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Radiolabeled arginine-glycine-aspartate (RGD) peptides are increasingly used in preclinical and clinical studies to assess the expression and function of the αvβ3 integrin, a cellular adhesion molecule involved in angiogenesis and tumor metastasis formation. To better understand the PET signal obtained with radiolabeled RGD peptides, we have constructed a compartmental model that can describe the time–activity curves in tumors after an intravenous injection.
We analyzed 60-min dynamic PET scans obtained with 64Cu-1,4,7,10-tetraazacyclododecane-N,N′,N″,N′′-tetraacetic acid (DOTA)-RGD in 20 tumor-bearing severe combined immunodeficient (SCID) mice after a bolus dose (18,500 kBq [500 μCi]), using variations of the standard 2-compartment (4k) tissue model augmented with a compartment for irreversible tracer internalization. αvβ3 binding sites were blocked in 5 studies with a coinjection of cold peptide. In addition, 20 h after injection, static PET was performed on 9 of 20 mice. We fitted 2k (k3 = k4 = 0), 3k (k4 = 0), 4k, and 4kc (k4 = constant) models to the PET data and used several criteria to determine the best model structure for describing 64Cu-DOTA-RGD kinetics in mice. Akaike information criteria (AIC), calculated from model fits and the ability of each model to predict tumor concentration 20 h after tracer injection, were considered.
The 4kc model has the best profile in terms of AIC values and predictive ability, and a constant k4 is further supported by Logan–Patlak analysis and results from iterative Bayesian parameter estimation. The internalization compartment allows quantification of the putative tracer internalization rate for each study, which is estimated here to be approximately an order of magnitude less than k3 and thus does not confound the apparent specific binding of the tracer to the tumor integrin during the first 60 min of the scan. Analysis of specific (S) and nonspecific or nondisplaceable (ND) binding using fitted parameter values showed that the 4kc model provided expected results when comparing αvβ3 blocked and nonblocked studies. That is, specific volume of distribution, [VS = (K1k3)/(k2k4)], is much higher than is nondisplaceable volume of distribution, [VND = (K1/k2)], in nonblocking studies (2.2 ± 0.6 vs. 0.85 ± 0.14); VS and VND are about the same in the blocking studies (0.46 ± 1.6 vs. 0.56 ± 0.09). Also, the ratio of static tumor and plasma measurements at 60 and 10 min [CT(60)/CP(10)] is highly correlated (RS = 0.92) to tumor VS.
We have developed and tested a compartmental model for use with the 64Cu-DOTA-RGD PET tracer and demonstrated its potential as a tool for analysis and design of preclinical and clinical imaging studies.
The cell surface glycoprotein αvβ3 is a member of the integrin family whose primary role is mediating interaction between αvβ3-expressing cells and the extracellular matrix, pathogens, or other cells (1,2). αvβ3 is expressed on certain tumor and endothelial cells and plays an important role in tumor migration and angiogenesis (1,3); αvβ3 antagonists have been shown to induce cell death (1), making this integrin an attractive target for novel cancer therapeutics that inhibit angiogenesis and tumor growth. αvβ3 binds to the arginine-glycine-aspartate (RGD) peptide motif within its in vivo protein ligands (e.g., fibrinogen) (2). Small-molecule RGD peptide antagonists with a high affinity for αvβ3 have been developed with the intention of blocking αvβ3 function. Haubner et al. (4) developed the first αvβ3-specific PET tracer, 18F-galacto-RGD, and subsequently used it to image patients with cancer (5) in whom a strong association between tracer uptake and αvβ3 expression was observed (6). In squamous cell carcinomas of the head and neck region, uptake of radiolabeled RGD has been suggested to be a potential surrogate parameter of tumor angiogenesis (7). Generally, small-molecule αvβ3 PET tracers are being developed as a means to assess tumor aggressiveness and monitor αvβ3 expression before and after treatment with αvβ3 antagonists.
To accurately assess the magnitude of specific binding of a PET tracer to αvβ3, one must be able to separate the PET signal into perfusion and nonspecific and specific binding components. Recently, pharmacokinetic analysis of the 18F-galacto-RGD PET tracer was performed by Beer et al. (8) using 1- and 2-compartment tissue models fitted to biodistribution data from patients with cancer. Here we applied a similar compartmental modeling approach to the kinetic analysis of the 64Cu-c(RGDfK(1,4,7,10-tetraazacyclododecane-N,N′,N″,N′″-tetraacetic acid [DOTA])) (64Cu-DOTA-RGD) PET tracer in mouse models bearing tumors grown from cell lines that express low (A431 epidermal carcinoma), intermediate (U373 glioblastoma-astrocytoma), and high (U87 glioblastoma-astrocytoma) levels of αvβ3. Additionally, αvβ3 binding sites are blocked with a coinjection of cold peptide in selected studies, and 20-h postinjection static PET scans are acquired for selected blocked and nonblocked studies. Four different 2-compartment tissue models are fitted to tumor time–activity curves, and the best model was chosen using the Akaike information criterion (AIC) (9) calculated for each model fitted to both the dynamic scans at 60 min and dynamic data at 20 h after injection. Model-fitting results using a Bayesian or population kinetics approach (10) are also considered. We demonstrated that magnitude of specific binding, as calculated on the basis of fitted model parameters, strongly correlates to the level of αvβ3 expression. The 20-h postinjection scans facilitate estimation of the αvβ3-mediated tracer internalization rate (11,12) and allow us to determine whether this process confounds measurement of specific binding during the initial 60-min dynamic scan. We also explored the possibility of estimating the capacity of tumor to sequester tracer via specific binding to αvβ3 by deriving a macroparameter equal to the ratio of static tumor and blood-tracer concentration measurements.
The peptide c(RGDfK(DOTA)) was constructed as described previously (13). 64CuCl2 (specific activity, 185 GBq [5 Ci/mg]) (MDS Norion) was labeled by incubating 1.25 µg of c(RGDfK(DOTA)) with 64CuCl2 (37 MBq [1 mCi]) for 1 h at 50°C in a total volume of 200 µL of 0.1 M ammonium acetate (pH 7.1). The radiolabeled peptide was purified using a 1-mL strata-X 33-µm polymeric reversed-phase column (Phenomenex, Inc.). After a water wash, the labeled peptide was eluted in 100% ethanol, dried over argon gas at 60°C, and resuspended in 0.9% saline. In vivo metabolic stability of a similar compound, 64Cu-DOTA-cRGDfk peptide tetramer, was demonstrated by Wu et al. (14), suggesting our monomer has comparable stability.
Severe combined immunodeficient (SCID) mice were purchased from The Jackson Laboratory. All animal manipulations were performed with sterile techniques according to the guidelines of the UCLA Animal Research Committee. U87MG, U373, and A431 cells (2 × 106 cells/mouse) were resuspended in phosphate-buffered saline and Matrigel (BD Biosciences) and injected subcutaneously into the right front or right rear leg of 7-wk-old male mice. Imaging was performed after tumors had grown to an approximate size of 100 mm3 as measured using calipers.
Animals were imaged with a microPET FOCUS 220 scanner (Siemens) and a micro-CAT II scanner (Siemens) (15). 64Cu-DOTA-RGD (18,500 kBq [500 μCi]) was injected via tail vein cannulation. At the time of injection, 60-min dynamic small-animal PET scans with corresponding 7-min micro-CT scans were obtained, followed by 10-min static small-animal PET and micro-CT scans approximately 20 h after injection as previously described (16). For blocked studies, c(RGDfK) (Peptides International) was resuspended in 0.9% saline and mixed with the radiolabeled probe at 10 mg of peptide per kilogram of mouse; scans were acquired as described above. Late-time small-animal PET and micro-CT scans were obtained at approximately 20 h after injection. PET images were reconstructed with filtered backprojection and CT-based attenuation correction. Frame durations were 20 × 0.5 s, 5 × 10 s, 10 × 60 s, 9 × 5 min, and 1 × 4 min for 60-min scans. The 90-min scans used a framing scheme of 6 × 10 s, 10 × 60 s, 10 × 5 min, 2 × 10 min, and 1 × 9 min. A total of 20 mice were used, 4 with both U87 and A431 tumors, for a total of 24 tumor time–activity curves. Here, we primarily considered the results of the 5 blocked and 12 nonblocked studies (17 tumor time–activity curves); 7 additional datasets, collected under slightly different conditions, were used for the population-modeling portion of this study.
Using Amide (17), we determined the tracer concentration in tumors by drawing spheric (diameter, 1.5 mm) regions of interest (ROIs) in the area of the reconstructed PET image within the tumor that exhibited the highest radioactivity, as determined by visual inspection. Whole-blood concentration was estimated by drawing an ROI in the region of the image corresponding to the left ventricle of the heart. Activity concentrations are expressed as percentage injected dose per gram of tissue.
A linear compartmental model (Fig. 1) was used in this study, where u(t) represents plasma concentration of the tracer calculated by correcting PET-measured blood concentration for partial-volume effects and absence of uptake by blood cells. A recovery coefficient of 0.7 (18) and hematocrit of 50% (19) are assumed, resulting in a PET-measured whole-blood (WBPET)–to–actual plasma (Pa) tracer concentration ratio of
for the 60-min dynamic scans, and
for the 20-h postinjection scans, where partial-volume effects are not an issue because of low plasma concentration of tracer and comparable activity in myocardium. Spillover from the myocardium may slightly increase apparent tracer concentration at 20 h after injection; here we assumed spillover error is negligible. Compartments q1(t) and q2(t) represent the amount of free or nonspecifically bound and specifically bound tracer within tumor extravascular space, respectively. Several model structures could be used to describe the 20-h postinjection data point; here we assumed internalization is a linear process mediated by binding of ligand to receptor, thus, compartment q3(t) was added to represent tracer that has been irreversibly internalized by tumor cells (20). Model equations are written as
where, putatively, K1 represents the tracer extravasation rate (min−1), k2 represents the rate of tissue efflux of free or nonspecifically bound tracer (min−1), and k3 represents the rate of specific binding (min−1) of 64Cu-DOTA-RGD to the extracellular portion of the αvβ3 integrin. k4 and kint represent rates of dissociation (min−1) and internalization (min−1) of specifically bound tracer, respectively. Note that kint is assumed to represent internalization; however, all slow uptake mechanisms are lumped into this parameter. The measurement model is written as
where VB is the fractional blood volume of the tumor (unitless) and c(t) is the tumor time–activity curve. Here we considered 4 structural perturbations of the model shown in Figure 1: a 2k model(k3 = k4 = 0) assumes PET data can be accurately described without explicitly accounting for the specific binding of 64Cu-DOTA-RGD to the αvβ3 integrin; a 3k model (k4 = 0) explicitly accounts for the specific binding of the tracer to integrin, which is assumed to be irreversible; a 4k model assumes reversible binding of tracer to integrin; and a 4kc (k4 = constant; k4 > 0) model assumes that k4 has approximately the same value across all datasets. Each of the 4 model variants is augmented with a compartment representing irreversible internalization of tracer by tumor cells (Eq. 5).
The SAAM II/PopKinetics tracer kinetic modeling program (21,22) was used to implement the model shown in Figure 1 and estimate unknown parameters (K1, k2, k3, k4, and kint). Each measured PET data point, i, was assigned a weight (wi) equal to the reciprocal of the data variance, calculated as follows:
where σi is the SD, di is frame duration, and μi is mean ROI value. Standard 2-stage (STS) and iterative 2-stage (ITS) parameter-estimation algorithms (10) were implemented using PopKinetics. The STS method sequentially fits a particular model (e.g., 4kc) individually to n PET-derived datasets using the SAAM II computational engine and calculates the mean and SD of each parameter across all datasets. The ITS method repeats this process using mean and SD values calculated using the STS method as Bayesian constraints (18,23) on the parameter space, resulting in a new set of parameter means and SDs to be used as Bayesian constraints for the next round of fits. This iterative process continues until all parameters reach a preset convergence value. Given a large enough population size, n, the ITS method can detect fixed effects in the model structure, which occur when the SD of a parameter across all n datasets approaches zero. All models were fitted to 60-min dynamic scans and then extrapolated to the 20-h postinjection data by extending the simulation time for each fitted model; the input function was extrapolated to 20 h by fitting a single exponential term (Ae−λt) to the 60-min and 20-h data points. Additionally, each model was fitted to the 60-min dynamic data plus the 20-h data.
The AIC was used to determine which of the 4 proposed model structures was most appropriate for use with 64Cu-DOTA-RGD. The AIC (9) considers goodness of fit and structural parsimony with the purpose of selecting a single model, from a group of candidate models, that best describes the data of interest while not being overly complex. The AIC is written here as
where J(p) is the objective function used to assess goodness of fit, nP is the number of adjustable model parameters, nD is the number of data points to which the model is fitted, p is the parameter vector that minimizes the objective function, and s(,ti) is the model simulation at time ti and parameter vector (22). On the basis of this criterion, the model with the lowest calculated AIC value is considered to have achieved the optimal balance between goodness of fit and structural parsimony. Additionally, we considered the ability of each model to predict the 20-h postinjection data by extrapolating models fitted to the initial dynamic PET scan.
Specific (S) and nondisplaceable (ND), that is, nonspecific, volumes of distribution (V) were calculated for blocked (n = 5) and nonblocked (n = 12) tracer studies using the following equations (24):
where K1, k2, k3, and k4 were calculated by setting kint to zero and fitting the model to data from the 60-min dynamic PET scans. Total volume of distribution (Vd) is defined as
All statistical analysis (standard and paired t test, Spearman correlation, linear regression) was performed using GraphPad Prism (version 4.03 for Windows; GraphPad Software) (available at: http://www.graphpad.com).
Figure 2 shows 2k, 3k, 4k, and 4kc models fitted to tumor time–activity curves from 4 selected 60-min dynamic scans; kint(Eq. 5) is fixed at zero. Qualitatively, the first 10 min of some fits are slightly off, possibly because of lower weights assigned to these data points. The mean and SD of the 5 estimated model parameters calculated using STS and ITS estimation methods are VB = 0.049 ± 0.024 (unitless) (STS) and 0.074 ± 0.044 (ITS); K1 = 0.046 ± 0.017 min−1 and 0.031 ± 0.011 min−1; k2 = 0.18 ± 0.20 min−1 and 0.13 ± 0.12 min−1; k3 = 0.041 ± 0.035 min−1 and 0.063 ± 0.029 min−1; and k4 = 0.013 ± 0.006 min−1and 0.0094 ± 0.0 min−1. These were calculated by applying STS and ITS parameter-estimation methods to the 4k model, which was fitted to all 24 tumor time–activity curves. The ITS method converges to the 4kc model (k4 = 0.00938 min−1 for all studies) after 23 iterations, using a convergence criterion of 0.05; this value of k4 was used for the aforementioned 4kc model fits (Fig. 2) and all subsequent 4kc fits.
Figure 3A plots AIC values for the blocked αvβ3 studies, in which the 2k model has the lowest value for 4 of 5 fits; Figure 3B shows that the 2k model also has the lowest AIC for 2 of 3 nonblocked A431 studies. 3k and 4kc models have the lowest values (<1% difference between AIC3k and AIC4kc for each study) for 2 of 2 U373 studies and 5 of 7 U87 studies (Fig. 3B). The 4k model has the highest AIC value for all blocked and A431 studies, and the 2k model has the highest AIC value for 7 of 9 U373 and U87 nonblocked studies. A lower AIC value indicates a more appropriate model structure.
Figure 4A depicts a representative extrapolation to the 20-h postinjection data using the aforementioned fits to the 60-min dynamic scans. 2k, 4k, and 4kc models provide similar extrapolations, with 4kc giving a slightly better qualitative prediction; the 3k model predicts a constant accumulation of tracer in tumor, resulting in a much higher predicted concentration than that measured by the 20-h postinjection scan.
Because the 2k and 4k models performed poorly and the 3k and 4kc models performed equally well with respect to AIC analysis (Fig. 3), 3k and 4kc models were fitted to data from each 60-min dynamic scan plus the 20-h postinjection datum, with kint (Eq. 5) set as an adjustable parameter. AICs calculated for each fit (not shown) show that 4kc has the lower value across the 13 tumor models when fitted to dynamic plus 20-h postinjection scans and, thus, the better structure. Figure 4B depicts a representative fit (black curve) of the 4kc model to dynamic PET data plus the 20-h postinjection data with the first hour of data and fit shown in the inset. kint was then set to zero (gray curve) for the fitted model depicted in Figure 4B; qualitatively, little change is seen during the first hour of the simulation (Fig. 4B, inset), whereas a dramatic decrease in tumor concentration is seen over the remaining 17 h of the simulation (Fig. 4B). Figure 5A compares estimated values of VB, K1, k2, and k3 based on the 4kc model fitted to 60-min dynamic data only and 60-min dynamic data plus the 20-h postinjection data (nonblocked and blocked studies). Estimated values of VB, K1, k2, and k3 based on the 4kc model fitted to each of these 3 datasets are all similar (P > 0.2, paired t test), with the exception of k3 based on blocked studies with 20-h data (solid black circle, P < 0.05, paired t test), which is lower than the other 2 estimated k3 values (open circles). We compared mean values across all 13 tumors with 20-h scans and determined that kint is approximately an order of magnitude lower than k3 (Fig. 5A); also, the mean estimated value of kint based on blocked studies is higher than kint based on nonblocked studies. Table 1 lists estimated parameter values for the 4kc model fitted to data from αvβ3 blocked and nonblocked dynamic scans and the 20-h postinjection scan where available; models are fitted to dynamic scan data only, with kint fixed at zero, for the 4 studies without a delayed static scan.
Specific (VS) and nondisplaceable (VND) volumes of distribution (Eqs. 10 and 11) were calculated for all blocked and nonblocked studies using parameter values based on model fits to the 60-min dynamic scans (Table 1). Figure 5B plots mean ± SD of both VS and VND for all blocked and nonblocked studies, with nonblocked organized by tumor type, location, and scan duration. No statistically significant difference between VS and VND is detected for the blocked studies, and a significant increase in VS is observed for the nonblocked studies (P<0.001, n = 12), using a standard t test. Qualitatively, A431 tumors located in the thigh show a small increase in VS, whereas all remaining tumor types exhibit a much larger increase. This analysis was repeated using ROIs drawn on regions of the reconstructed PET image corresponding to muscle and liver (not shown). Blocking of αvβ3 via coinjection of cold peptide appeared to have no effect on the relationship between VS and VND in these tissues, suggesting that tracer uptake in muscle and liver is independent of αvβ3.
Additionally, VS and VND were calculated using values of K1, k2, k3, and k4 estimated by Beer et al. (8) on the basis of dynamic PET scans of 19 patients with cancer; the mean value (shown without SD) across all patients is plotted in Figure 5B. We compared means and found that both VS and VND calculated from patient PET scans were qualitatively similar to volumes of distribution calculated from our mouse studies ([0.635 (n = 19) vs. 0.754 (n = 17)] for VS and [0.271 (n = 19) vs. 0.261 (n = 17)] for VND). To obtain parameter values comparable to those listed here, we multiplied each K1 listed in Beer et al. by 0.45 (patient hematocrit ≈ 45%) (26) because tracer concentration in whole blood was used as an input function in the patient study.
Figure 5C depicts the strong correlation (RS = 0.92) that was observed between VS and the ratio of tracer concentration in tumor at 60 min after injection [CT(60)] to tracer concentration in plasma at 10 min after injection [CP(10)].
The results of our study suggest that the 4kc model, derived using the ITS parameter-estimation method, is most appropriate for describing 64Cu-DOTA-RGD PET data. Figure 6 summarizes the model discrimination process that was applied to the 2k, 3k, 4k, and 4kc structures. We were able to rule out the 2k and 4k structures by AIC analysis (Fig. 3) of each model fitted to the initial dynamic PET scans (Fig. 2). The 2k model structure yielded the lowest AICs for tumor time–activity curves in which concentration of free αvβ3 was low(blocked and A431 studies), suggesting that only a single compartment is required to describe 64Cu-DOTA-RGD kinetics in αvβ3-negative tissues. Likewise, the 3k and 4kc models yielded the lowest AICs for tumor time–activity curves in which density of free αvβ3 was high (U373 and U87 studies), suggesting that 2 compartments are needed to describe 64Cu-DOTA-RGD kinetics in αvβ3-positive tissues. Implementation of a fixed value of k4 is supported by the ITS parameter-estimation process, in which k4 converges to 0.00938 min−1 for all studies under consideration (Fig. 3), and by graphical analysis, in which Patlak uptake (Ki) and Logan volume of distribution (Vd) are highly correlated (RS ≈ 0.90, not shown) across all studies, suggesting little variability in tracer dissociation rate (k4), because Ki = f(K1, k2, k3) and Vd = f(K1, k2, k3, k4) when calculated from fitted model parameters. The 3k model structure is ruled out by fitting 3k and 4kc models to 60-min dynamic scans plus the 20-h postinjection scan, where the 4kc structure yields lower AICs (not shown); the 3k model also provides a less accurate prediction of the 20-h postinjection data, compared with 2k, 4k and 4kc structures (Fig. 4A). Although the PET-derived input function, u(t), is corrected for partial-volume effects, errors due to spillover, delay, and dispersion are assumed to be negligible and are not accounted for in the present study. The impact of spillover, in particular, is expected to be small, because uptake of αvβ3-binding RGD peptides by the myocardium is minimal (4).
By using the 20-h postinjection scans, we were able to estimate kint, the rate of irreversible tracer internalization. The black curve in Figure 4B depicts a model fit to selected 20-h data, with the inset showing the first 60 min of data and fit; the gray curve illustrates the effect of setting kint to zero, in which a negligible shift from the original fitted black curve is observed (Fig. 4B, inset). The effect of setting kint to zero suggests that although the internalization rate is high enough to produce significant retention of the tracer over a 20-h period, the rate does not confound apparent tracer retention because of specific binding to αvβ3 (k3) during the first 60–90 min after tracer injection. Even when fitting the model to data collected over a 20-h period, only a slight decrease in estimated value of k3 is observed with kint included in the model structure, compared with k3 estimated via a model fit to the 60-min dynamic scan with kint set to zero (Fig. 5A). Because tracer metabolite analysis has not yet been performed at 20 h after injection, it is possible that we overestimated 64Cu-DOTA-RGD plasma concentration at the late static scan. This overestimation would affect the accuracy of the input function past 60 min and thus the confidence level of the estimated value of kint. To assess the effect a lower actual tracer plasma concentration 20 h after injection might have on conclusions drawn from the fitted model, we lowered 20-h plasma values calculated from the reconstructed PET image by 2 orders of magnitude and then reestimated the input function as described in the “Parameter Estimation” section. As expected, the resulting kint values are higher than those listed in Table 1; however, the fitted model suggests that tracer internalization does not confound the apparent specific binding capacity of the tumor during the first 60 min after tracer injection, even when plasma concentration of tracer at 20 h after injection is assumed to be close to zero. That is, the result is similar to that shown in Figure 4B.
Figure 5A and Table 1 show that the average estimated value of kint is much higher in the blocked studies than in the nonblocked studies, suggesting that a greater fraction of αvβ3-bound peptide may be internalized per unit of time when the 10 mg/kg dose of cold peptide is coinjected with 64Cu-DOTA-RGD. The αvβ3 integrin is activated by the binding of substrate, which stimulates recycling of the integrin from the cell surface to the intracellular compartment. This process occurs when the integrin binds RGD sequences on molecules such as fibronectin or fibrinogen—analogous to the interaction between the integrin and 64Cu-DOTA-RGD described by our model—and may explain why internalization rates are higher in tumors exposed to a large bolus of integrin substrate in the form of coinjected cold peptide, compared with tumors exposed to tracer alone. The effect of kint on apparent tracer kinetics in blocked studies is similar to the effect seen in nonblocked studies (Fig. 4B).
Estimated values of specific volume of distribution (Table 1) appear to be strongly correlated with concentration of available αvβ3 binding sites within the tumor (Fig. 5B); with the exception of a single A431 study, VS increases in parallel with αvβ3 expression from baseline (blocked studies) to low (A431), intermediate (U373), and high (U87) expression. Estimated values of nondisplaceable (nonspecific) tumor uptake are approximately constant, regardless of αvβ3 status (Table 1; Fig. 5B). Along with the AIC analysis presented in Figure 3, which suggests a 1-compartment tissue model is most optimal for describing tracer kinetics in low αvβ3-expressing tissue, these data support the putative physiologic significance of the 2-compartment tissue model and associated parameters for 64Cu-DOTA-RGD, in which compartment q1(t) represents accumulation of tracer in the tumor resulting from nonspecific transport mechanisms such as extravasation (K1), tissue efflux (k2), and nonspecific binding (K1/k2). Compartment q2(t) represents accumulation in tumor due to specific binding (k3) and dissociation (k4) of tracer from αvβ3. Additionally, the internalization term kint was introduced and is required to fit the model to tracer kinetics measured over a 20-h period (not shown).
Interestingly, VS and VND calculated from a previous patient study involving 18F-galacto-RGD (8) closely match our results. Although variability across patients is not represented here, mean patient VND is virtually identical to VND calculated from our mouse studies and patient VS is similar to values calculated for the U373 tumor, which expresses αvβ3 at an intermediate level. This similarity suggests that the methods and model developed here for kinetic analysis of 64Cu-DOTA-RGD may be readily applied to patient data.
A high correlation (RS = 0.92) between the ratio of tracer concentration in the tumor at 60 min after injection to tracer concentration in plasma at 10 min [CT(60)]/[CP(10)] and specific volume of distribution (VS) (Fig. 5C) was gleaned from an extensive analysis of correlations between model microparameters (VB, K1, k2, k3, k4), macroparameters (VS, VND, Ki, Vd), and tracer uptake at discrete time points (10, 30, and 60 min). This correlation, along with the aforementioned discussion of patient VS and VND values (Fig. 5B), suggests that magnitude of αvβ3 expression could be estimated in a clinical setting on the basis of a blood sample taken at 10 min after injection and a single static PET scan at 60 min.
We conducted a thorough pharmacokinetic analysis of 64Cu-DOTA-RGD and observed the following. First, we demonstrated that the 4kc model, compared with the 2k, 3k, and 4k models, is the most appropriate structure for use with this tracer (and presumably other small molecule tracers that target αvβ3) and examined the putative physiologic significance of the 2-compartment tissue model commonly used in PET tracer kinetic analysis by demonstrating that VS, calculated on the basis of fitted model parameters, strongly correlates with the concentration of free αvβ3. Next, we showed that 20-h postinjection scans facilitated quantification of nonspecific internalization of tracer by tumor cells (kint), which is shown to occur at a slow rate relative to specific binding (k3) and dissociation (k4) and, thus, kint can be neglected for 1- to 2-h dynamic scans. Third, this model has potential for clinical applications, as demonstrated by the comparison of our results with a previous pharmacokinetic study in patients with cancer, in which the model-based values of VND and VS are similar, and the observation that VS can be approximated using a single blood sample and static PET scan.
We thank Dr. David Stout, Dr. Arion Chatziioannou, Waldemar Ladno, and Judy Edwards at the Crump Institute for Molecular Imaging for technical assistance in small-animal imaging; David Truong, David Vu, and Weber Shao (Crump) for computer support; and Stephan Schwarz at the Department of Nuclear Medicine, Medical University of Innsbruck, for excellent technical assistance in producing c(RGDfK(DOTA)). Funding was provided by NCI cancer education grant R25-CA098010 and NIBIB R01-EB001943.