The acquisition scheme utilized in this study demonstrated the feasibility of detecting changes in pyruvate to lactate conversion in real time at a spatial resolution of 3.125×3.125×4 mm in only 3.5 s. The advantage of this technique lies in the fact that frequency selecting for only the lactate resonance preserves the amount of hyperpolarized pyruvate signal available that would have otherwise been depleted from multiple excitations. This allows for the acquisition of multiple time points at a high resolution. A flyback echo-planar readout trajectory was implemented to acquire eight lines of k-space per excitation, therefore requiring only 64 excitations for the entire volume of 16,384 voxels. For the 10° flip angle utilized in these experiments, this resulted in consumption of at least 63% of the initial available ¹³C-lactate magnetization and provided enough signal for the duration of the imaging volume. Smaller flip angles (<5°) would preserve >80% of the signal, resulting in a dynamic time course that is proportional to the total amount of lactate accumulation. The images from these low flip-angle acquisitions, however, did not possess sufficient SNR as shown in Fig. 1. Employing larger flip angles (20–25°) should, theoretically, both fully saturate the signal from the previous time point and increase SNR; however, we observed similar SNR values between acquisitions acquired with 10° and 25° flip angles, probably because the slightly lower expected SNR due to the 10° flip angle was balanced by some residual ¹³C-lactate signal from the previous time point.

The data from this study showed that the maximum amount of lactate produced was increased for more advanced disease in these TRAMP mouse tumors. The interpretation of lactate levels in the prostate region in the wild-type mouse, however, was complicated by the small size of the normal mouse prostate (~0.029 cm³) and the potential for partial voluming of surrounding tissues, as well as the low SNR in this region. In contrast, prostate tumors in TRAMP mice were significantly larger than the lactate imaging voxels, and an array of voxels could be obtained from even the smaller-size tumors. The levels of lactate observed in most tumors appeared to be elevated compared to both normal mouse prostate and the surrounding anatomy, indicating that hyperpolarized lactate has the potential to be a very sensitive biomarker for prostate cancer detection and staging, with much higher levels of ¹³C-lactate present in mice with more advanced disease. There was no overlap between tumors classified as early-stage and advanced-stage disease using the MLS parameter derived from the curves. Not only were the MLS levels stage dependent, but also the values varied substantially within the tumor, with increases in the standard deviation of MLS values for more advanced-stage disease compared to that of earlier stage disease. This supported the heightened heterogeneity that was visually observed and quantified (in terms of standard deviation) with disease progression. The lower ¹³C-lactate SNR in mice with earlier disease development may have limited the accuracy of the FWHM parameter measurement. Nonetheless, FWHM values were similar between tumor stages when removing voxels that did not reach a certain noise criteria, as were time-to-peak values, indicating comparable kinetics and time course of conversion between stages. Consequently, the increase in areas observed with tumor stage was driven mostly by the heightened MLS.

There are several main factors affecting the observed ¹³C-lactate signal, including the residual magnetization due to the flip angle, the amount of ¹³C-pyruvate present, the T1 relaxation times of the labeled pyruvate and lactate, the conversion rate of ¹³C-pyruvate to ¹³C-lactate, as well as hemodynamics. The MLS in the kidney region was both higher and occurred earlier than the lactate signal from the tumor region in all TRAMP mice, although the different time courses observed in these regions make it difficult to directly compare the amount of lactate formed. Early arrival may be due to a number of factors including higher levels of ¹³C-pyruvate present for conversion to ¹³C-lactate at earlier time points, an increased rate of conversion from ¹³C-pyruvate to ¹³C-lactate and/or a faster arrival time of the bolus due to elevated blood flow in the kidneys. The location of maximum lactate in the kidney region corresponded to the central bright region on the T2-FSE image where the long T2 signal is indicative of high fluid content. This suggests that the heightened lactate levels we see early on may be due to washout of lactate from the blood and/or other tissues such as heart and muscle. The conversion of labeled pyruvate to lactate in normal mice followed a time course that was very similar to previous data from similar experiments conducted in TRAMP mice and rat kidneys [16,23]. The timing of the MLS in the kidney from the dynamic lactate imaging data coincided within a few seconds of the maximum ¹³C-pyruvate concentration from the 1D dynamic spectroscopic data, while the slower time course of ¹³C-lactate production in the tumor region peaked when the ¹³C-pyruvate concentration has nearly halved (Fig. 2). Therefore, the lactate signal observed in the kidney region was most likely dominated by the arrival of pyruvate, whereas the local conversion of new lactate most likely influenced the observed signal in the prostate/tumor region. This further suggests that the labeled lactate observed in the kidneys was closely related to the blood flow into the organ, while labeled lactate observed within the tumor region was converted from the uptake of ¹³C-pyruvate by tumor cells where LDH activity is elevated [24]. Although it was not the aim of this work to study the metabolism of murine kidneys, the comparison of the dynamic lactate curves between different organ tissues highlights the wealth of information provided by this technique for investigating real-time metabolism.

In conclusion, this study demonstrated the feasibility of using 3D dynamic ¹³C-lactate imaging to characterize lactate formation in vivo at a high spatial and temporal resolution in a transgenic mouse model of prostate cancer. Parameters quantified from the dynamic ¹³C-lactate curves elucidated differences within individual tumors as well as between tumors with varying levels of disease progression. This new acquisition offers novel spatially resolved dynamic data of ¹³C-lactate and may improve our understanding of in vivo lactate formation in these disease models. Further studies will attempt to model the effect of hyperpolarized pyruvate concentration on this data and investigate whether the differences that were seen in the dynamic ¹³C-lactate imaging data were related to blood supply, substrate uptake and/or the rate of conversion of pyruvate to lactate.

Acknowledgments

We thank Peder Larson, Jason Crane and Vicki Zhang of the Department of Radiology and Biomedical Imaging at UCSF for their assistance with data acquisition or processing regarding this manuscript.

Footnotes

This article was presented in part at the 16th Annual Meeting of ISMRM, Toronto, Ontario, Canada, 2008.

This research was supported by NIH grants R01-EB007588, R21-EB005363 and R01-CA111291, and UC Discovery grants LSIT01–10107 and ITL-BIO04–10148 in conjunction with GE Healthcare.

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