Introduction

In the past two decades, the diagnosis of coronary artery disease (CAD) has undergone a remarkable evolution from conventional anatomical assessment of coronary arteries to an integral diagnostic approach combining anatomical and functional cardiovascular imaging modalities. Although coronary computed tomography angiography (CCTA) remains the first-line diagnostic tool for patients with suspected CAD,1 a significant proportion of patients presenting with angina show no evidence of epicardial stenosis2 and may suffer from a condition called INOCA (ischemia with no obstructive coronary arteries) caused by vasospastic disorders or microvascular dysfunction.3 The latter is associated with a reduced coronary flow reserve (CFR) and can be quantified by rest/stress myocardial perfusion imaging (MPI) with positron emission tomography (PET). As such, PET-MPI has shown a high diagnostic accuracy and independent prognostic value in INOCA patients.4 Further, a recent meta-analysis revealed that a reduced CFR was associated with an increased risk of cardiovascular and all-cause mortality across multiple disease populations, including patients with acute and chronic coronary syndromes, heart failure, aortic stenosis, heart transplant, and systemic sclerosis, demonstrating the versatile use of CFR in cardiovascular medicine.5

18F-flurpiridaz has recently been introduced as a novel radiofluorinated probe for PET-MPI.6,7,8 Despite the excellent performance characteristic of 18F-flurpiridaz, the physical half-life of 109.8 minutes constitutes a major challenge for efficient rest/stress testing protocols. Indeed, conventional 1-day protocols, as they are routinely performed with rubidium-82, 13N-ammonia or 15O-water, are hampered by the residual myocardial radioactivity from the initial 18F-flurpiridaz injection, which affects the time-activity curves (TACs) obtained after the second 18F-flurpiridaz injection. Indeed, several unanswered questions remain regarding the ideal scan duration with 18F-flurpiridaz, as well as the most accurate time frame post injection for the assessment of myocardial perfusion and CFR. Further, given the widespread use of CAD mouse models, the feasibility of rest/stress PET-MPI with 18F-flurpiridaz in mice would ultimately allow the assessment of molecular determinants affecting myocardial perfusion and CFR in these disease models.

The aim of the study was (1) to identify the optimal time frame for PET imaging following 18F-flurpiridaz injection and (2) to assess whether a simplified and image-derived model would allow sequential rest and stress PET-MPI, thereby providing accurate information on myocardial perfusion and CFR in mice.

Methods

Animals

Animal care and experimental procedures were performed in accordance with the Swiss Animal Welfare legislation and approved by the Veterinary Office of the Canton Zurich, Switzerland. Female and male FVB/N mice (N = 27, 14 females) were obtained from Janvier Labs (Le Genest-Saint-Isle, France), kept with free access to food and water and were scanned at the age of 7–8 months.

Study protocol and image acquisition

18F-Flurpiridaz radiolabeling and precursor synthesis were reported elsewhere.9,10,11 PET/CT was performed in animals that were anaesthetized using 1.3–2.0% isoflurane in oxygen-enriched air (1:1). Depth of anesthesia was monitored via respiratory rate measurement (SA Instruments, Inc., Stony Brook, USA). Body temperature was monitored using a rectal probe and was kept at 37°C with a temperature-adjusted air stream. A dose of 0.6-3.0 MBq 18F-flurpiridaz was administered via tail-vein injection 60 sec after the start of the PET scan. Tracer distribution was recorded in dynamic PET acquisition mode over a time period of 41 min, before a bolus of regadenoson (0.1 µg·g−1) and a second dose of 18F-flurpiridaz (2.2-8.1 MBq) were injected via a pre-installed intravenous catheter. PET imaging was performed with a calibrated Super Argus PET/CT scanner (Sedecal, Spain) with an axial field of view of 4.8 cm and a spatial resolution of 1.6-1.7 mm in full width at half-maximum,12,13 followed by a CT scan for anatomical information. PET data reconstruction was carried out using the manufacturer’s 2D iterative (OSEM, ordered subset expectation maximization, 2 iterations, 16 subsets) algorithm, and corrections for dead time, decay, scatter, and attenuation, at a voxel size of 0.3875 x 0.3875 x 0.775 mm3. All radioactivities were decay-corrected to the time of tracer injection.

Image analysis and generation of rest/stress time-activity curves

Reconstructed PET data were processed with PMOD v.3.8 (PMOD Technologies Ltd., Switzerland) via manual delineation of the myocardium to generate volumes of interest (VOIs) and respective time-activity curves. Decay-corrected time-activity curves were calculated for the myocardium VOI either as kBq/cc or % injected dose per gram tissue (%ID/g). An exponential model was fitted for each rest scan to estimate the radioactivity that remained in the myocardium at 41 to 82 min post injection from the initial 18F-flurpiridaz injection (Figure 1A, extrapolation curve). To obtain the corrected time-activity curves following stress injection (Figure 1A, 18F-flurpiridaz and regadenoson), extrapolation curves were subtracted from the respective image-derived time-activity curves at 41 to 82 min post injection. Correction for the injected dose yielded the final rest and stress time-activity curves (Figure 1B).

Figure 1
figure 1

Time-activity curves (TACs) of the mouse myocardium upon tail-vein injections of 18F-flurpiridaz. (A). Native TACs after rest (18F-flurpiridaz) and stress (18F-flurpiridaz + regadenoson) injection, presented as kBq per voxel. The model curve was fitted with a single exponential model to subtract 18F-flurpiridaz injection 1 from injection 2. (B) Final rest and stress TACs after correction for injected 18F-flurpiridaz dose, presented as percent injected dose per gram tissue (%ID/g). Note that the correction of the stress curve was performed prior to the normalization to the injected dose

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Input function

An arteriovenous shunt and portable coincidence detector (twilite, swisstrace, Menzingen, Switzerland) were used to record the tracer concentration in the blood by continuous sampling and simultaneously with the PET data acquisition in five FVB/N mice (30.1–32.6 g). The coincidence detector was cross-calibrated to the PET for kBq/cc output. The delay between tissue and blood time-activity curves was determined as part of the model fitting procedure, and the final input function was corrected for plasma metabolites and plasma-to-blood ratio (Supplemental Information). Metabolite-corrected input functions were used for all analyses. The resulting five input functions were averaged, and the average was used as a surrogate input function for all animals scanned without arteriovenous shunt system (Supplemental Information).

Kinetic modeling

Kinetic modeling was performed with the PKIN tool of PMOD v.3.8 (PMOD Technologies Ltd., Switzerland). The kinetics of 18F-flurpiridaz was evaluated with a one- and two-tissue compartment model using the following equations:

One-tissue compartment model:

$$\frac{{dC}_{1}}{dt} = {K}_{1 }{C}_{\mathrm{p}}\left(t\right)-{k}_{2}{C}_{1}(t)$$
(1)
$${C}_{\mathrm{Model}}\left(t\right) = \left(1-{v}_{\mathrm{b}}\right){C}_{1}(t)+{v}_{\mathrm{b}}{C}_{\mathrm{b}}(t)$$
(2)

Two-tissue compartment model:

$$\frac{{dC}_{1}}{dt} = {K}_{1}{C}_{\mathrm{p}}\left(t\right)-\left({k}_{2}+{k}_{3}\right){C}_{1}\left(t\right)+{k}_{4}{C}_{2}\left(t\right)$$
(3)
$$\frac{{dC}_{2}}{dt} = {k}_{3}{C}_{1}\left(t\right)-{k}_{4}{C}_{2}(t)$$
(4)
$${C}_{\mathrm{Model}}(t) = \left(1-{v}_{\mathrm{b}}\right)\times ({C}_{1}(t)+{C}_{2}(t))+{v}_{\mathrm{b}}\times {C}_{\mathrm{b}}(t)$$
(5)
$${V}_{T} = {K}_{1}*\frac{\left(1+\frac{{k}_{3}}{{k}_{4}}\right)}{{k}_{2}}$$
(6)

\({C}_{\mathrm{p}}\left(t\right)\) is the input function, \({C}_{1}\left(t\right)\) and \({C}_{2}\left(t\right)\) are the concentrations in the first and second tissue compartments. \({K}_{1}\) [mL·cm−3·min−1] and \({k}_{2}\) [1 min−1] represent the uptake and clearance rates from the plasma to the first tissue compartment, whereas \({k}_{3}\) [1 min−1] and \({k}_{4}\) [1 min−1] are the rate constants describing the exchange between the first and second tissue compartment. \({C}_{\mathrm{Model}}(t)\) shows the operational model curve, with the concentration \({C}_{\mathrm{b}}(t)\) in the whole blood, and the blood volume fraction \({v}_{\mathrm{b}}\), which was set to 0.13, as previously reported for the myocardium.14 Tissue distribution volume (VT) was calculated from the fit \({K}_{1}\) and apparent rate constants \({k}_{2}\), as well as \({k}_{3}\) and \({k}_{4}\) according to Eq. 6, and was additionally assessed by graphical Logan analysis.15

Statistics

Continuous variables are presented as mean ± standard error of the mean (SEM). Student’s t test and analysis of variance (ANOVA) tests were used for group comparisons of continuous variables. For multiple comparisons, Bonferroni correction was applied. Strength and direction of associations were assessed by Spearman’s rank-order correlation (rs). Outliers were assessed based on the Grubb’s test.16 A two-tailed P value of ≤ 0.05 was deemed statistically significant. Statistical analyses were carried out with SPSS (SPSS Statistics for Windows Version 24.0. IBM Corp. Armonk, NY).

Results

Rest/stress myocardial perfusion imaging

Time-activity curves (TACs) of 18F-flurpiridaz in the myocardium are depicted in Figure 1. At initial 18F-flurpiridaz injection, a rapid myocardial tracer inflow was observed, followed by a slow washout. Preliminary experiments revealed that a scan time of 40 min was sufficient to obtain accurate fits for the terminal washout phase (Figure 1A, model curve), thus allowing to account for residual myocardial activity from the initial 18F-flurpiridaz injection. Details on model curve fitting are given in the Supplemental Information. Subtraction of the extrapolated model curves from respective native TACs at 40-80 min post injection and correction for the injected 18F-flurpiridaz dose yielded the final stress TACs (Figure 1B). Notably, myocardial TACs were higher for the stress than for the rest scans at every measured time point, indicating a sustained increase of myocardial 18F-flurpiridaz uptake following regadenoson injection (Figure 1B). The increase of myocardial 18F-flurpiridaz uptake under pharmacological vasodilation conditions was visually confirmed by PET images of the mouse myocardium (Supplemental Information).

Quantification of absolute myocardial blood flow by kinetic modeling

To determine absolute myocardial blood flow (MBF), we employed kinetic tracer modeling using a metabolite-corrected input function that was recorded by continuous arterial blood sampling. Results of kinetic modeling were compared for one- and two-tissue compartment models. While the kinetic results were satisfactory by visual inspection for the two-tissue compartment model (Figure 2), the one-tissue compartment model did not provide accurate fitting. Along this line, a comparison of “goodness-of-fit” parameters such as the Akaike information criterion (AIC), Schwartz criterion (SC), Model selection criterion (MSC), and R2 consistently confirmed that the two-tissue compartment model was the superior model (Supplemental Information). K1, which is typically considered a measure of absolute MBF for tracers with high myocardial extraction fraction such as 18F-flurpiridaz,8 ranged from 6.7 to 20.0 mL·cm−3·min−1, while myocardial VT values between 34.6 and 83.6 mL/cm3 were obtained. A representative example of the two-tissue compartment model fit is shown in Figure 2B. VT values obtained from Logan graphical analysis were in agreement with the two-tissue compartment model fit (Figure 2C). These results suggest that the two-tissue compartment model constitutes a suitable model for the assessment of 18F-flurpiridaz kinetic parameters in mice, which is in agreement with previous studies in pigs and humans.17,18,19

Figure 2
figure 2

Two-tissue compartment model for 18F-flurpiridaz in the mouse myocardium. (A) Visualization of the model. While K1 and k2 describe tracer delivery to the myocardium and clearance from the myocardium, respectively, k3 and k4 represent the association and dissociation rate constants toward mitochondrial complex I (MC-I), which is located at the mitochondrial membrane of cardiomyocytes. (B) Representative two-tissue compartment fitting for the assessment of K1 and tissue volume of distribution (VT). (C) Representative logan graphical analysis

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Correlation of myocardial 18 F-flurpiridaz uptake with K 1 and V T

In a next step, we sought to assess whether the image-derived myocardial tissue uptake of 18F-flurpiridaz (%ID/g tissue) can be used as a surrogate measure for relative myocardial perfusion changes. Myocardial 18F-flurpiridaz uptake was significantly correlated with K1 from two-tissue compartment modeling. As shown in Tables 1 and 2, Spearman’s coefficients (rs) ranged between 0.478 and 0.573 for the rest scans and were higher after regadenoson injection (0.617-0.681), whereas significant correlations were obtained for all tested time slots. Nonetheless, R2 values were generally low, ranging from 0.21 to 0.43, which indicates that K1 does not sufficiently explain a large proportion of the variability in image-derived myocardial 18F-flurpiridaz uptake.

Table 1 Correlation of image-derived myocardial 18F-flurpiridaz uptake with perfusion constant K1 at resting state (n = 27)
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Table 2 Correlation of image-derived myocardial 18F-flurpiridaz uptake with perfusion constant K1 following regadenoson injection (n = 27)
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In contrast, when myocardial 18F-flurpiridaz uptake was compared to the respective volumes of distribution (VT), excellent correlations were obtained between %ID/g tissue and VT at rest (Figure 3). Notably, it was found that the two-tissue compartment model described the myocardial 18F-flurpiridaz uptake most accurately at later time frames (rest scans: Figure 3C, 7-11 min post injection, R2 = 0.98, Figure 3D, 11-20 min post injection, R2 = 0.99, and Figure 3E, 20-40 min post injection, R2 = 0.99), while earlier time frames were associated with lower R2 values (Figure 3A, 0-2 min post injection R2 = 0.71; Figure 3B, 2–7 min post injection, R2 = 0.95). Similarly, the correlation model between %ID/g tissue and VT was superior at later time frames following regadenoson injection, as depicted in Figure 4. Overall, %ID/g tissue, averaged from 20 to 40 min post injection, was most accurately described by the two-tissue compartment model under rest conditions and following pharmacological vasodilation.

Figure 3
figure 3

Resting state (no regadenoson) correlations of image-derived myocardial 18F-flurpiridaz uptake (%ID/g tissue), averaged at different time intervals, with tissue volume of distribution (VT). Early time intervals revealed lower R2 values, while later time intervals reached an R2 value of up to 0.99, indicating an excellent correlation between VT and %ID/g tissue 18F-flurpiridaz. Averaged time intervals included (A) 0-2 min, (B) 2-7 min, (C), 7-11 min, (D) 11-20 min, (E) 20-40 min and (F) 0-40 min post injection

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Figure 4
figure 4

Correlations of image-derived myocardial 18F-flurpiridaz uptake (%ID/g tissue) following regadenoson-induced stress, with tissue volume of distribution (VT). Early time intervals revealed lower R2 values, while later time intervals reached an R2 value of up to 0.98, indicating an excellent correlation between VT and %ID/g tissue 18F-flurpiridaz. Averaged time intervals included (A) 0-2 min, (B) 2-7 min, (C), 7-11 min, (D) 11-20 min, (E) 20-40 min and (F) 0-40 min post injection

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Coronary Flow Reserve

CFR can be calculated from the ratio of MBF during regadenoson-induced vasodilation to the MBF under resting conditions.20 Given that K1 constitutes a measure of absolute MBF, we used the ratio of K1 following regadenoson injection to K1 at resting condition to calculate the CFR. As expected, K1 was significantly higher following regadenoson injection (Figure 5A, P < 0.001). Similarly, regadenoson-induced coronary vasodilation led to a significant increase in VT (Figure 5B, P < 0.001). The resulting mean stress-to-rest ratios for K1 and VT were identical (Figure 5C, 1.41±0.29 vs 1.41±0.17, P = 0.92), however, with a higher variability obtained for K1. These results support the concept that both, K1 and VT, are similarly sensitive to pharmacologically induced changes of MBF in mice, while VT seems to constitute a more robust parameter for the estimation of CFR. Notably, it was found that stress-to-rest ratios of image-derived myocardial 18F-flurpiridaz uptake accurately predicted CFR, as depicted in Figure 6. While tracer washout led to a gradual reduction of averaged %ID/g tissue over time, under resting conditions (Figure 6A) and following regadenoson injection (Figure 6B), the stress-to-rest ratio did not differ significantly between time intervals (Figure 6C). With a mean stress-to-rest ratio of 1.40±0.20, %ID/g 18F-flurpiridaz from 20 to 40 min post injection provided the most accurate mean ratio, as compared to CFR determined from K1 by the two-tissue compartment model.

Figure 5
figure 5

Average K1 and VT under resting conditions and following pharmacological stress testing. (A) K1 was significantly higher following regadenoson administration (P < 0.001). (B) VT was significantly elevated following regadenoson administration (P < 0.001). (C) Mean coronary flow reserve estimated from stress-to-rest ratios of K1 and VT

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Figure 6
figure 6

Myocardial 18F-flurpiridaz uptake averaged from 7-11, 11-20 and 20-40 min post injection. A significant reduction of averaged %ID/g tissue of 18F-flurpiridaz was found toward later time intervals (A) at resting state as well as (B) following pharmacological stress testing. (C) In contrast, stress-to-rest ratios did not significantly differ between different time intervals

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Discussion

In the present study, we show that rest/stress MPI with 18F-flurpiridaz in mice follows a two-tissue compartment model. While K1 and VT were both similarly sensitive to vasodilator-induced increase of MBF, VT exhibited a superior correlation with image-derived myocardial tracer uptake at all measured time intervals. In particular, image-derived tracer uptake at later time intervals revealed ideal coefficients of determination (R2 up to 0.99) when correlated with VT. Further, the average stress-to-rest ratio of myocardial tracer uptake (%ID/g tissue), obtained from 20 to 40 min post injection, was identical to the stress-to-rest ratios of K1 and VT. These results suggest that myocardial 18F-flurpiridaz uptake (%ID/g) in mice, as determined from dynamic PET, correlates with MBF and can be used to estimate relative myocardial perfusion changes as well as CFR when pharmacological vasodilation is employed.

To the best of our knowledge, this is the first study to assess the feasibility of rest/stress PET-MPI with 18F-flurpiridaz in mice. In agreement with previous reports in other species, including pigs21 and humans,19 we found that a two-tissue compartment model was suitable to predict 18F-flurpiridaz uptake in the mouse myocardium. Nonetheless, significant species differences were observed with regard to tracer washout from the myocardium. While myocardial 18F-flurpiridaz washout was negligible in pigs and humans, our time-activity curves unveiled a demonstrably faster kinetics in mice with evident washout from the mouse myocardium starting at 5–10 min post injection.19,21 Our results point toward species differences in myocardial tracer retention that need to be taken into consideration for kinetic modeling. As such, while k4 (dissociation rate constant) was manually set to zero in previous studies with other species,17,21,22 we did not employ any restrictions for k4 in mice. Of note, a fast decline of the parent tracer fraction was detected in the mouse plasma following tail-vein injection of 18F-flurpiridaz (Supplemental Information), which might, at least in part, explain the observed species differences in tracer washout from the myocardium. To account for the metabolic degradation, we used metabolite-corrected input functions for all animals tested. By ex vivo metabolite analysis, the myocardium was found to show an intact parent fraction of > 99%, suggesting that the contribution of radiometabolites to the overall myocardial radioactivity was negligible. In contrast to the two-tissue compartment model, the one-tissue compartment model did not result in satisfactory results by visual inspection and assessment of different model fit indicators, suggesting that binding to MC-I has a significant contribution to the kinetics as well as perfusion-linked 18F-flurpiridaz delivery to the mouse myocardium.

Due to the availability of rubidium-82 generators, which obviates the need for a cyclotron, rubidium-82 is the most frequently used probe for PET-MPI. Nonetheless, the relatively high positron range results in an inferior spatial resolution, as compared to other PET isotopes.23 In contrast, 15O-water and 13N-ammonia exhibit superior spatial resolutions to rubidium-82 and are validated perfusion tracers; however, their short physical half-lives do not allow satellite distribution, thus, rendering an on-site cyclotron indispensable.21 Efforts to develop a radiofluorinated myocardial perfusion tracer with increased physical half-life and spatial resolution have ultimately led to the discovery of 18F-flurpiridaz.6,7,8 Unlike other probes for PET-MPI, 18F-flurpiridaz binds to the mitochondrial complex I (MC-I), which is highly abundant in cardiomyocytes.8,21 The latter allows selective visualization of the myocardium, providing remarkably high signal-to-background ratios and thus high image quality.9,24,25,26,27,28,29,30 In experimental models, 18F-flurpiridaz exhibited a relatively high myocardial extraction fraction of 0.94, which was consistent at different flow rates, and demonstrated favorable performance characteristics as a myocardial perfusion tracer.7,8,17,27,31,32,33,34 Notably, we observed that peak arterial radioactivity was lower than peak myocardial activity across all animals tested, which might be explained by the relatively high first-pass myocardial extraction fraction of 18F-flurpiridaz.

Despite the reported favorable properties of 18F-flurpiridaz for PET-MPI, the sustained myocardial radioactivity from the initial scan may affect the time-activity curves upon the second injection—particularly if rest and stress scans are performed on the same day. In our study, pilot experiments were conducted to determine the minimum scan duration required to allow adequate extrapolation of the terminal phase via non-linear regression models. Employing these models, we were able to correct for the residual myocardial radioactivity from the first 18F-flurpiridaz injection. In light of the observed species differences in 18F-flurpiridaz clearance from the myocardium, we conclude that a careful evaluation of the terminal phase for the underlying test species seems crucial for 1-day rest/stress PET-MPI protocols with 18F-flurpiridaz.

Absolute MBF quantification has proven its utility in clinical routine; however, the latter requires an arterial input function35 that can be derived from the PET image by placing a VOI in the left ventricular cavity.36 While image-derived input functions are routinely obtained in clinical PET-MPI, this approach is hampered in mice due to the relatively small left ventricular dimensions. Accordingly, quantification of absolute MBF in mice requires arterial blood sampling, which is associated with significant technical challenges. To circumvent this limitation, we assessed whether myocardial 18F-flurpiridaz uptake can be used to provide information on myocardial perfusion changes as well as fundamental kinetic parameters such as K1 and VT. Indeed, although correlations of K1 with image-derived myocardial 18F-flurpiridaz uptake were significant, R2 values were generally below 0.5, indicating a poor fit for all time frames investigated. In contrast, ideal fits were obtained for the correlation of VT with myocardial 18F-flurpiridaz uptake, particularly at later time intervals such as 20–40 min post injection. Although K1 is closely linked to perfusion, our results suggest that the rapid tracer kinetics renders myocardial 18F-flurpiridaz uptake more highly weighted toward MC-I binding than absolute MBF in mice. Further, early time intervals, which are critical for the accurate estimation of K1, are particularly susceptible to spillover effects from the blood pool as well as variability in manual injection time and potential animal distress that resulted from the injection procedure. Accordingly, the relation between K1 and myocardial 18F-flurpiridaz uptake did not allow the prediction of absolute values for MBF from myocardial 18F-flurpiridaz uptake in our study. Notably, however, %ID/g 18F-flurpiridaz was highly correlated with VT. Indeed, our findings suggested that VT was reliably estimated from myocardial 18F-flurpiridaz uptake in the absence of an arterial input function. Given (1) that VT is sensitive to changes in K1 according to Eq. 6 and (2) that mean rest-to-stress ratios were comparable for VT and K1, it appears that changes in myocardial perfusion were accurately reflected by the model microparameter VT. Accordingly, although %ID/g 18F-flurpiridaz was not suitable to estimate values for absolute MBF, our data indicate that %ID/g 18F-flurpiridaz can be used for intra- and interindividual comparisons of relative myocardial perfusion in mice. Further, mean CFR values were comparable when calculated from stress-to-rest ratios of K1, VT, and %ID/g 18F-flurpiridaz from 20 to 40 min post injection, suggesting that stress-to-rest ratios of %ID/g 18F-flurpiridaz can be used as a surrogate of CFR when pharmacological vasodilation is employed. In contrast to pharmacological vasodilation, however, it should be noted that the assessment of CFR from exercise stress testing is not recommended in the absence of an input function, particularly due to the substantial increase of cardiac output under exercise testing, which leads to a proportional dilution of the intravenous radiotracer dose.37,38

There are study limitations that should be pointed out. First, the lack of a reference standard to validate PET-MPI findings in mice constitutes a limitation of this study. Indeed, the assessment of CFR by PET-MPI in mice is a major challenge in contemporary cardiovascular research and studies of CFR by rest/stress MPI using PET in rodents are scarce in general. Although the spatial resolution of our PET scanner was in the range of reported left ventricular thickness  < 1.8 mm for mice,39 the positron ranges of conventional PET-MPI probes such as rubidium-82, 15O-water, and 13N-ammonia would not allow a sufficient spatial resolution for the assessment of CFR in the small mouse heart.40 Conversely, the availability of a radiofluorinated probe now provides new perspectives for PET-MPI in mice and the fact that myocardial 18F-flurpidaz uptake correlated well with K1 and VT from quantitative kinetic modeling with an invasive metabolite-corrected input function is particularly encouraging. Second, high isoflurane concentrations can prompt coronary vasodilation and may have affected outcome measures of our study.41 However, previous work has shown that heart rate and mean systolic blood pressure remain stable at isoflurane concentration up to 2.0% in mice.42,43 To minimize the vasodilatory properties of isoflurane, its concentration was kept at or below 2.0% throughout the entire experiment. Nonetheless, a vasodilatory effect of isoflurane cannot be completely ruled out in the present study. Third, an experimental arterial input function was only available in five animals, and the average of all five input functions was used as a population (surrogate) input function for kinetic modeling in animals without arterial shunt, as previously reported.44 However, a linear regression analysis revealed that K1 and VT obtained from the surrogate input function and the respective input functions from shunt surgery were in good agreement (Supplemental Information). While obtaining an image-derived input function in mice is particularly challenging and prone to error, the approach of a surrogate input function constitutes a valid alternative for high-throughput studies.

In conclusion, our results indicate that 18F-flurpiridaz can be used for rest/stress myocardial perfusion imaging in mice and follows a two-tissue compartment model. Myocardial 18F-flurpiridaz uptake was equally sensitive to vasodilator stress as K1 and VT, suggesting that a simplified assessment of CFR, based on image-derived findings, is feasible when pharmacological vasodilation is employed. Further, although arterial blood sampling is required for absolute quantification of MBF, myocardial 18F-flurpiridaz uptake can be used for relative comparison of myocardial perfusion in mice.

New Knowledge Gained

In the present study, we show that rest/stress myocardial perfusion imaging in mice is feasible with 18F-flurpiridaz and follows a two-tissue compartment model. Critical kinetic modeling parameters such as K1 and VT were sensitive to vasodilator-induced increase of myocardial blood flow. Further, the average stress-to-rest ratio of myocardial tracer uptake from 20 to 40 min post injection was identical to the stress-to-rest ratios of K1 and VT, indicating that myocardial 18F-flurpiridaz uptake can be used to estimate relative myocardial perfusion changes and coronary flow reserve (CFR) in mice. The translational relevance of this study lies in the detrimental implications of an abnormal CFR in coronary artery disease (CAD) patients. The present findings encourage a wider use of PET-MPI for the assessment of CFR in mouse models of CAD, and pave the way for mechanistic studies that aim at identifying molecular variables affecting CFR.