Bolus tracking data obtained with paramagnetic intravascular tracers are commonly analyzed and quantified by the direct measurement of properties of the tissue concentration-time curve (e.g., time to peak (TTP)). The measurement of these "summary parameters" is used as an accessible alternative approach to the complex deconvolution procedure, and provides indirect measures of perfusion. However, summary parameters do not take into account differences in arterial input functions (AIFs) or residue functions (R(t)) between patients or studies. Simulations were performed to assess the variability of summary parameters over a realistic range of AIFs and for differing R(t), to establish whether they can be used as reliable measures of tissue perfusion status. Results showed that the value of each summary parameter investigated is highly dependent upon both the AIF and R(t). The referencing of summary parameters to their corresponding value in the AIF or in normal tissue is a method commonly used to normalize results, but this approach did not lead to any measures that were independent of both the AIF and R(t) in this study. The results presented here show that the use of summary parameters requires considerable caution, since tissue or patient types can easily be incorrectly classified due to the effect of variations in patient AIF and R(t). Dynamic susceptibility contrast (DSC) MRI is increasingly used for the measurement of cerebral perfusion (1). This method requires the injection of a bolus of a paramagnetic intravascular contrast agent, and the rapid measurement of the MR signal loss caused by the passage of the bolus through the tissue. This signal loss can be converted to a concentration-time curve of contrast agent within the tissue, C(t). Using principles of indicator dilution theory, C(t) within a region of interest (ROI) can be expressed as a convolution (1,2):where C a (t) is the arterial input function (AIF), i.e., the concentration of tracer entering the ROI, and R(t) is the residue function, which describes the fraction of contrast agent remaining in the ROI at time t, following the injection of an ideal bolus at t ϭ 0. CBF is cerebral blood flow, is the density of brain tissue, and k H accounts for the difference in hematocrit between capillaries and large vessels. There are two commonly used approaches to the analysis and quantification of DSC data. The first requires measurement of the AIF in order to perform the deconvolution of C(t) using Eq. [1] (2). This method can produce direct information about the physiological parameters CBF, cerebral blood volume (CBV), and mean transit time (MTT), but involves very time-consuming postprocessing. The second approach uses summary parameters calculated directly from the profile of the C(t) curve (e.g., time to peak (TTP), maximum peak concentration (MPC), etc.). This is a commonly used method (see for example Refs. 3-10) because the analysis of data is fast and straightforward, and does not necessarily require measurement of the AIF. However, summary paramete...