The allometric model in chronic myocardial infarction
© Bonomini et al.; licensee BioMed Central Ltd. 2012
Received: 15 February 2012
Accepted: 11 May 2012
Published: 11 May 2012
An allometric relationship between different electrocardiogram (ECG) parameters and infarcted ventricular mass was assessed in a myocardial infarction (MI) model in New Zealand rabbits.
A total of fifteen animals were used, out of which ten underwent left anterior descending coronary artery ligation to induce infarction (7–35% area). Myocardial infarction (MI) evolved and stabilized during a three month-period, after which, rabbits were sacrificed and the injured area was histologically confirmed. Right before sacrifice, ECGs were obtained to correlate several of its parameters to the infarcted mass. The latter was normalized after combining data from planimetry measurements and heart weight. The following ECG parameters were studied: RR and PR intervals, P-wave duration (PD), QRS duration (QRSD) and amplitude (QRSA), Q-wave (QA), R-wave (RA) and S-wave (SA) amplitudes, T-wave peak amplitude (TA), the interval from the peak to the end of the T-wave (TPE), ST-segment deviation (STA), QT interval (QT), corrected QT and JT intervals. Corrected QT was analyzed with different correction formulae, i.e., Bazett (QTB), Framingham (QTFRA), Fridericia (QTFRI), Hodge (QTHO) and Matsunaga (QTMA) and compared thereafter. The former variables and infarcted ventricular mass were then fitted to the allometric equation in terms of deviation from normality, in turn derived after ECGs in 5 healthy rabbits.
Six variables (JT, QTB, QA, SA, TA and STA) presented statistical differences among leads. QT showed the best allometric fit (r = 0.78), followed by TA (r = 0.77), STA (r = 0.75), QTFRA (r = 0.72), TPE (r = 0.69), QTFRI (r = 0.68) and QTMA (r = 0.68). Corrected QT’s (QTFRA, QTFRI and QTMA) performed worse than the uncorrected counterpart (QT), the former scaling allometrically with similar goodness of fits.
QT, TA, STA and TPE could possibly be used to assess infarction extent in an old MI event through the allometric model as a first approach. Moreover, the TPE also produced a good allometric scaling, leading to the potential existence of promising allometric indexes to diagnose malignant arrhythmias.
In a previous paper , we briefly gave the basic idea to apply the allometric concept in electrocardiography, that is, and quoting almost verbatim: «Scaling of many biological processes can be described by the allometric equation Y = a*(Bmass)b, where Y is the biological process, Bmass the body mass and “a” and “b” are scaling constants. In general, the weights of most individual organs scale as a constant fraction of body mass (i.e., the body mass exponent, “b” equals 1.0). Volume rates, instead (the product of volume and rate), such as cardiac output, ventilation and oxygen uptake, vary with “b” around 0.75. Finally, rates (heart and respiratory rate) scale as “b” close to 0.25. These emergent patterns provide insights into body-size dependent principles that seem to dictate several aspects of design and function across species among all mammals [2, 3] » .
Noujaim et al. assumed that the heart behaves as a set of “fractal-like” networks tending to minimize propagation time across the conducting system while ensuring a hemodynamically optimal atrioventricular activation sequence. With the mathematical relationship given above and, subsequently, based on previously published values of PR interval, heart rate, and body masses of 541 mammals, they reported as best fit the equation PR = 53 × (Bmass)0.24.
Inspired in the latter report, the following question seems pertinent:
Would a relationship similar to the allometric equation be conceivable, say, between the number of cardiac diseased fibers and any of several ECG parameters when a myocardial infarct (MI) affected the heart?
The objective of this paper tries to find an answer to such question. The Q-wave growth appears as a good candidate because well-known is the fact that normal depolarization suffers with compromised myocardial mass, augmenting the Q-wave and shrinking the R-wave within the QRS complex. Also, additional MI changes include alterations in the T-wave morphology and QRS complex voltages and duration, as well as distortion in intervals such as JT and QT. Many reports confirm this concept, such as Klootwijk, in 1998 , Kléber, in 2000 , or Balian et al., in 2006 , among others. All of these variables and their behaviour on a MI model deserve to be looked at under the allometric light, which seems to maintain interest, especially in general mammalian biology [3, 8].
Experimental protocol and procedure to myocardial infarction
An overall of fifteen animals were used in this study. Ten New Zealand rabbits (7 male and 3 female, 1.5–2.5 kg) underwent left anterior descendent (LAD) coronary artery ligation to provoke infarction on a varying extent of myocardial tissue. MI evolved and stabilized during a three month-period after which, rabbits were sacrificed and MI histologically confirmed.
Ventricular infarcted mass in grams was calculated after combining data from planimetric measurements and heart weights. The infarcted mass was then normalized to heart weight in order to compare among different rabbit sizes. Normalized ventricular infarcted mass (VIMn) and the ECG parameters mentioned above were, thereafter, fitted to the allometric equation.
This study conformed to the Guide for the Care and Use of Laboratory Animals published by the US National Institutes of Health (NIH Publication No. 85–23, revised 1996).
After anaesthesia with ketamine (75 mg/kg) and Rompun (0,75 mg/kg xylazine) was administered subcutaneously, an endotracheal tube (3 mm inner diameter) was placed to mechanically ventilate the rabbits with room air using a Harvard respirator (25 ml, 34–38 cycles/min). Immediately after, 5% dextrose solution (3 ml/min) was infused through a flexible catheter placed at the marginal vein of one of the ears. Using this venous access throughout the surgical procedure, anaesthesia was maintained by applying additional doses of ketamine and sodium thyopental as needed during the surgical procedure. A left thoracotomy on the fourth intercostal space and a pericardiectomy were performed to expose the heart. Thereafter, a lateral or posterolateral coronary artery branch of the LAD coronary artery was ligated using a curved needle and 6.0 silk thread . The appearance of regional paleness confirmed ventricular wall ischemia. Finally, the thorax was closed with linen thread keeping the order of the different anatomical parts. At the end of the surgical procedure, the animals were placed in a quiet environment for their recovery. Antiobiotic therapy was administered and animals were closely observed during the first 24 hours. Afterwards, animals were placed in individual cages up to the finalization of a three month period.
For the control group, 5 healthy rabbits underwent the above mentioned anaesthetic protocol and ECG recordings were obtained. Analogously to the MI group, the three standard limb leads were recorded.
Histology and planimetry
To assess infarct size, Masson’s Trichrome (MT) staining was carried out, while infarction was corroborated by Hematoxiline-Eosine (HE). Once excised, hearts were perfused with 10% formaldehyde during 5 min for fixation, remaining in that solution for at least 72 hs. Four millimeter slices were cut out from apex to base and then processed for paraffin embedding and staining. After the latter, fibrotic tissue turned blue, so differentiating itself from healthy tissue, while HE allowed morphological recognition of necrotic tissue.
where PIM: planimetric infarcted area (% of the total ventricular area); VM: ventricular mass and HW: heart weight.
ECG acquisition and preprocessing
Rabbits were heparinized (500 U/Kg IV) 10 minutes before anesthesia by intramuscular injection of ketamine (35 mg/Kg) and lidocaine (5 mg/Kg). All animals were in sinus rhythm at the time of ECG recordings (frontal leads I, II, and III).
ECG data were recorded using instrumentation amplifiers with a gain factor of 1000 and a bandwidth of 0.05–150 Hz. The signals were digitalized at a sampling rate Fs = 500 Hz and 12-bit resolution using a digital acquisition board (Lab PC+, National Instruments, Austin, TX, USA). When necessary, a band-stop filter was used to remove 50-Hz. All of the data were acquired and monitored using customized software made in C++.
QRS detection was based on methods described by Hamilton and Tompkins in 1986 . All the ectopic or aberrant beats were automatically rejected by the computer. If needed, baseline corrections were performed by cubic spline interpolation .
We computed the running signal average of 30 beats. The template for signal averaging in each ECG channel were created, thereafter, by aligning 30 beats with 98% cross-correlated QRS waveforms using the predefined window and the R-wave peak as the trigger point while, at the same time, correcting for fiducial point jitter. Two rejected beats were the accepted limit on the computation of each final template beat.
ECG delineation was accomplished on the template obtained as explained in section “ECG acquisition and preprocessing”. The start and end of the QRS complex were determined by searches on each side of the R-wave for regions where the slope (dV/dt) fell to sufficiently low values. Isoelectric level was taken as the median of all data values preceding the start of the QRS. For the P-wave, we used a modified version of the algorithm described by , which is based on finding the peaks and valleys of a 9-point derivative signal. In case of the T-wave delineation, a search was made for the first significant peak of either sign, starting from a point after the end of the QRS. If a suitable peak was found, a straight line was adjusted by least squares from the peak to the tail of the T-wave. The intersection of this line with the isoelectric line was accepted as the T-wave end. ST-segment deviation was defined as the ECG amplitude 50 ms after QRS onset .
where HR = heart rate in bpm, RR = RR interval in s, QT = QT duration in s, QTC = corrected QT interval in s.
Allometric model – Mathematical setting
where δ = logα + β*logγ, VIMn: log(normalized ventricular infarcted mass) and ECG D and ECG N are the diseased and healthy counterparts of the following ECG parameters; STA: log(|ST deviation|) in mV; QA: log(|Q-wave amplitude|) in mV; SA: log(|S-wave amplitude|) in mV; RA: log(|R-wave amplitude|) in mV; QRSA: log(|Q| + |R| + |S|) in mV; TA: log(T-wave peak amplitude) in mV, TPE: log(T-wave time from peak to end); QRSD: log(QRS width);.QT: log(QT interval); QTc: log(QT interval corrected by different formulae); RR: log(RR interval); PR: log(PR interval); PD: log(P duration). Linear regressions were carried out to obtain numerical values for the intercept δ and the slope β in the log-log plot.
Data are expressed as mean ± standard deviation (Mean ± SD). To assess statistical significance, leads I, II and III were compared among them. When data did not pass the D’Agostino & Pearson normality test, a non-parametric Kruskall-Wallis test was applied and the Dunn’s post test carried out. Otherwise, one-way ANOVA and Bonferroni post-test were calculated.
Electrocardiographic time-related parameters (Mean ± SD) from a 3 month-MI rabbit evolution
365 ± 92
71 ± 8
29 ± 7
45 ± 6
120 ± 21
59 ± 23
397 ± 99
76 ± 8
32 ± 6
45 ± 4
161 ± 35*
74 ± 25
394 ± 108
72 ± 9
24 ± 6
41 ± 4
127 ± 26
59 ± 24
Electrocardiographic amplitude-related parameters (Mean ± SD) from a 3 month-MI rabbit evolution
−0.50 ± 0.33*
0.21 ± 0.23
−0.12 ± 0.36*
0.83 ± 0.92
0.08 ± 0.04*
0.10 ± 0.12*
−0.29 ± 0.23
0.22 ± 0.16
0.01 ± 0.05
0.52 ± 0.44
0.01 ± 0.05
−0.03 ± 0.09
−0.12 ± 0.15
0.37 ± 0.24
−0.02 ± 0.03
0.51 ± 0.42
−0.02 ± 0.03
−0.05 ± 0.07
Corrected and uncorrected QT intervals (Mean ± SD) from a 3 month-MI rabbit evolution
182 ± 24
296 ± 25
272 ± 16
242 ± 23
359 ± 50
189 ± 20
187 ± 35
293 ± 42
265 ± 19
235 ± 28
350 ± 54
184 ± 25
169 ± 29
272 ± 28*2
262 ± 20
231 ± 25
347 ± 57
182 ± 25
The remaining variables, RR, PR, PD, QRSD, JT, QTHO, QTB, QRSA and QA, RA and SA did not present a fit with a good statistical significance (p > 0.05). Moreover, they kept almost constant for all MI extents (data not shown).
Linear regressions of all ECG parameters for a 3 month-MI rabbit evolution grouped by leads
β (Mean ± SD)
δ (Mean ± SD)
3.464 ± 1.072
3.494 ± 0.8387
−2.474 ± 0.7736
−3.593 ± 0.5926
1.832 ± 0.5997
0.06115 ± 0.4994
0.1042 ± 0.03840
2.462 ± 0.03198
2.303 ± 0.9132
3.087 ± 0.7142
0.1691 ± 0.06926
2.456 ± 0.05769
0.1918 ± 0.07858
2.346 ± 0.06545
0.1384 ± 0.0617
2.531 ± 0.05142
−0.6352 ± 0.2849
−0.8878 ± 0.2228
1.202 ± 0.6668
0.03635 ± 0.5215
1.011 ± 0.5893
1.510 ± 0.4514
1.210 ± 0.7190
0.2376 ± 0.5988
0.5699 ± 0.3995
1.566 ± 0.3124
0.5025 ± 0.3669
2.675 ± 0.3056
−0.7553 ± 0.7338
0.3425 ± 0.5621
0.7621 ± 0.7972
0.09869 ± 0.6639
0.5296 ± 0.6854
1.821 ± 0.5360
0.1448 ± 0.3730
2.350 ± 0.2917
Findings of the present study
An allometric study was presented here in order to analyze the allometric scaling of different ECG parameters with respect to the infarction extent in a chronic experimental MI rabbit model. The idea behind this work was to find ECG data to estimate myocardial injured area as a first, simple and inexpensive step before resorting to more complex or invasive technologies, such as magnetic resonance imaging or radioscopic procedures. The chief findings of this study were as follows:
1- Six variables (JT, QTB, QA, SA, TA and STA) showed statistical differences among leads. Lead I versus Lead III contained 5 out of 6 of these statistical differences (QTB, QA, SA, TA and STA), while JT presented differences in Lead II with respect to Lead I. Most of these variables turned out to be amplitude-related (QA, SA, TA and STA) and, probably, the lead with the most evident changes was related to infarct localization.
2- Seven out of eighteen parameters presented a significant allometric fit (p < 0.05). Lead I accounted for the majority of them (STA, QTFRA, QTFRI, QTMA), followed by Lead III (QT, TPE) and Lead II (TA). See Table 4, where it can also be seen that QTB and QA showed borderline significances and still with a good fit.
3- The variables that best adjusted to the allometric equation were QT, TA and STA with a goodness of fit enough to assess infarction size within a sensitive range (r = 0.78, r = 0.77, r = 0.75, respectively.
Significance and interpretation of the data
Ventricular changes found during the chronic MI state can be split into ventricular depolarization and repolarization changes.
Ventricular Depolarization Changes
In chronic MI hearts, QRS morphologies changed [21, 22]. Even though not statistical significant, a negative Q-voltage slope and a positive S-voltage slope in the allometric equation suggest a shift from the QR to the RS morphology.
Surprisingly, QRSD did not fit well the allometric equation, as it would have been expected. We cannot find a good explanation for such behaviour. Evidence refers to the prognostic importance of QRS duration in acute and chronic myocardial infarction [23, 24]; hence, further investigation would be needed.
Ventricular Repolarization Changes
The T-wave showed a change in morphology, too, becoming flat instead of rounded. Moreover, negative T-wave morphologies appeared, mostly in lead II and III. These changes forced the JT interval to be longer and TPE to be longer as well as a smaller TA. On the other hand, QT interval and TPE presented a good allometric scaling. It is tempting to link this observation with the fact that increased arrhythmogenesis is related to MI hearts, as reported elsewhere [25–32].
The JT-interval could be considered as a total ventricular repolarization process. In our study, such interval was increased in MI, which might indicate a differential lengthening or shortening of the action potential duration (APD) in some myocardial areas, so reflecting the range of times at which action potentials end and, therefore, it would be an expression of APD heterogeneity . However, JT showed a bad allometric scaling and, at least based on this study, we could not establish the allometric behaviour of this parameter.
Uncorrected QT offered the best fit, in agreement with the literature on QT and ischaemia. With transmural ischaemia, the T-wave axis shifts in the opposite direction towards the region of epicardial involvement, being often a sign of infarction. Such T-waves are tall and peaked, frequently with long QT intervals . These changes may assist in the localization of ischaemia and also in the quantification of the injury size. It is worth noting that the slope of all corrected QT where about 0.25, similar to those found in the literature related to allometry; the uncorrected QT was the only one out of this pattern (β = 3.464 ± 1.072) [2, 4].
Surprisingly, STA deviation in Lead I displayed a good linear regression with VIMn in a log-log representation. This fact was opposite to our expectations since in humans, ST deviation tends to normalize in chronic MI. Nevertheless, ST-segment in rodents (especially in rats, and less markedly in rabbits) shows a different behaviour in the physiological case . Thus it is plausible to think that these differences will still hold for the pathological cases.
In addition, someone may think that a multilead approach would be a good methodology to measure the parameters. However, in our case, the number of leads was only three and we think that is not enough number to guarantee that kind of analysis. On top of that, we did not have a criterion to select one or the other lead.
from which numerical results are not shown in this report (see also above, Findings of the present study, item 3).
Study implications and future work
The first half of the T-wave is mainly related to epicardial APD, whereas the second half is to the endocardial and mid-myocardial APD [36, 37]. As a result, at the peak of the T-wave the transmural voltage gradient reaches the maximum and, therefore, the descending limb represents the extent of transmural dispersion of ventricular repolarization. Therefore, great is the importance of TPE producing a good allometric scaling, leading to a new and attractive future work, which is the search of allometric indexes for diagnosing malignant arrhythmias.
QT, TA and STA showed the strongest allometric behavior. This implies that chronic MI extents could be roughly assessed by feeding the allometric equation with any of these parameters. Whether one outstands from the others or not and hence, whether the allometric equation should be fed with any of these parameters individually or collectively with any combination of them, remains open.
Another consideration is pertinent regarding MI localization. Data presented in this work is valid for anteroseptal injury only. Thus, the search of electrocardiographic allometric scaling on different MI localizations would complete this study.
In the analysis of several electrocardiographic parameters, most of the ECG time-related and amplitude-related measurements have been taken into account. Nevertheless, other approaches for QT correction should be explored, like the individual correction suggested by Malik  or the correction for animals carried out by Valentinuzzi . On the other hand, the relations found here are strictly related to infarcts originated from LAD coronary artery ligation, not covering other MI localizations. Besides, a wider range of infarction extent would be desirable, allometrically speaking, but not possible due to the extremely low survival rates at MI extents greater than 40%.
The objectives of this paper were met, since ECG parameters related to depolarization and repolarization phases showed a certain degree of adjustment to the allometric equation, some of them rather good. The parameters that best allometrically scaled were QT, TA and STA, with a goodness of fit enough to assess infarction size within an acceptable range. Besides, the TPE produced a good allometric scaling, leading to the potential existence of promising indexes to diagnose malignant arrhythmias.
Partially supported by PIP #538, from CONICET (Consejo Nacional de Investigaciones Científicas y Técnicas). All three authors are CONICET Career Investigators.
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