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From this comparison it was concluded that much lower doses are needed from HFA pMDIs compared to CFC pMDIs to achieve the same clinical effect [48]. The improvement is contributed to the much smaller particles delivered by HFA pMDIs, having a MMAD of 1.1�C1.5?��m versus 3.5�C4.0?��m from the CFC holding pMDIs, which facilitates higher deposition in the peripheral lung from the HFA pMDI. However, another even more substantial difference between both types of pMDIs is their plume velocity, which (without valved holding chamber) causes approx. 90% oropharyngeal deposition from CFC containing pMDIs versus 30% from HFA devices [49]. The corresponding doses delivered to the lung are 10% and 70% and it may be expected that a seven-fold lung dose gives a better clinical effect in spite of a lower deposition efficiency for the smaller particles (Fig.?4). In Fig.?4, the mass fraction exhaled for monodisperse particles as function http://www.selleckchem.com/products/sch772984.html of the particle diameter is presented [31]. The trends measured for 1.5; 3 and 6?��m particles (two different flow rates) are extrapolated to 1?��m particles (red markers) and they are compared with the settling time needed to fall a distance equal to the diameter of a respiratory bronchiole (0.43?mm). The fair match between both relationships seems to indicate that the extrapolated data points have a realistic value. With this inefficient deposition for small particles in mind, the expectation that DPIs producing extra fine aerosols Ritonavir will give improved clinical effect too compared to conventional DPIs, may be false considering that not only the particle size distribution, but also the this website flow rate with which the aerosol is delivered is important. Such fine aerosols contain substantial particle mass fractions