# Graham’s compartmental model for input function

Compartmental models for arterial input function (AIF)
have been developed for PET data analysis and simulation,
specifically for [^{15}O]H_{2}O studies
(Maguire et al., 2003), and a
general AIF model for PET was presented by
Graham (1997):

In this model the radiopharmaceutical is introduced directly into the plasma compartment, and
therefore, instead of the boxcar function often used to represent infusion, Graham simulated
the bolus injection and bolus infusion with functions that include exponential terms.
The exponentials represent the initial dispersion that
distorts the bolus shape before it enters the arterial network for the first time.
Bolus injection was simulated with simple decaying exponential with time constant
*k _{i}*:

, where *H* represents the amount (radioactivity) of injected radiotracer (Figure 2),
with units of radioactivity/time.
Longer bolus with infusion duration *T _{dur}* was simulated with boxcar function
including exponential terms on both leading and trailing edges:

Definite integrals of the inputs for Graham’s compartmental plasma model, when considering not
only the duration of infusion *T _{dur}* but also the start time of bolus/infusion

*T*, are for the short bolus:

_{i}, and for the infusion:

Differential equations for the Graham’s compartmental model are (Graham, 1997):

The ordinary differential equations for discrete data can be
solved practically using the 2nd order Adams-Moulton
method, based on implicit Euler integration of the *n*th compartment:

, where *Δt* is the time between two samples.
To shorten the equations, we will below use term *E _{n}* for the part that only
contains data from previous data points:

and thus

Substitution of these into the equation for *C _{TF}* gives equations

These equations can be used to solve *C _{IF}* and its integral:

and with these, *C _{P}*:

The Graham’s model depicts slowly varying plasma activity over several minutes, but is not
intended to model the first-pass kinetics and recirculation effects with radiotracers such as
[^{15}O]H_{2}O.
As Graham points out,
all compartmental models will have a simple exponential behaviour at late times,
although many radiopharmaceuticals tend to have a slight upward convexity long times after
injection. This model cannot account for this phenomenon, nor the appearance of label-carrying
metabolites in the blood
or plasma.
Compartmental model for metabolite correction was
developed by Huang et al. (1991), and
Graham (1997) suggested combining the
compartmental models for plasma curve and
metabolites.
Graham et al (2000) used his
compartmental model for smoothing and interpolating TACs from aorta in a
FDG study to construct a
population-based input function.
Spence et al (2008) used the method to
extrapolate metabolite-corrected blood TAC in a
[^{18}F]FLT study.

In a slightly expanded version of the Graham’s compartmental model the blood (or plasma) compartment is separated into two compartments, arterial (BA) and venous (BV) (Figure 3). This adds dispersion that happens in the pulmonary circulation to the modelled arterial blood curve. Radiotracer is administered to the venous compartment, which accounts for the initial dispersion of bolus infusion, and therefore the infusion can be simulated using simple rectangular (boxcar) function. Tissue compartments are in parallel, not in series; kinetically the parallel model is indistinguishable from the model with compartments in series, but differential equations for the parallel model are simpler.

Differential equations for the compartments in the extended model are

The integrated forms of the ordinary differential equations for discrete data can be solved as above, giving equations

Integral for the boxcar function used to represent the infusion, starting at time
*T _{i}* and lasting for time

*T*, can be calculated as

_{dur}
Parent radiopharmaceutical could be metabolized in the tissues (*TS* and/or *TF*)
and/or in the circulation (*BV* and/or *AV*).
While metabolism and subsequent removal of the metabolite(s) from circulation can be accounted for
by the rate constant *k _{U}* in the model above, removal of parent tracer into
metabolite pool in other compartments can only be accounted for by adding rate constants for the
metabolism rates (Figure 4):

Differential equations for the parent radiopharmaceutical compartments in the extended model, including escape via metabolism, are

The integrated forms of the ODEs for discrete parent radiopharmaceutical concentrations are

*E*s are defined as before, and

_{X}Although the model is shown like the metabolites from in the tissue compartments or in the
venous and pulmonary system would return to the *BV* compartment, this model only accounts
for the disappearance of the parent radiopharmaceutical via metabolism, but does not actually
consider the fate of the labelled metabolite. However, the metabolites formed in this model setting
could be used as input for compartmental models
describing the plasma kinetics of the metabolites.

## See also:

- Compartmental models for input function
- Compartmental models for metabolite correction
- Fitting compartmental models
- Input for simulations
- Blood sampling
- Input function
- Modelling A-V difference
- Plasma pharmacokinetics

## References

Graham MM. Physiologic smoothing of blood time-activity curves for PET data analysis.
*J Nucl Med.* 1997; 38(7): 1161-1168.
PMID: 9225813.

Tags: Input function, Fitting, Compartmental model, Extrapolation

Updated at: 2019-05-26

Created at: 2003-03-30

Written by: Vesa Oikonen