| Literature DB >> 35800697 |
Paras Jain1, Walaa F Alsanie2,3, Dulio Oseda Gago4, Gilder Cieza Altamirano5, Rafaél Artidoro Sandoval Núñez5, Ali Rizwan6, Simon Atuah Asakipaam7.
Abstract
ECG (electrocardiogram) identifies and traces targets and is commonly employed in cardiac disease detection. It is necessary for monitoring precise target trajectories. Estimations of ECG are nonlinear as the parameters TDEs (time delays) and Doppler shifts are computed on receipt of echoes where EKFs (extended Kalman filters) and electrocardiogram have not been examined for computations. ECG, certain times, results in poor accuracies and low SNRs (signal-to-noise ratios), especially while encountering complicated environments. This work proposes to track online filter performances while using optimization techniques to enhance outcomes with the removal of noise in the signal. The use of cost functions can assist state corrections while lowering costs. A new parameter is optimized using IMCEHOs (Improved Mutation Chaotic Elephant Herding Optimizations) by linearly approximating system nonlinearity where multi-iterative function (Optimized Iterative UKFs) predicts a target's unknown parameters. To obtain optimal solutions theoretically, multi-iterative function takes less iteration, resulting in shorter execution times. The proposed multi-iterative function provides numerical approximations, which are derivative-free implementations. Signals are updated in the cloud environment; the updates are received by the patients from home. The simulation evaluation results with estimators show better performances in terms of reduced NMSEs (normalized mean square errors), RMSEs (root mean squared errors), SNRs, variances, and better accuracies than current approaches. Machine learning algorithms have been used to predict the stages of heart disease, which is updated to the patient in the cloud environment. The proposed work has a 91.0% accuracy rate with an error rate of 0.05% by reducing noise levels.Entities:
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Year: 2022 PMID: 35800697 PMCID: PMC9256335 DOI: 10.1155/2022/3773883
Source DB: PubMed Journal: Comput Intell Neurosci
Figure 1Block diagram of the proposed ECG.
LFM radar values of scenario I and scenario II used for simulation.
| S.N. | Quantity | Values for scenario 1 | Values for scenario 2 |
|---|---|---|---|
| 1 | Number of pulses (M) | 10 | 20 |
| 2 | Number of frequency intervals (L) | 500 | 500 |
| 3 | Frequency increment (∆f) | 10 MHz | 10 MHz |
| 4 | Pulse duration (T0) | 5 us | 200 us |
| 5 | Pulse repetition interval (Tpri) | 1 ms | 0.4 ms |
| 6 | Centre frequency (fc) | 10 GHz | 9 GHz |
Modified NCs. Two monostatic ECG with different parameter values were studied and are listed in Table 1 for scenarios 1 and 2, which refer to the two ECG [34]. Scenario 1 depicts realistic LFM ECG, where parameter values differ from those of scenario 2's ECG.
Figure 2For scenario 1, NMSE plots of time delay estimation with estimators based on KLMS-modified NC, UKFs, EKFs, and OIUKF.
Figure 3NMSE plots of Doppler shift estimation for scenario 1 using estimators based on KLMS-modified NC, UKFs, EKFs, and OIUKF.
NMSE estimation values of scenario I for estimators.
| No. of iterations ( | Time delay estimation | Doppler shift estimation | ||||||
|---|---|---|---|---|---|---|---|---|
| KLMS-modified NC | EKF | UKF | OIUKF | KLMS-modified NC | EKF | UKF | OIUKF | |
| 1000 | 1.28 | 0.095 | 0.044 | 0.0091 | 0.97 | 0.095 | 0.044 | 0.0082 |
| 2000 | 1.12 | 0.082 | 0.036 | 0.0067 | 0.68 | 0.072 | 0.026 | 0.0064 |
| 3000 | 0.98 | 0.055 | 0.022 | 0.0054 | 0.51 | 0.064 | 0.022 | 0.0042 |
| 4000 | 0.67 | 0.045 | 0.015 | 0.0046 | 0.43 | 0.051 | 0.015 | 0.0026 |
| 5000 | 0.42 | 0.029 | 0.012 | 0.0032 | 0.36 | 0.045 | 0.0092 | 0.00094 |
Figure 4For scenario 2, NMSE plots of time delay estimation with estimators based on KLMS-modified NC, UKFs, EKFs, and OIUKF.