njit-etd2003-081 - New Jersey Institute of Technology
njit-etd2003-081 - New Jersey Institute of Technology njit-etd2003-081 - New Jersey Institute of Technology
217 In addition, group-average transfer function estimates were derived for all the studies by using a weighting algorithm based on the coherence estimates 7 2 (f) for each individual transfer function [29]. However, in this research the MATLAB System Identification toolbox is used to estimate the transfer function. As one can see below, with minor modification to the programs in the toolbox, the model transfer function can be easily obtained and the results are quite acceptable. Once the transfer function is obtained, the cardiovascular system model for normal subjects is estimated. It can now be examined and be used for further investigation. This estimated model of normal subjects would also be used as reference in developing the diseased cardiovascular model for COPD patients. Figures 5.55 — 5.59 present the case of a file from a normal subject resting and breathing at 14 breaths per minute (bpm). The HRV iibi signal was derived from the ECG signal and the first half of this signal was used as output of the cardiovascular model while the first half of the respiration signal was used as the single input. The two halves of the input/output were used to calculate the coefficients of the transfer function for the model. Figure 5.55 shows the rsp input and the iibi signal derived from the actual ECG as output. Below the figure are the transfer function coefficients of the estimated model in System Identification format. The basic format for representing models in the System Identification Toolbox is called the theta format. It stores all relevant information about the model structure used, including the values of the estimated parameters, the estimated
218 covariances of the parameters, and the estimated variance and so on. It also contains some information about how and when the model was created. Figure 5.55 Plot of output HR IIBI (Top) and input RSP (Bottom) signals. » present(th); This matrix was created by the command ARX on 4/16 2001 at 5:55 Loss fcn: 0.071384 Akaike's FPE: 0.071431 Sampling interval 0.005 The polynomial coefficients and their standard deviations are: B= Columns 1 through 7 0 0 0 -0.0072 -0.0103 -0.0008 -0.0003 0 0 0 0.0174 0.0177 0.0180 0.0181
- Page 195 and 196: 166 HRV more information about HRV
- Page 197 and 198: 168 Figure 5.9 (c) CWD plots of a n
- Page 199 and 200: Figure 5.10 CWT (Morlet) HRV plot o
- Page 201 and 202: 172 The following figures show the
- Page 203 and 204: 174 Figure 5.15 CWT (Mexican Hat) H
- Page 205 and 206: 176 5.2.5 Best Wavelet Selection fo
- Page 207 and 208: 178 Table 5.1 Correlation Indices o
- Page 209 and 210: 180 5.2.6 Vagal Tone and Sympathova
- Page 211 and 212: 182 These figures basically show th
- Page 213 and 214: 184 Figure 5.20 Sympathetic and par
- Page 215 and 216: 186 Figure 5.24 Sympathetic and par
- Page 217 and 218: 188 5.2.7 Time-Frequency Analysis (
- Page 219 and 220: 190 Figure 5.29 3D and contour plot
- Page 221 and 222: 192 Figure 5.33 3D and contour plot
- Page 223 and 224: 194 Figure 5.34 Sympathetic and par
- Page 225 and 226: 196 Figure 5.38 Sympathetic and par
- Page 227 and 228: 198 Figure 5.42 Sympathetic and par
- Page 229 and 230: Figure 5.44 Plot of raw respiration
- Page 231 and 232: Figure 5.46 The LF partial coherenc
- Page 233 and 234: Figure 5.48 HF partial coherence pl
- Page 235 and 236: Table 5.2 Cross-Spectral Analysis o
- Page 237 and 238: Table 5.3 Cross-Spectral Analysis o
- Page 239 and 240: Figure 5.50 HF coherence of COPD (1
- Page 241 and 242: 212 For better presentation of the
- Page 243 and 244: Figure 5.53 Coherence and partial c
- Page 245: 216 2. Interpretation of the transf
- Page 249 and 250: 220 deviations are interpreted as A
- Page 251 and 252: 222 Figure 5.58 Bode plot of the HR
- Page 253 and 254: 224 In this section a simple model
- Page 255 and 256: 226 The data for all 47 COPD subjec
- Page 257 and 258: 228 Figure 5.60 Normal and COPD cla
- Page 259 and 260: 230 Figure 5.61 Normal and COPD cla
- Page 261 and 262: 232 Figure 5.62 Normal classificati
- Page 263 and 264: 234 5.7 Cluster Analysis The purpos
- Page 265 and 266: 236 Figure 5.64 Severity classifica
- Page 267 and 268: 238 both the normal and COPD subjec
- Page 269 and 270: 240 In summary, COPD subjects had h
- Page 271 and 272: APPENDIX A EXERCISE PHYSIOLOGY A.1
- Page 273 and 274: 244 A.3 Figure Out Your Target Hear
- Page 275 and 276: APPENDIX B ANALYSIS PROGRAM LISTING
- Page 277 and 278: 248 4) Click on file, close to exit
- Page 279 and 280: 250 • TN 11
- Page 281 and 282: 252 B.1.2 Partial Coherence Between
- Page 283 and 284: 254
- Page 285 and 286: 256 Block Diagram !rime of record K
- Page 287 and 288: 258
- Page 289 and 290: 260 B.2.2 Time — Frequency Analys
- Page 291 and 292: 262 This program provides the STFT
- Page 293 and 294: 264 G(:j+1)=G(:,j+1)/(2*sum(G(:j+1)
- Page 295 and 296: 266 T=(length(Signa)/sample)/(Times
217<br />
In addition, group-average transfer function estimates were derived for all the studies by<br />
using a weighting algorithm based on the coherence estimates 7 2 (f) for each individual<br />
transfer function [29].<br />
However, in this research the MATLAB System Identification toolbox is used to<br />
estimate the transfer function. As one can see below, with minor modification to the<br />
programs in the toolbox, the model transfer function can be easily obtained and the results<br />
are quite acceptable. Once the transfer function is obtained, the cardiovascular system<br />
model for normal subjects is estimated. It can now be examined and be used for further<br />
investigation. This estimated model <strong>of</strong> normal subjects would also be used as reference<br />
in developing the diseased cardiovascular model for COPD patients.<br />
Figures 5.55 — 5.59 present the case <strong>of</strong> a file from a normal subject resting and<br />
breathing at 14 breaths per minute (bpm). The HRV iibi signal was derived from the<br />
ECG signal and the first half <strong>of</strong> this signal was used as output <strong>of</strong> the cardiovascular model<br />
while the first half <strong>of</strong> the respiration signal was used as the single input. The two halves<br />
<strong>of</strong> the input/output were used to calculate the coefficients <strong>of</strong> the transfer function for the<br />
model.<br />
Figure 5.55 shows the rsp input and the iibi signal derived from the actual ECG as<br />
output. Below the figure are the transfer function coefficients <strong>of</strong> the estimated model in<br />
System Identification format. The basic format for representing models in the System<br />
Identification Toolbox is called the theta format. It stores all relevant information about<br />
the model structure used, including the values <strong>of</strong> the estimated parameters, the estimated