Dispersion of input function

The measured blood curve after a radiotracer bolus is smeared out, because of inhomogeneous velocity fields in the vessels and in the catheter and detector assemblies. Also sticking of radiotracer to the tubing may add to this dispersion effect. While different distance and blood velocity in different arteries causes variable appearance time (delay) of radioactivity in the blood between sampling sites and the tissue being scanned, dispersion affects the shape of the blood curve, especially at the time of the blood curve peak after bolus administration. In manual blood sampling the volume of each sample is relatively large compared to the volume of blood in catheter, making dispersion effects in tubing negligible; with flow-through detectors long tube lengths can lead to considerable dispersion (Votaw & Shulman, 1998).

Dispersion does not affect the AUC0-T of blood TAC, after T is large enough. Therefore, dispersion correction is necessary only when very fast kinetics are measured, for example perfusion measurement with radiowater (Kanno et al., 1987), and when precise estimates of K1 and other individual parameters of compartmental models are fitted. Multiple-time graphical analysis methods (Logan and Patlak plots) are relatively insensitive to dispersion (Blais & Lee, 2015).

Bolus curve is distorted during its passage in vasculature Measured blood TAC is distorted by dispersion
Figure 1. After intravenous bolus infusion, depicted with rectangular (boxcar) function (black), venous blood that contains the radiotracer travels to right atrium and ventricle, from there to the lungs, and left atrium and ventricle of the heart. At this stage the blood TAC (red) is already dispersed and delayed, but well-mixed, so that similar concentration of radiotracer is distributed from the heart into the whole arterial network. Depending on the diameter and length of the arteries, blood TAC is more dispersed and delayed; short distance and high blood flow into the brain causes less dispersion and delay (purple) than in the radial artery which is common blood sampling site (blue). Sampling apparatus causes additional dispersion and delay to the measured blood TAC (green).
To retrieve correct input function for the brain, the measured blood TAC must be corrected for the delay and dispersion to match the blood TAC in the arteries of the brain.
This figure is based on a simplistic simulation, assuming no recirculation.

In theory, input function is the same for all organs and can be measured from arterial blood, but since dispersion effect differs for the measured and true input function to the region of interest, this is not strictly true (Figure 1), unless dispersion correction is applied. Venous blood sampling causes additional delay, dispersion and other biases.

Arterial time-activity curves following intravenous bolus administration have been observed to be of the form of the gamma variate function because of dispersion, or sums of gamma variate functions when recirculation is taken into account, too. The recirculation starts to affect the arterial curve very soon, because coronary circulation time is only few seconds. Arterial input curve is thus dispersed already before entering any tissue, and this part of dispersion, and recirculation effect, obviously must not be corrected (van den Hoff et al., 1993).

Iida et al (1986) suggested that a single monoexponential function d(t) could be used to represent the effect of dispersion:

, where τ denotes the time constant of dispersion. The measured arterial curve Cmeas(t) and the true arterial curve Ctrue(t) are related as:

, where ⊗ denotes the operation of convolution. Essentially, this is a compartmental model, where the first compartment represents the concentration before dispersion, and the second compartment the concentration in the compartment that can be measured.

Compartmental model for dispersion effect
Figure 2. Dispersion can be thought of been caused by a compartment through which the blood must flow before it is measured. The compartment represents arterial vasculature or blood tubing. The rate constants into and out of measurement compartment are k = 1 / τ.

This model can be described with an ordinary differential equation (ODE):

, where k = 1 / τ. Equation can be integrated, assuming that at time zero all concentrations are zero:

For discrete data the equation can be solved using definite integrals and Euler integration like a one-tissue compartment model, giving equation

, or, using dispersion time constant τ instead of k:

These equations can be used to simulate the effect of dispersion on input curves. For example, the simulations in Figure 1 were done using those; data and script can be downloaded from GitLab repository. Simulation of dispersion is also necessary as part of fitting procedure, when dispersion time constant for blood sampling equipment is estimated.

In addition to these exponential models, dispersion has been modelled using laminar flow model (Hutchins et al., 1986) and turbulent fluid flow model (Wollenweber et al., 1997).

Dispersion correction

Measured blood curve can be corrected for the dispersion using deconvolution methods. Dispersion correction should be done before time delay correction, or simultaneously (Meyer, 1989).

Dispersion corrected AUC0-T of blood TAC can be calculated from reorganized equation (4) when dispersion time constant τ is known

With the help of the integral curve, dispersion corrected blood curve can be calculated applying 2nd order Adams-Moulton method, based on Euler integration:

While this works with noiseless simulated data, with measured data the resulting curve would be very noisy. Calculation over three adjacent sample point provides slight smoothing and less noisy dispersion corrected blood curve:

Dispersion correction is essentially deconvolution, and adds noise to the blood curve. Regardless of that, dispersion correction should not be accompanied by smoothing (Wollenweber et al., 1997). Munk et al. (2004 and 2008) proposed a dispersion correction method with less noise problem.

If a function is fitted to the input curve, the dispersion correction can and should be included in the fitting: not only does it remove the problem with noise, but it improves the fit, too, since the functions are aimed for fitting input curves with little or no dispersion. Program fit_sinf can currently use up to two known dispersion time constants to fit function, representing dispersion corrected input curve, to the measured blood or plasma curve.

Dispersion in the detector system

With Automatic blood sampling system (ABSS) blood needs to be drawn via long tubing to minimize background radiation from the subject to the detectors. Most ABSSs are not compatible with MR, requiring long distance from PET-MR, even when ABSS detector is well shielded. Certain ABSSs are MR-compatible (Breuer et al., 2010). While long tubing increases the dispersion error, O’Doherty et al. (2015) have shown that dispersion correction can be successful even with 3 m arterial sampling tubing.

External dispersion of the input function can be determined by measuring the rising/falling edges of the detector system’s response to an input step function (Iida et al., 1986; Senda et al., 1988; Weinberg et al., 1988; Votaw & Shulman, 1998; Boellaard et al., 2001; Convert et al., 2007). Alternatively, a separate β-microprobe placed close to the arterial catheter could be used to measure the shape of the blood curve without most of the dispersion effects of the main detector system and blood tubing (Seki et al., 1998). Microprobe system could also work without the pump, relying only on the impedance of the system to control the blood flow (Wollenweber et al., 1996).

Internal dispersion

The internal (physiological) dispersion (caused by human vascular system) between the radial artery and the brain is 4-6 sec (Iida et al., 1986). The liver is especially difficult case with dual input (Keiding, 2012).

In heart PET studies, delay and dispersion (both internal and detector system) can be corrected by fitting the compartmental model (van den Hoff et al., 1993) to the curve of the LV cavity (Iida et al., 1989) or ascending aorta (Harms et al., 2014).

The methods for estimating delay and dispersion simultaneously have been developed with [15O]H2O data, where these effects can cause especially high biases, but applied to other radiotracers, too. [15O]H2O data is analyzed using single-tissue compartment model, which is applicable for delay and dispersion modelling with other tracers when only the initial part of the curves are used. Meyer (1989) gave the formula for simulating the tissue curve in the optimization procedure (notations changed):

, where CAm(t) is the measured arterial blood curve containing both delay, Δt, and dispersion, τ, errors. This was further investigated by Lüdemann et al (2006). The linearized version of this, proposed by van den Hoff et al. (1993), with the same notations is

Neither of these formulas include the vascular volume fraction, VA, which in case of radiowater represents only arterial volume fraction, and can quite safely be neglected in brain studies where even the total blood volume is <5%. The single-tissue compartmental model equation that includes the vascular volume fraction, with corrected input function, CA(t), is

Comparison of this to the previous equations used for fitting delay and dispersion shows that dispersion time constant and vascular volume fraction cannot be estimated independently. This can be utilized in time delay correction: dispersion does not affect the estimated delay time between input function and tissue curve, because vascular volume fraction accounts for the dispersion (Mourik et al., 2008).

Dispersion correction in Turku PET Centre

In Turku PET Centre, when the dispersion correction is necessary, it is usually done automatically by the blood data processing software: first, the external dispersion is corrected, and secondly the internal dispersion is corrected, if an estimate of internal dispersion time constant is available.

In Turku PET Centre, the external dispersion time constant has been estimated to be 2.5 sec for the assemblies that are currently in use. If tubing is changed, the dispersion time constant should be measured again.

Internal dispersion time constant of 5 sec has been used for the brain studies.

The corrections are done using disp4dft. Alternatively, the two dispersion time constants can be given to program fit_sinf to fit measured curve with function that represents dispersion corrected input curve.

The impact of dispersion can be simulated by adding dispersion to input curves. This can be done using disp4dft. Alternatively, same result can be obtained with convexpf that convolves TAC with exponential functions; set a1=b1=1/τ and a2=b2=a3=b3=0.

See also:


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Bol A, Vanmelckenbeke P, Michel C, Cogneau M, Goffinet AM. Measurement of cerebral blood flow with a bolus of oxygen-15-labelled water: comparison of dynamic and integral methods. Eur J Nucl Med. 1990; 17: 234-241. doi: 10.1007/BF00812363.

Iida H, Higano S, Tomura N, Shishido F, Kanno I, Miura S, Murakami M, Takahashi K, Sasaki H, Uemura K. Evaluation of regional difference of tracer appearance time in cerebral tissues using [15O]water and dynamic positron emission tomography. J Cereb Blood Flow Metab. 1988; 8: 285-288. doi: 10.1038/jcbfm.1988.60.

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Meyer E. Simultaneous correction for tracer arrival delay and dispersion in CBF measurements by the H215O autoradiographic method and dynamic PET. J Nucl Med. 1989; 30:1069-1078.

Munk OL, Keiding S, Bass L. A method to estimate catheter dispersion and to calculate dispersion-free blood time-activity curves. J Nucl Med. 2004; 45(5): 392P-393P.

Munk OL, Keiding S, Bass L. A method to estimate dispersion in sampling catheters and to calculate dispersion-free blood time-activity curves. Med Phys. 2008; 35(8): 3471-3481. doi: 10.1118/1.2948391.

O’Doherty J, Chilcott A, Dunn J. Effect of tubing length on the dispersion correction of an arterially sampled input function for kinetic modeling in PET. Nucl Med Commun. 2015; 36(11): 1143-1149. doi: 10.1097/MNM.0000000000000374.

Seki C, Okada H, Mori S, Kakiuchi T, Yoshikawa E, Nishiyama S, Tsukada H, Yamashita T. Application of a beta microprobe for quantification of regional cerebral blood flow with 15O-water and PET in rhesus monkeys. Ann Nucl Med. 1998; 12(1): 7-14.

van den Hoff J, Burchert W, Müller-Schauenburg W, Meyer G-J, Hundeshagen H. Accurate local blood flow measurements with dynamic PET: fast determination of input function delay and dispersion by multilinear minimization. J Nucl Med. 1993; 34:1770-1777.

Walker MD, Feldmann M, Matthews JC, Anton-Rodriguez JM, Wang S, Koepp MJ, Asselin M-C. Optimization of methods for quantification of rCBF using high-resolution [15O]H2 PET images. Phys Med Biol. 2012; 57: 2251-2271. doi: 10.1088/0031-9155/57/8/2251.

Wollenweber SD, Hichwa RD, Ponto LLB. A Simple on-line arterial time-activity curve detector for [O-15]water PET studies. IEEE Trans Nucl Sci. 1997; 44(4): 1613-1617. doi: 10.1109/23.597022.

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Updated at: 2019-02-08
Written by: Vesa Oikonen