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Wavelet-transformed-electrocardiographic (WT-ECG) signals were measured using PC software that we developed (BIOMAS for Wavelet, version 3.0, Elmec Co. Ltd., Tokyo, Japan). The Morlet wavelet was applied to measure WT-ECG signals with a wavelet function consisting of 40 scale bands, corresponding [http://www.selleckchem.com/products/ipi-145-ink1197.html Duvelisib chemical structure] to a target frequency between 5?Hz and 300?Hz. The time�Cfrequency power was calculated using the same formula reported in the previous studies [17], [18]?and?[19]. Of the ECGs that were to be analyzed, we eliminated twelve percent that had baseline drift and visual noise between U�CP segments and were judged inappropriate for frequency analysis by CWT. A single QRS from a V1 chest lead was analyzed in patients with antero-septal, localized anterior, and antero-lateral MI, whereas limb lead II was analyzed in those with inferior, infero-lateral and infero-posterior MI. We investigated the effects of fibroblasts on the frequency power during QRS using a 2-D ventricular [http://www.selleckchem.com/products/Bleomycin-sulfate.html Bleomycin concentration] tissue model with diffuse fibroblast distribution, as described by Xie et al. [20]. The model is explained in detail in the appendix. A 25-��m-thick 2-D tissue model was divided into cubes with sides 25?��m long. One fibroblast accounts for one box (one unit), whereas a myocyte accounts for five boxes in a row. The total size of the model was 400?��?400 units with 10?��?10?mm side lengths. The long axes of myocytes were arranged in parallel and their common direction determined the longitudinal fiber orientation of the myocardial layer (see Appendix). Fibroblasts were randomly inserted between [http://en.wikipedia.org/wiki/PRDX4 PRDX4] myocytes. The amount of fibrosis was specified by the fibroblast�Cmyocyte ratio (r), which is the number of fibroblasts divided by the number of myocytes in the tissue. Neither electromotive force (EMF) nor the ECG has been addressed in previous descriptions of 2-D tissue models [20]. Therefore, we devised a method with which to measure the EMF generated in the 2-D tissue model (see Appendix), based on the assumption that the spatial gradient of the membrane potential is proportional to the EMF density [21]. Fibroblasts do not generate EMF since their membranes are ��passive.�� The total EMF, which is obtained by summing the scalar components of unit vectors derived from small areas of ~?1?mm width in the model, is considered to be an instantaneous pseudo-QRS, and the time course of the pseudo-QRS during the excitation process corresponds to a fraction of the QRS in a human ECG. Statistical significance in multiple-group comparisons was assessed using a one-way analysis of variance (ANOVA), followed by Tukey's honestly significant difference adjustment for multiple comparisons. Categorical data were compared using the ��2 test with Yates correction for 2?��?2 tables. These statistical values were calculated using SPSS Base 11.0J. Data are expressed as means?��?1 SD (standard deviation). A value of p?