Research article

Economic, ecological and social benefits through redistributing revenues from increased mineral oil taxation in Austria: A triple dividend

  • To meet the future energy and climate targets in 2030 and 2050 in Austria, it is absolutely necessary to apply extensive measures to reduce the use of fossil fuels. By then, Austria will have to realize a 36% decrease (from 2005 levels) for emission sources outside the European Emission Trading System. The transport sector is a key driver of recently increasing greenhouse gas emissions in Austria. Hence, we examine the macroeconomic and ecologic impacts of an environmental tax reform in Austria from 2020 to 2030. We implement a revenue-neutral tax reform that raises revenues via an increase of the mineral oil tax on diesel and petrol consumption and redistributes these fiscal revenues to the industry and households. In addition, increased fossil fuel taxing would enhance revenues for green investments in e-mobility and thermal refurbishment that stimulate the Austrian economy. The simulation analyses focus on central macroeconomic variables as gross domestic product, employment, investment and private consumption and carbon dioxide emissions. We find that the proposed environmental tax reform generates a triple dividend, leading simultaneously to economic growth and the reduction of greenhouse gas emissions while low-income households can be fully compensated.

    Citation: Sebastian Goers, Friedrich Schneider. Economic, ecological and social benefits through redistributing revenues from increased mineral oil taxation in Austria: A triple dividend[J]. Green Finance, 2019, 1(4): 442-456. doi: 10.3934/GF.2019.4.442

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  • To meet the future energy and climate targets in 2030 and 2050 in Austria, it is absolutely necessary to apply extensive measures to reduce the use of fossil fuels. By then, Austria will have to realize a 36% decrease (from 2005 levels) for emission sources outside the European Emission Trading System. The transport sector is a key driver of recently increasing greenhouse gas emissions in Austria. Hence, we examine the macroeconomic and ecologic impacts of an environmental tax reform in Austria from 2020 to 2030. We implement a revenue-neutral tax reform that raises revenues via an increase of the mineral oil tax on diesel and petrol consumption and redistributes these fiscal revenues to the industry and households. In addition, increased fossil fuel taxing would enhance revenues for green investments in e-mobility and thermal refurbishment that stimulate the Austrian economy. The simulation analyses focus on central macroeconomic variables as gross domestic product, employment, investment and private consumption and carbon dioxide emissions. We find that the proposed environmental tax reform generates a triple dividend, leading simultaneously to economic growth and the reduction of greenhouse gas emissions while low-income households can be fully compensated.


    HRV analysis is widely used for cardiovascular health monitoring and disease prediction [1,2]. It is also considered an important indicator to evaluate the control of cardiac autonomic nervous balance [3,4], which is related to physical activity [2], mental stress [1] and sleep health [5,6]. The crux of HRV analysis involves studying the fluctuations in time intervals between successive heartbeats, known as inter-beat intervals. Typically, the inter-beat interval is gauged as the time between two consecutive R-peak (R-R interval or RRi) ECG signals. Given that the precision of HRV analysis is contingent on accurately pinpointing R-peaks within the ECG signal, the development of a high-precision R-peak localization algorithm is of paramount significance.

    For over four decades, the field of automated R-peak detection has undergone extensive exploration. Numerous algorithms targeting R-peak or QRS detection have been made available to the public [7,8], leveraging diverse principles like template matching [9,10,11], derivative analysis [12,13], digital filtering [14,15,16], wavelet transform [17,18], Hilbert transform [19,20], morphology classification [21], phase space reconstruction [22] and dynamic thresholding [23,24,25,26,27]. Despite these advancements, formulating a robust and universally accepted algorithm remains a challenge, given the diverse morphological differenes present in ECG signals [28]. The incorporation of machine learning, particularly deep neural networks [29,30,31], has significantly enhanced the sensitivity of R-peak or QRS detection, surpassing the 99.9% mark. However, the crux of the matter is that, instead of accurately pinpointing the chronological localization of R-peaks, current algorithms primarily emphasize sensitivity and overall accuracy in detecting R-peaks, accommodating a certain temporal discrepancy between actual and detected R-peaks [32].

    This study centers on developing an algorithm to accurately identify the exact positions of R-peaks within ECG signals. This is achieved by enhancing an existing R-peak detection method. Among the available algorithms, we initiated our work by adapting the PT algorithm [33], which remains widely employed due to its robustness, efficiency and accuracy in R-peak detection [34]. The PT algorithm utilizes a moving-window-integration of 150 ms, a step that can occasionally lead to a random shift in the detected R-peak location. To address the lack of precision in R-peak localization, in particular from noisy or low-quality ECG data, we propose to first roughly localize the QRS complex through the computation and identification of the QRS envelope, and then refine the localization with a template matching method.

    The assessment of the proposed technique was carried out using the MIT-BIH Arrhythmia database [35], available through PhysioNet [36]. The database contained 48 thirty-minute records with a sample rate of 360 Hz, which were captured from a group of patients with 22 females and 25 males aged between 23 and 89 years. Notably, some of these records exhibited noticeable morphological distortions, particularly evident in the P and T waves of the ECG signal. Expert cardiologists annotated the database as a point of reference. Each record contained 2 leads, and lead I was used to evaluate the proposed algorithm.

    According to the Special Requirements for the Safety and Basic Performance of Dynamic ECG Systems from international standard IEC60601-2-47:2001, it is considered that the R-peak position is correctly detected by an algorithm if the R-peak position obtained by the algorithm is within 150 ms of the annotated position. The proposed algorithm is evaluated in terms of both the sensitivity of R-peak detection and the accuracy of the detected R-peak location. Sensitivity (Se), positive prediction value (PPV) and detection error rate (DER) are calculated by Eq (1) for the evaluation of R-peak detection [32]:

    Se=TPTP+FN×100%;PPV=TPTP+FP×100%;DER=FN+FPTP+FN×100% (1)

    where TP (true positive) refers to the number of correctly detected R-peaks, FN (false negative) refers to the number of undetected R-peaks which exist in annotation and FP (false positive) refers to the number of falsely detected R-peaks which do not exist in annotation (i.e., > 150 ms away from any annotated R-peaks).

    The accuracy of the detected R-peak location is evaluated by the annotated-detected error (ADE) with unit ms calculated by Eq (2) [32]:

    ADE=1TPTPn=1(KnDn)2Ts (2)

    where Kn refers to the annotated R-peak location, Dn refers to the detected R-peak location and Ts refers to ECG signal sampling period with unit ms.

    The R-peak position detected by the algorithm may have a group time delay with the annotated R-peak position. The final R-peak position group time delay needs to be compensated once for best alignment between the detected R-peaks and the annotated R-peaks with a fixed shift of several samples in each record. The group time delay is related to the filtering operation and also to the spectral characteristics of the QRS complex. Group time delay compensation is only used for fair comparison between different algorithms and has no effect on RRi calculation. Group time delay TD with unit ms can be simply calculated by Eq (3):

    TD=[1TPTPn=1(KnDn)]Ts (3)

    The PT algorithm consists of 5 processes: band-pass filter (BPF), derivative, squaring, moving window integration (MWI) and R-peak detection [33], as shown in Figure 1.

    Figure 1.  Functional block diagram of the Pan-Tompkins algorithm for R-peak detection. BPF: band-pass filter; MWI: moving window integration.

    The 5–15 Hz BPF was achieved by cascading a 15 Hz low-pass filter (LPF) cascaded with a 5 Hz high-pass filter (HPF). LPF was used to remove the high-frequency noise such as electromyogram (EMG) and power line interference [34]. HPF was used to remove the low-frequency interference, such as the baseline wander. Taking the derivative would enhance the slope information of the QRS complex and suppress the low-frequency P-wave and T-waves [34]. The squaring process was applied so that the positive and negative values were not canceled out in the following MWI process, and the QRS complex were further enhanced. The MWI process was performed with a 150 ms integration window to acquire the envelope of the R-wave. The 150-ms window width is used since it is slightly larger than that of a normal QRS complex for better adaptivity. We chose a third-party PT algorithm from NeuroKit [37] as a reference for performance evaluation. The source code is publicly available in Python on www.github.com.

    In the PT algorithm, the MWI process may result in an R-peak location shift because the maximum slope position of the rising edge of the integration waveform was not the precise R-peak temporal location [33]. The precise R-peak is on the point of minimum slope position of the rising edge of integration waveform in theory, which will be illustrated in discussion section. In addition, the 5–15 Hz BPF may result in distortion of QRS complex which will also be illustrated in the discussion section. These processes could result in temporal shifts of R-peaks from their real positions and need to be further improved for more precise localization of R-peaks.

    The proposed algorithm includes three stages (Figure 2). The first is the preprocessing stage, where the raw ECG signal is filtered by a 5–35 Hz BPF, which is achieved by a 35 Hz LPF cascaded with a 5 Hz HPF. The second stage calculates a window that marks the QRS complex, including 3 processes: squaring, 5 Hz LPF and windowing. The third stage is the template matching stage, in which a program auto-selected QRS template is taken to localize the R-peak by finding the maximum moving-window cross-correlation (CC) with the windowed pre-processed ECG signal.

    Figure 2.  Block diagram of the proposed method. BPF: band pass filter; HPF: high pass filter; LPF: low pass filter. X(i) is the ECG raw data. T(n) is the QRS template with 120-ms width. R(k) is the file of final R-peak position. Y(i), S(i), L(i), W(i), C(i) are signals during process.

    The windowing stage is inspired from the PT algorithm. A 5–35 Hz pass band is used here instead of the 5–15 Hz pass band for better performance and adaptability. The derivative process can highlight the slope characteristic of the QRS complex, but can also induce a phase shift, so it is not used in our algorithm. The MWI process is replaced by a forward-backward digital 5 Hz LPF for better noise filtering and zero-time delay. After the windowing transformation of L(i), windows with 200-ms width are generated in accordance with the center of the QRS envelopes.

    The template matching stage is an improvement for precise R-peak position detection. The QRS template is generated by automatic selection among the first five QRS windows from each ECG recording Y(i). Among the first five QRS complexes inside the window, the one with the median R-peak amplitude (absolute value) is selected. A 120 ms segment from the selected ECG waveform symmetrical about the R-peak position is taken as the template. One hundred twenty ms is determined because the width of 120 ms is the maximum width of normal QRS complexes [38]. The QRS template has a window width of N = 43 samples with a 360 Hz sampling rate, where N must be an odd number to ensure that the R-peak position is centered.

    The proposed method was implemented on Python 3.9 software and evaluated over the MIT-BIH Arrhythmia database to compare with the state-of-the-art PT algorithm.

    The filters used in the algorithm are all second-order forward-backward Butterworth infinite impulse response (IIR) filters with zero-phase delay. The forward-backward filtering processes are implemented as Eq (4) to Eq (6):

    Z(i)=b0X(i)+b1X(i1)+b2X(i2)c1Z(i1)c2Z(i2) (4)
    Z(i)=Z(i) (5)
    Y(i)=b0Z(i)+b1Z(i1)+b2Z(i2)c1Y(i1)c2Y(i2) (6)

    where X(i) is the original ECG data, Y(i) is the filtered signal and b0, b1, b2, c1, c2 are filter parameters. Equations (4) and (6) are difference equations of the IIR filter. Equation (5) is included to reverse Z(i) and pass it through the IIR filter again for zero-phase delay.

    Here, the 5–35 Hz BPF process is achieved by a 35 Hz LPF cascaded with a 5 Hz HPF. All filters are implemented with SciPy.signal.sosfiltfilt function available in Python. The first 4 s segment from record 209 was used to display the results of this stage, as shown in Figure 3.

    Figure 3.  An example of the input and output signals of the preprocessing stage. (a) ECG raw data, X(i); (b) signal after 5–35 Hz BPF, Y(i).

    This stage calculates a window to mark the QRS complex in each ECG beat. First, the Y(i) signal is squared to obtain S(i) according to Eq (7), which enhances the QRS complex:

    S(i)=Y(i)2 (7)

    Second, S(i) passes through a 5 Hz low-pass filter to obtain L(i) as the envelope of the QRS complex. Third, L(i) is converted into the window signal W(i) through dynamic thresholding. W(i) is composed of "0" and "1", where "1" indicates the interval of QRS window. The conversion logic is shown as Eqs (8) and (9):

    D(n)=M(n)+D(n1)(n1)n (8)
    W(i)={1,L(i)>max(0.3M(n)+0.1D(n),0.05A(n))0,L(i)max(0.3M(n)+0.1D(n),0.05A(n)) (9)

    where M(n) is the maximum value of the n-th 400 ms window, D(n) is the average of all past maximum value of windows and A(n) is the maximum value of the 2 s segment of the signal (five consecutive 400 ms windows). W(i) is set to "1" or "0" according to Eq (9). The window threshold D(n) is dynamically updated every 400 ms according to Eq (8) and A(n) is updated every 400 ms with the forward-moving 2 s segment. We also verified the performance of different window widths, such as 200,300,400 and 500 ms, in which the 400 ms window had the best result.

    The 400 ms window segmentation would cause some QRS complexes to be split, resulting in duplicate windows. Hence, W(i) was further processed to remove small windows resulting from window segmentation. Small-width windows, whose width were less than 1/4 of the average window width, were removed. And, the window with the smaller width was removed when there was another window within 0.4 s. Finally, the windows were symmetrically widened to 200 ms (72 samples for 360 Hz sample rate) about the center position. The windows whose width were greater than 200 ms remained unchanged. Figure 4 shows the first 4 s segment from record 209 as an example.

    Figure 4.  Processes of windowing stage. (a) S(i) signal; (b) L(i) signal; (c) Final W(i) signal.

    The QRS template is an N-sample time series T(n) extracted from Y(i). The CC is calculated by Eq (10):

    C(i)=jn=j(T(n)¯T)(Y(i+n)¯Y)jn=j(T(n)¯T)2jn=j(Y(i+n)¯Y)2 (10)

    where the parameter j=(N1)/2 is half the QRS window width. C(i) is the CC result of moving window correlation between QRS template T(n) and Y(i).

    The R-peak location (R(k) where k is the index of R-peaks number) is determined by finding the largest CC (Cp(k)). Figure 5 shows the first 4 s segment from record 209 as an example. R(k) and Cp(k) were further processed to reduce false detection of R-peaks. When the RRi is less than 0.4 times the average RRi, remove the corresponding R-peak with the smaller Cp value. The Cp(k) is used to select the R-peak because it shows the similarity of QRS complexes with the QRS template and may be used as an indicator for the reliability of R-peak detection. The final complete Cp(k) of record 209 was showed in Figure 6.

    Figure 5.  Examples of the results in the template matching stage. (a) Y(i) signal with window, red lines were window start positions, green lines were window end positions; (b) C(i) signal, the red dots indicated R-peaks (R(k): R-peak locations).
    Figure 6.  Peak values distribution of template matching of record 209.

    ECG signals are highly susceptible to external interference and noise, which often leads to distortions in the ECG waveform. This introduces significant challenges in detecting R-peaks accurately. Most QRS detection algorithms are structured around three essential steps: denoising, R-peak enhancement and R-peak detection [39]. The algorithm proposed in this paper aligns with this strategy as well. The initial preprocessing stage serves the purpose of noise reduction, followed by the application of windowing to enhance R-peaks. Ultimately, the template matching stage is used for R-peak detection. The 5–35 Hz band-pass filter effectively captures the spectrum energy of the QRS complex while preserving the essential morphology of QRS and simultaneously attenuating interference and noise. Employing the template matching technique stands out as a potent method for precisely identifying the exact positions of R-peaks.

    The performances of the proposed algorithm on the Arrhythmia database are shown in Appendix Table A1. TB represents the total number of R-peaks annotated in the record. DB represents the total number of detected R-peaks. TD is the group time delay between TB and DB with an integer number of samples. DB is 109491, only 3 less than TB of 109494. Average TD is only 0.17 ms (0.0625 sample). The maximum FP value was 139 and the maximum FN value is 43. In general, the number of false detections (FP = 242) was slightly less than the number of missed detections (FN = 245).

    The performances of the PT algorithm on the Arrhythmia database were shown in Appendix Table A2. The maximum FP value was 591 and the maximum FN value was 482, appearing in the same record, 108. In general, the number of false detections (FP = 934) was less than the number of missed detections (FN = 1233). The average TD of the PT algorithm was 30.49 ms (10.975 samples), much larger than that of the proposed algorithm, which was 0.17 ms on average.

    Performance comparison between the two algorithms was also evaluated with different tolerance for R-peak detection, as shown in Table 1, in which: 150 ms was the time of 54 sample periods, 25 ms was the time of 9 sample periods, 2.78 ms was the time of 1 sample period. The proposed algorithm outperformed the PT algorithm on all metrics.

    Table 1.  Performance comparison between the Pan-Tompkins algorithm and the proposed.
    Pan-Tompkins Algorithm Proposed Algorithm
    Tolerance Se(%) PPV(%) DER(%) ADE(ms) Se(%) PPV(%) DER(%) ADE(ms)
    150 ms 98.87 99.14 1.98 21.65 99.78 99.78 0.44 8.35
    25 ms 79.41 79.63 40.90 13.37 96.82 96.82 6.36 3.17
    2.78 ms 11.85 11.88 176.03 2.42 86.18 86.18 27.64 1.86
    Note: TB: total beats annotated; Se: sensitivity; PPV: positive prediction value; DER: detection error rate; ADE: annotated-detected error.

     | Show Table
    DownLoad: CSV

    The main purpose of this algorithm is to improve the detection accuracy of R-peak location, paying less attention to Se/PPV/DER metrics. Yet, the algorithm derives satisfying performance in the Se/PPV/DER metrics on the Arrhythmia database. Additionally, the proposed algorithm completely surpassed the comparison algorithm in the accuracy of R-peak location [32]. Refer to Table 2 for details.

    Table 2.  Comparison of R-peak detection performance.
    Method TB Se(%) PPV(%) DER(%) ADE(ms)
    Proposed 109,494 99.78 99.78 0.44 8.35
    Kai Zhao et al. [32] 109,966 99.81 99.88 0.31 12.2
    * Pan and Tompkins [33] 109,966 99.13 99.63 1.24 13.4
    * Indicates that the data is quoted from literature [32].

     | Show Table
    DownLoad: CSV

    The introduced algorithm showcased superior performance over the PT algorithm across all metrics including SE, PPV, DER and ADE when tested on the Arrhythmia database. Notably, the achieved ADE of 8.35 ms surpassed the 12.2 ms reported in a comparative study [32]. To optimize the integrity of QRS morphology, a 5–35 Hz BPF was employed in the proposed algorithm. Furthermore, the template matching method was proved an effective strategy to identify the precise location of R-peaks.

    The Arrhythmia database is widely used to evaluate the QRS detection algorithm, because it includes various arrhythmic QRS complexes, different types of noise and various QRS morphology with detailed annotation. However, the Arrhythmia database still has the problem of inaccurate R-peak annotation [40]. A large number of literatures with nearly perfect performance also have a problem with non-standardized R-peak numbers. There are various different values for the total number of R-peaks suggested for this database, such as 109,494 [10], 109,966 [27], 106,581 [41], 109,475 [42]. The Arrhythmia database have many categories of annotation: "*", "N", "L", "R", "a", "V", "F", "J", "A", "S", " "E", "j", "/", "Q", "e", "n", "f". This paper used 109,494 as the total R-peak number, and the categories excluded in the statistics were: "*", "n". The poor performance in ADE may result from not only the error of R-peak position detected, but also the error of R-peak position annotated. As shown in Figure 7, there are annotation errors in record 104, obviously, which results in detection error in both algorithms, although more in the PT algorithm.

    Figure 7.  R-peaks from 0–4 s of record 104. (a) 5 annotated R-peaks; (b) 4 detected R-peaks by PT algorithm; (c) 5 detected R-peaks by the proposed algorithm.

    We extracted record 122 and record 115 from the best ADE of the Arrhythmia database, and compared them with record 104 and record 208 from the worst ADE as shown in Table 3. Record 122 and record 115 only have normal beats. While the proportion of the number of "V" categories in TB (total number of R-peaks) is obviously larger in record 208 and record 104, which may be a reason for the poor ADE performance. "V" refers to the category of premature ventricular contract, "/" refers to the paced beat, 'f ' refers to fusion of paced and normal beat. Those kinds of QRS morphology differ from normal QRS morphology (and therefore the QRS template), which could result in degraded performance in template matching. These categories have different QRS templates which are not covered in the proposed method. But, the method still has the ability to detect R-peaks in a wrong position with a lower cross-correlation peak value, which induce detected R-peak shift from the real location and reduce the ADE performance.

    Table 3.  Comparison between the two of the best records and the two of the worst records on ADE.
    File ADE(ms) TB N V / Q F f S
    122 1.12 2476 2476
    115 1.19 1953 1953
    104 16.75 2229 163 2 1380 18 1 666
    208 24.96 2955 1586 992 2 373 2
    Note: normal beats; V: beats of premature ventricular contract; /: paced beats; f: fusion of paced and normal beats; Q: Unclassifiable beats; F: fusion of ventricular and normal beats; S: supraventricular premature beats.

     | Show Table
    DownLoad: CSV

    There is another reason for false R-peak detection in the PT algorithm. The narrow-band BPF would distort the QRS morphology, causing the wrong R-peak position to be detected. Examples are shown in Figure 8. Comparing Figure 8(a), (c), 5–15 Hz BPF could shift the R-peak location forward about 22 samples while R-peak location nearly has no shift with 5–35 Hz BPF. And, the MWI process is another possible reason for R-peak location shift. In Figure 8(b), the blue line is the real R-peak location in raw ECG data, while the red line is the final detected R-peak by the PT algorithm with a shift of 26 samples. In Figure 8(d), the blue line is the real R-peak location in raw ECG data, while the red line is the final detected R-peak by the PT algorithm with a shift of 11 samples. The MWI process will result in a time delay of Trs (R-wave peak to S-wave offset) for R-peak position [33], where Trs is related with the QRS morphology and varies with noise.

    Figure 8.  Filter bandwidth effect on QRS morphology: examples from sample 280 to sample 390 on record 114. The blue is raw ECG data, the red is filtered signal which has been amplified and level shifted for amplitude matching. (a) 5–15 Hz BPF effect; (b) 5–15 Hz BPF and its related output waveform after MWI; (c) 5–35 Hz effect; (d) 5–35 Hz BPF and its related output waveform after MWI.

    This paper presents an enhanced version of the PT algorithm, wherein the inclusion of the QRS template matching substantially enhances the accuracy of R-peak position detection. This advancement is particularly effective in refining the precision of R-peak localization. Moving forward, the potential exists to expand the algorithm's versatility by incorporating various templates for atypical QRS patterns, thereby bolstering its adaptability. The contribution of this study lies in the introduction of a highly precise R-peak position detection algorithm capable of accurately pinpointing R-peak locations. This advancement holds the promise of significantly amplifying the clinical applications of HRV analysis.

    The authors declare they have not used Artificial Intelligence (AI) tools in the creation of this article.

    The authors wish to acknowledge the funding support from Science and Technology Program of Guangzhou (No. 2019050001), Program for Chang Jiang Scholars and Innovative Research Teams in Universities (No. IRT_17R40), Guangdong Provincial Key Laboratory of Optical Information Materials and Technology (No. 2017B030301007), Guangzhou Key Laboratory of Electronic Paper Displays Materials and Devices (201705030007), MOE International Laboratory for Optical Information Technologies, the 111 Project.

    The authors declare there is no conflict of interest.

    Table A1.  Performance evaluation of the proposed algorithm for arrhythmia database.
    File TD(ms) TB DB TP FP FN Se(%) PPV(%) DER(%) ADE(ms)
    100 0.00 2273 2273 2273 0 0 100 100 0 2.21
    101 0.00 1865 1865 1862 3 3 99.84 99.84 0.00 2.53
    102 0.00 2187 2187 2187 0 0 100 100 0 10.80
    103 0.00 2084 2083 2083 0 1 99.95 100 0.00 2.32
    104 0.00 2229 2237 2228 9 1 99.96 99.60 0.00 16.75
    105 0.00 2572 2590 2557 33 15 99.42 98.73 0.02 9.54
    106 0.00 2027 2021 2020 1 7 99.65 99.95 0.00 5.30
    107 –2.78 2137 2136 2135 1 2 99.91 99.95 0.00 7.47
    108 2.78 1763 1758 1754 4 9 99.49 99.77 0.01 14.95
    109 –2.78 2532 2530 2530 0 2 99.92 100 0.00 5.08
    111 0.00 2124 2123 2123 0 1 99.95 100 0.00 5.78
    112 0.00 2539 2539 2539 0 0 100 100 0 2.14
    113 0.00 1795 1795 1795 0 0 100 100 0 1.93
    114 30.56 1879 1880 1876 4 3 99.84 99.79 0.00 8.02
    115 2.78 1953 1953 1953 0 0 100 100 0 1.12
    116 0.00 2412 2390 2387 3 25 98.96 99.87 0.01 2.91
    117 –19.44 1535 1535 1535 0 0 100 100 0 6.97
    118 0.00 2278 2278 2278 0 0 100 100 0 3.15
    119 0.00 1987 1988 1987 1 0 100 99.95 0.00 6.00
    121 –2.78 1863 1861 1861 0 2 99.89 100 0.00 2.26
    122 0.00 2476 2476 2476 0 0 100 100 0 1.19
    123 0.00 1518 1518 1518 0 0 100 100 0 1.82
    124 0.00 1619 1619 1619 0 0 100 100 0 6.99
    200 –5.56 2601 2601 2599 2 2 99.92 99.92 0.00 17.64
    201 0.00 1963 1942 1942 0 21 98.93 100 0.01 4.15
    202 0.00 2136 2122 2122 0 14 99.34 100 0.01 2.47
    203 –5.56 2980 2954 2937 17 43 98.56 99.42 0.02 15.28
    205 0.00 2656 2648 2648 0 8 99.70 100 0.00 5.27
    207 0.00 1860 1991 1852 139 8 99.57 93.02 0.08 12.98
    208 8.33 2955 2939 2936 3 19 99.36 99.90 0.01 24.96
    209 0.00 3005 3005 3005 0 0 100 100 0 1.54
    210 0.00 2650 2623 2621 2 29 98.91 99.92 0.01 7.34
    212 0.00 2748 2748 2748 0 0 100 100 0 2.24
    213 0.00 3251 3248 3248 0 3 99.91 100 0.00 5.78
    214 0.00 2262 2258 2258 0 4 99.82 100 0.00 4.60
    215 0.00 3363 3359 3359 0 4 99.88 100 0.00 3.18
    217 –13.89 2208 2205 2204 1 4 99.82 99.95 0.00 8.09
    219 0.00 2154 2154 2154 0 0 100 100 0 1.46
    220 2.78 2048 2048 2048 0 0 100 100 0 1.82
    221 0.00 2427 2425 2425 0 2 99.92 100 0.00 2.65
    222 0.00 2483 2485 2483 2 0 100 99.92 0.00 1.81
    223 0.00 2605 2603 2603 0 2 99.92 100 0.00 7.61
    228 0.00 2053 2062 2047 15 6 99.71 99.27 0.01 5.69
    230 2.78 2256 2256 2256 0 0 100 100 0 1.64
    231 0.00 1571 1570 1570 0 1 99.94 100 0.00 1.55
    232 0.00 1780 1782 1780 2 0 100 99.89 0.00 1.68
    233 –5.56 3079 3076 3076 0 3 99.90 100 0.00 16.33
    234 0.00 2753 2752 2752 0 1 99.96 100 0.00 0.86
    Total 109,494 109,491 109,249 242 245 99.78 99.78 0.44 8.35
    TB: total beats annotated; DB: detected beats by algorithm; TD: Group time delay between TB and DB; TP: true positive, the number of correctly detected R-peaks; FP: false positive, the number of false detected R-peaks; FN: false negative, the number of undetected R-peaks; Se: sensitivity; PPV: positive prediction value; DER: detection error rate; ADE: annotated-detected error.

     | Show Table
    DownLoad: CSV
    Table A2.  Performance evaluation of the PT algorithm for arrhythmia database.
    File TD(ms) TB DB TP FP FN Se(%) PPV(%) DER(%) ADE(ms)
    100 44.44 2273 2271 2271 0 2 99.91 100 0.00 25.01
    101 30.56 1865 1868 1863 5 2 99.89 99.73 0.00 13.98
    102 22.22 2187 2187 2187 0 0 100 100 0 18.24
    103 36.11 2084 2080 2079 1 5 99.76 99.95 0.00 16.79
    104 16.67 2229 2273 2221 52 8 99.64 97.71 0.03 21.90
    105 0.00 2572 2599 2561 38 11 99.57 98.54 0.02 18.40
    106 25.00 2027 1996 1995 1 32 98.42 99.95 0.02 23.96
    107 50.00 2137 2135 2135 0 2 99.91 100 0.00 26.49
    108 19.44 1763 1872 1281 591 482 72.66 68.43 0.61 43.72
    109 25.00 2532 2528 2527 1 5 99.80 99.96 0.00 24.43
    111 25.00 2124 2125 2123 2 1 99.95 99.91 0.00 21.21
    112 36.11 2539 2539 2539 0 0 100 100 0 32.70
    113 44.44 1795 1794 1793 1 2 99.89 99.94 0.00 24.20
    114 47.22 1879 1882 1876 6 3 99.84 99.68 0.00 15.68
    115 38.89 1953 1953 1952 1 1 99.95 99.95 0.00 10.89
    116 30.56 2412 2391 2387 4 25 98.96 99.83 0.01 16.35
    117 25.00 1535 1535 1533 2 2 99.87 99.87 0.00 22.72
    118 41.67 2278 2278 2274 4 4 99.82 99.82 0.00 25.16
    119 30.56 1987 1988 1986 2 1 99.95 99.90 0.00 25.33
    121 16.67 1863 1864 1858 6 5 99.73 99.68 0.01 23.31
    122 2.78 2476 2476 2475 1 1 99.96 99.96 0.00 15.93
    123 52.78 1518 1515 1513 2 5 99.67 99.87 0.00 18.09
    124 8.33 1619 1620 1619 1 0 100 99.94 0.00 21.26
    200 33.33 2601 2603 2596 7 5 99.81 99.73 0.00 22.39
    201 33.33 1963 1912 1912 0 51 97.40 100 0.03 18.87
    202 22.22 2136 2128 2127 1 9 99.58 99.95 0.00 15.54
    203 19.44 2980 2957 2924 33 57 98.09 98.88 0.03 22.66
    205 25.00 2656 2649 2648 1 8 99.70 99.96 0.00 14.22
    207 36.11 1860 1919 1826 93 34 98.17 95.15 0.07 24.20
    208 38.89 2955 2658 2654 4 301 89.81 99.85 0.10 28.16
    209 41.67 3005 3005 3003 2 2 99.93 99.93 0.00 20.36
    210 27.78 2650 2607 2603 4 47 98.23 99.85 0.02 15.29
    212 13.89 2748 2749 2748 1 0 100 99.96 0.00 18.92
    213 16.67 3251 3249 3249 0 2 99.94 100 0.00 26.62
    214 22.22 2262 2255 2253 2 9 99.60 99.91 0.00 14.22
    215 47.22 3363 3363 3362 1 1 99.97 99.97 0.00 19.16
    217 41.67 2208 2205 2202 3 6 99.73 99.86 0.00 25.10
    219 33.33 2154 2152 2150 2 4 99.81 99.91 0.00 17.94
    220 38.89 2048 2048 2046 2 2 99.90 99.90 0.00 17.17
    221 38.89 2427 2361 2360 1 67 97.24 99.96 0.03 21.64
    222 19.44 2483 2488 2483 5 0 100 99.80 0.00 15.72
    223 33.33 2605 2603 2602 1 3 99.88 99.96 0.00 29.88
    228 19.44 2053 2080 2045 35 8 99.61 98.32 0.02 20.37
    230 50.00 2256 2255 2255 0 1 99.96 100 0.00 15.21
    231 41.67 1571 1569 1568 1 3 99.81 99.94 0.00 29.59
    232 44.44 1780 1790 1776 14 4 99.78 99.22 0.01 25.12
    233 22.22 3079 3072 3072 0 7 99.77 100 0.00 19.89
    234 19.44 2753 2750 2750 0 3 99.89 100 0.00 11.04
    Total 109,494 109,196 108,262 934 1233 98.87 99.14 1.98 21.65

     | Show Table
    DownLoad: CSV


    [1] Austrian Automobile, Motorcycle and Touring Club (2018) Mineralölsteuer. Available from: https://www.oeamtc.at/thema/verkehr/mineraloelsteuer-17914742
    [2] Austrian Federal Environmental Agency (2019) Austria's Annual Greenhouse Gas Inventory 1990-2017. Report REP-0672. Vienna: Umweltbundesamt.
    [3] Baumol W (1972) On taxation and the Control of Externalities. Amer Econ Rev 62: 307-321.
    [4] Baumol W, Oates W (1971) The Use of Standards and Pricing for the Protection of the Environment. Swedish J Econ 73: 42-54. doi: 10.2307/3439132
    [5] Bointner R, Biermayr P, Goers S, et al. (2013) Wirtschaftskraft Erneuerbarer Energie in Österreich und Erneuerbare Energie in Zahlen. Blue Globe Report #1/2013. Vienna: Austrian Climate and Energy Fund.
    [6] Breuss F, Steininger K (1995) Reducing the Greenhouse Effect in Austria. A General Equilibrium Evaluation of CO2-Policy-Options. EI Working Papers, Vienna.
    [7] Brons M, Nijkamp P, Pels E, et al. (2008) A meta-analysis of the price elasticity of gasoline demand. A SUR approach. Energ Econ 30: 2105-2122. doi: 10.1016/j.eneco.2007.08.004
    [8] Druckman A, Jackson T (2009) The carbon footprint of UK households 1990-2004: a socio-economically disaggregated, quasi-multi-regional input-output model. Ecol Econ 68: 2066-2077. doi: 10.1016/j.ecolecon.2009.01.013
    [9] European Environment Agency (2018) Transport greenhouse gas emissions. Available from: https://www.eea.europa.eu/airs/2018/resource-efficiency-and-low-carbon-economy/transport-ghg-emissions
    [10] Federal Ministry of Austria for Sustainability and Tourism and Federal Ministry of Austria for Transport, Innovation and Technology (2018) #mission2030. Austrian Climate and Energy Strategy. Vienna: Federal Ministry of Austria for Sustainability and Tourism and Federal Ministry of Austria for Transport, Innovation and Technology.
    [11] Goers S, Baresch M, Tichler R, et al. (2015) MOVE2-Simulation model of the (Upper) Austrian economy with a special focus on energy including the socio-economic module MOVE2social-integration of income, age and gender. Linz: Energieinstitut at the Johannes Kepler University.
    [12] Goers S, Schneider F (2019) Austria's Path to a Climate-Friendly Society and Economy-Contributions of an Environmental Tax Reform. Modern Economy 10: 1369-1384. doi: 10.4236/me.2019.105092
    [13] Goulder L (1995) Environmental taxation and the double dividend: A reader's guide. Int Tax Public Finan 2: 157-183. doi: 10.1007/BF00877495
    [14] Goulder L, Parry I, Burtraw D (1997) Revenue-Raising versus Other Approaches to Environmental Protection: The Critical Significance of Preexisting Tax Distortions. Rand J Econ 28: 708-731. doi: 10.2307/2555783
    [15] Hymel KM, Small KA, Van Dender K (2010) Induced demand and rebound effects in road transport. Transport Res B 44: 1220-1241. doi: 10.1016/j.trb.2010.02.007
    [16] Kirchner M, Sommer M, Kratena K, et al. (2019) CO2 Taxes, Equity and the Double Dividend: Macroeconomic Model Simulations for Austria. Energ Policy 126: 295-314. doi: 10.1016/j.enpol.2018.11.030
    [17] Köppl A, Kettner C, Kletzan-Slamanig D, et al. (2014) Energy Transition in Austria: Designing Mitigation Wedges. Energy Environ 25: 281-304.
    [18] Moser S, Mayrhofer J, Schmidt R, et al. (2018) Socioeconomic cost-benefit-analysis of seasonal heat storages in district heating systems with industrial waste heat integration. Energy 160: 868-874. doi: 10.1016/j.energy.2018.07.057
    [19] Ottelin J, Heinonen J, Junnila S (2018) Carbon and material footprints of a welfare state: Why and how governments should enhance green investments. Environ Sci Policy 86: 1-10. doi: 10.1016/j.envsci.2018.04.011
    [20] Pearce D (1991) The Role of Carbon Taxes in Adjusting to Global Warming. Econ J 101: 938-948. doi: 10.2307/2233865
    [21] Shammin M, Bullard C (2009) Impact of cap-and-trade policies for reducing greenhouse gas emissions on US households. Ecol Econ 68: 2432-2438. doi: 10.1016/j.ecolecon.2009.03.024
    [22] Sims R, Schaeffer R, Creutzig F, et al. (2014) Transport, In: Edenhofer O, Pichs-Madruga R, Sokona Y, Climate Change 2014: Mitigation of Climate Change. Contribution of Working Group III to the Fifth Assessment Report of the Intergovernmental Panel on Climate Change, Cambridge, New York: Cambridge University Press.
    [23] Statistik Austria (2019a) Ökosteuern. Available from: http://statistik.gv.at/web_de/statistiken/energie_umwelt_innovation_mobilitaet/energie_und_umwelt/umwelt/oeko-steuern/index.html
    [24] Statistik Austria (2019b) Kraftfahrzeuge-Neuzulassungen. Available from: http://www.statistik.at/web_de/statistiken/energie_umwelt_innovation_mobilitaet/verkehr/strasse/kraftfahrzeuge_-_neuzulassungen/index.html
    [25] Steinmüller H, Tichler R, Kienberger T, et al. (2017) Smart Exergy Leoben: Exergetische Optimierung der Energieflüsse für eine smarte Industriestadt Leoben. Vienna: Austrian Climate and Energy Fund.
    [26] Tichler R (2009) Optimale Energiepreise und Auswirkungen von Energiepreisveränderungen auf die oberösterreichische Volkswirtschaft. Analyse unter Verwendung des neu entwickelten Simulationsmodells MOVE. Linz: Energiewissenschaftliche Studien.
    [27] Titelbach G, Leitner G, van Linthoudt J-M (2018) Verteilungswirkungen potentieller Verkehrsmaßnahmen in Österreich. Research Report. Vienna: Institute for Advanced Studies.
    [28] Yeo S (2019) Where climate cash is flowing and why it's not enough. Nature 573: 328-331. doi: 10.1038/d41586-019-02712-3
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