The dataset consists of two populations of fetuses: 160 healthy and 102 Late Intra Uterine Growth Restricted (IUGR). Late IUGR is an adverse pathological condition encompassing chronic hypoxia as a consequence of placental insufficiency, resulting in an abnormal rate of fetal growth. In standard clinical practice, Late IUGR diagnosis can only be suspected in the third trimester and ultimately confirmed at birth. This data collection comprises of a set of 31 Fetal Heart Rate (FHR) indices computed at different time scales and domains accompanied by the clinical diagnosis.
The data for healthy and Late IUGR populations are included in a single .xlsx file.
Participants are listed by rows and features by columns. In the following we report an exhaustive list of features contained in the dataset accompanied by their units, time interval employed for the computation, and scientific literature references:
Fetal and Maternal Domains
- Clinical Diagnosis [HEALTHY/LATE IUGR]: binary variable to report the clinical diagnosis of the participant
- Gestational Age [days]: gestational age at the time of CTG examination
- Maternal Age [years]: maternal age at the time of CTG examination
- Sex [Male (1)/Female (2)]: fetal sex
Morphological and Time Domains
- Mean FHR [bpm] – 1-min epoch: the mean of FHR excluding accelerations and decelerations
- Std FHR [bpm] – 1-min epoch: the standard deviation of FHR excluding accelerations and decelerations
- DELTA [ms] – 1-min epoch: defined in accordance with ,  excluding accelerations and decelerations
- II  – 1-min epoch: defined in accordance with ,  excluding accelerations and decelerations
- STV [ms] – 1-min epoch: defined in accordance with ,  excluding accelerations and decelerations
- LTI [ms] – 3-min epoch: defined in accordance with ,  excluding accelerations and decelerations
- ACC_L [#] – entire recording: the count of large accelerations defined in accordance with , 
- ACC_S [#] – entire recording: the count of small accelerations defined in accordance with , 
- CONTR [#]– entire recording: the count of contractions defined in accordance with , 
- LF [ms²/Hz] – 3-min epoch: defined in accordance with , LF band is defined in the range [0.03 - 0.15] Hz
- MF [ms²/Hz] – 3-min epoch: defined in accordance with , MF band is defined in the range [0.15 - 0.5] Hz
- HF [ms²/Hz] – 3-min epoch: defined in accordance with , HF band is defined in the range HF [0.5 - 1 Hz]
- ApEn [bits] – 3-min epoch: defined in accordance with , m = 1, r = 0.1*standard deviation of the considered epoch
- SampEn [bits] – 3-min epoch: defined in accordance with , m = 1, r = 0.1*standard deviation of the considered epoch
- LCZ_BIN_0 [bits] – 3-min epoch: defined in accordance with , binary coding and p = 0
- LCZ_TER_0 [bits] – 3-min epoch: defined in accordance with , tertiary coding and p = 0
- AC/DC/DR [bpm] – entire recording: defined in accordance with –, considering different combinations of parameters T and s, L is constant and equal 100 samples; e.g, AC_T1_s2 is defined as the acceleration capacity computed setting the parameters T = 1 and s = 2
 D. Arduini, G. Rizzo, A. Piana, P. Bonalumi, P. Brambilla, and C. Romanini, “Computerized analysis of fetal heart rate—Part I: description of the sys- tem (2CTG),” J Matern Fetal Invest, vol. 3, pp. 159–164, 1993.
 M. G. Signorini, G. Magenes, S. Cerutti, and D. Arduini, “Linear and nonlinear parameters for the analysis of fetal heart rate signal from cardiotocographic recordings,” IEEE Trans. Biomed. Eng., vol. 50, no. 3, pp. 365–374, 2003.
 FIGO, “Guidelines for the Use of Fetal Monitoring,” Int. J. Gynecol. Obstet., vol. 25, pp. 159–167, 1986.
 R. Rabinowitz, E. Persitz, and E. Sadovsky, “The relation between fetal heart rate accelerations and fetal movements.,” Obstet. Gynecol., vol. 61, no. 1, pp. 16–18, 1983.
 S. M. Pincus and R. R. Viscarello, “Approximate entropy: a regularity measure for fetal heart rate analysis.,” Obstet. Gynecol., vol. 79, no. 2, pp. 249–55, 1992.
 D. E. Lake, J. S. Richman, M. P. Griffin, and J. R. Moorman, “Sample entropy analysis of neonatal heart rate variability,” Am. J. Physiol. - Regul. Integr. Comp. Physiol., vol. 283, no. 3, pp. R789–R797, 2002.
 A. Lempel and J. Ziv, “On the complexity of finite sequences,” IEEE Trans. Inf. Theory, vol. 22, no. 1, pp. 75–81, 1976.
 A. Bauer et al., “Phase-rectified signal averaging detects quasi-periodicities in non-stationary data,” Phys. A Stat. Mech. its Appl., vol. 364, pp. 423–434, 2006.
 A. Fanelli, G. Magenes, M. Campanile, and M. G. Signorini, “Quantitative assessment of fetal well-being through ctg recordings: A new parameter based on phase-rectified signal average,” IEEE J. Biomed. Heal. Informatics, vol. 17, no. 5, pp. 959–966, 2013.
 M. W. Rivolta, T. Stampalija, M. G. Frasch, and R. Sassi, “Theoretical Value of Deceleration Capacity Points to Deceleration Reserve of Fetal Heart Rate,” IEEE Trans. Biomed. Eng., pp. 1–10, 2019.
This dataset aims at providing a toy demo for the comparison between the doubly orthogonal matching pursuit (DOMP) and its predecessor, the OMP.
- toydemo.m: Main file. It provides a comparison of the algorithms by loading the measurement and performing a behavioral model of the PA.
- demo_meas.mat: example of the input and output measurements of a power amplifier (PA) working under a 15-MHz LTE signal sampled at a sampling rate of 92.16MHz.
- model_gmp_domp_omp.m: generates the model structure and calls the pruning techniques.
- omp_domp.m: executes the OMP and DOMP techniques.
S&P 500 index of monthly data of bull/bear markets
Reinforcement Learning (RL) agents can learn to control a nonlinear system without using a model of the system. However, having a model brings benefits, mainly in terms of a reduced number of unsuccessful trials before achieving acceptable control performance. Several modelling approaches have been used in the RL domain, such as neural networks, local linear regression, or Gaussian processes. In this article, we focus on a technique that has not been used much so far:\ symbolic regression, based on genetic programming.
The proposed signals are used for electromagnetic-based stroke classification. Six realistic head phantom computed from MRI scans, is surrounded by an antenna array of 16 dipole antennas distributed uniformly around the head. These antennas are deployed in a fixed circular array around the head, at a distance of approximately 2-3 mm from the head. A Gaussian pulse covering the bandwidth from 0:7 to 2 GHz is emitted from each of the antennas, sequentially, while all of the antennas capture the scattered signals. Since 16 antennas were used, there are a total of 256 channel signals (i.e.
The proposed hardware architecture is modelled by Verilog HDL and synthesized by a Synopsys Design compiler with Semiconductor Manufacturing International Corporation (SMIC) 65-nm CMOS technology. The upload files are the systhesis reports.
When heterogeneous honeycomb materials are cut using ultrasonic techniques, the ultrasonic frequency tends to vary over time, thereby degrading the quality of the machining. This variation can be addressed with a proportional–integral–derivative (PID) controller; however, these controllers perform relatively poorly in fixed parameter tracking scenarios. In contrast, this paper proposes a tracking model that combines fuzzy and PID control.
This is the Smulation Data for Power System State Estimation.