A mathematical model of aerosol delivery from holding chambers (spacers) wa
s developed incorporating tidal volume (V-T), chamber volume (V-ch), appara
tus dead space (V-D), effect of valve insufficiency and other leaks, loss o
f aerosol by immediate impact on the chamber wall, and fallout of aerosol i
n the chamber with time. Four different spacers were connected via filters
to a mechanical lung model, and aerosol delivery during "breathing" was det
ermined from drug recovery from the filters. The formula correctly predicte
d the delivery of budesonide aerosol from the AeroChamber (Trudell Medical,
London, Ontario, Canada), NebuChamber (Astra, Sodirtalje, Sweden) and Nebu
haler (Astra) adapted for babies. The dose of fluticasone proprionate deliv
ered by the Babyhaler (Glaxco Wellcome, Oxbridge, Middlesex, UK) was 80% of
that predicted, probably because of incomplete priming of this spacer. Of
the above-mentioned factors, initial loss of aerosol by impact on the chamb
er wall is most important for the efficiency of a spacer. With a V-T of 195
mt, the AeroChamber and Babyhaler were emptied in two breaths, the NebuCha
mber in four breaths, and the Nebuhaler in six breaths. Insufficiencies of
the expiratory valves were demonstrated by comparison of pressure flow curv
es during "inspiratory" flow with and without occluded expiratory openings.
Insufficient inspiratory valves were demonstrated by comparison of "expira
tory" pressure flow curves with and without occluded inspiratory openings.
With children breathing through the spacers, mask pressure variations were
generally on the same order as that seen with the mechanical respirator, su
pporting the clinical relevance of the in vitro findings.