Forced oscillation technique for early detection of the effects of smoking and COPD: contribution of fractional-order modeling

Introduction

COPD is currently the fourth and will soon become the third most frequent cause of death.¹ This disease is responsible for 6% of all deaths worldwide.¹ The spirometry test is typically used to evaluate respiratory obstruction in COPD.^2,3 Although considered the gold standard test, spirometry has the disadvantage of requiring great effort and great cooperation from patients, which can result in variation in the quality of test results, and performing the test on some patients can be difficult.^4–6

There is a consensus in literature about the great importance of early COPD diagnosis, enabling the establishment of measures that may alter the course of the disease, including pharmacological and non-pharmacological interventions and smoking cessation.^7–11 Assessment of respiratory obstruction in the early stages is critically dependent on the sensitivity of pulmonary function tests.¹² It has previously been observed that spirometric indices are not sensitive to small changes due to smoking.¹³

The forced oscillation technique (FOT) is a non-invasive method that aims to evaluate the respiratory system resistance and reactance during spontaneous ventilation.⁶ The method is based on the application of sinusoidal pressure variations in the opening of the airway through a mouthpiece during spontaneous ventilation.² Thus, the FOT only requires passive cooperation; forced expiratory maneuvers are not necessary. This method has reached a high level of sophistication currently representing the state-of-the-art in terms of the evaluation of pulmonary function.¹⁴ FOT was successfully applied in our laboratory and in several other research groups to diagnose early respiratory changes in respiratory mechanics.^13,15–26

Fractional-order (FrOr) models were recently proposed, allowing a more detailed and accurate description of the dynamic behavior of living systems. In the particular case of the respiratory system, these models provide new insight into the mechanisms associated with peripheral changes in the diseased lung.²⁷ Recently, new FrOr models were introduced and have been found to be particularly useful for the analysis of patients with COPD.^28–32 These models provide sensitive information about resistive properties and hysteresivity, which reflects changes in heterogeneity and lung structure, as well as parenchymal deformity and elastance.²⁷ However, these models were not evaluated for the early detection of the effects of smoking and COPD.

In this context, the main objectives of this study were 1) to evaluate the potential of the FOT combined with FrOr models in the early diagnosis of the adverse effects of smoking and COPD; and 2) to determine the best parameters for the previously mentioned diagnoses.

Patients and methods

Study design

The FOT and spirometry assessments were performed at the Biomedical Instrumentation Laboratory of the State University of Rio de Janeiro (LIB/UERJ) and at the Pedro Ernesto University Hospital (Hospital Universitário Pedro Ernesto – HUPE) and were approved by the Research Ethics Committee of HUPE. Prior to the tests, the individuals signed a free and informed consent form. Forty healthy volunteers with no history of smoking or pulmonary disease (the control group), 40 smoking volunteers and 40 volunteers with mild COPD were studied.

Patients with COPD were stable and classified according to the GOLD criteria as having mild airway obstruction.¹ The eligibility criteria for COPD included a history of smoking >10 packs of cigarettes per year, an FEV₁/ FVC ratio <0.7, no respiratory infections in the previous 3 weeks and an absence of other respiratory diseases or other thoracic comorbidities, including cardiovascular disease, malignant disease and chest deformities. Before the study, all patients were taking their usual medication as recommended by the GOLD, but medication that could interfere with the assessment of the BD response was suspended, as established by the American Thoracic Society/European Respiratory Society (ATS/ERS).^1,33

The control group was composed of healthy individuals without any previous history of pulmonary or cardiac disease or smoking. Using a closed-circuit spirometer (Vitrace VT-139; Pro-médico, Rio de Janeiro, Brazil), the following measurements were obtained for all subjects while they were in a sitting position: forced expiratory volume in the first second (FEV₁), FVC, forced expiratory flow (FEF) between 25% and 75% of the FVC, the FEF/FVC ratio and the FEV₁/FVC ratio. The best of the three repeatable maneuvers was recorded.

Interpretation of respiratory impedance measurements

The interested reader may find details of the FOT instrumentation in the supplement. Traditional FOT parameters were initially used to interpret the results. The resistive component was evaluated using linear regression in the frequency range between 4 and 16 Hz, which allowed us to obtain the intercept resistance (R0) and the slope of the resistive impedance values (S). In the frequency range of the present study (4–32 Hz), resistances are related to the airway and tissue Newtonian resistance in addition to the delayed airway resistance resulting from gas redistribution. Therefore, R0 estimates how the cited properties work at low frequencies.³⁴ S reflects the frequency-dependent alteration in the distribution of gas flow within the system, ie, both spatial and temporal inhomogeneities.^34,35 The resistance of the respiratory system at 4 Hz (R4) and the average resistance between 4 and 16 Hz (Rm), which is associated with airway caliber, were also examined.³⁶

The mean reactance (Xm) and the resonance frequency (fr) were used to interpret the results related to the reactive properties. These parameters reflect changes in airway heterogeneity, as well as tissue changes associated with the presence of fibrosis, for example.^34,37 The area of Xrs(f) from 4 Hz to fr, designated as the reactance area (AX), is related to respiratory compliance and is believed to be sensitive to the degree of peripheral airway obstruction.³⁸ The respiratory system dynamic compliance (Cdyn) was obtained using the respiratory reactance at 4 Hz (Cdyn=−1/(2πfX4 Hz)).³⁹ The same frequency was used to estimate the respiratory impedance module (Z4), which is related to the work done by respiratory muscles to overcome the resistive and elastic properties of the respiratory system in order to generate airflow.^36,40

Respiratory modeling

The extended RIC model (eRIC, Figure 1) was suggested as a model that has been improved when compared to the basic RIC model. In these models, R is the variable representing central airway resistance, Rp describes the peripheral resistance and I and C are associated with pulmonary inertance and compliance, respectively. The eRIC model can also be used to evaluate the total resistance (Rt=R+Rp).

Figure 1 Two-compartment integer-order model used to analyze respiratory impedance. Notes: The resistance (R), inductance (I) and capacitance (C) are the analogs of respiratory resistance, inertance and compliance, respectively. Rp represents the peripheral resistance.

A two-compartment integer-order model (InOr) was used to analyze respiratory impedance. The resistance (R), inductance (I) and capacitance (C) are the variables representing respiratory resistance, inertance and compliance, respectively. Rp represents the peripheral resistance.

The FrOr proposed for evaluation in this study (Equation 1, Figure 2) is physiologically interpreted as a frequency-dependent fractional inertia (FrL) which takes into account the capacity of the fractional terms to approximate the resistive properties being 0≤α≤1, and a component relative to more peripheral airways described as a constant-phase impedance, where 0≤β≤1, and frequency-dependent fractional compliance (FrC) is a fractional compliance.³⁰

(1)

Figure 2 Two-compartment fractional-order model evaluated in this study. Notes: The model includes a constant phase inertance (CPL) and a constant phase compliance (CPC) composed of a frequency-dependent fractional inertia (FrL) and a frequency-dependent fractional compliance (FrC). A simplified description of the ability of the fractional terms to represent the resistive and reactive respiratory properties, depending on the α and β values is also described. R is associated with the influence of the respective fractional-order term on the resistance values; L describes the influence of the FrL in the reactance, producing a more positive reactance in higher frequencies, while C describes the influence of the FrC in reactance, producing more negative reactance values in low frequency.

These results were interpreted physiologically using the damping (G), elastance (H) and hysteresivity coefficient (η) values, as described by the following equations:

(2)

(3)

(4)

Hysteresivity describes the heterogeneity of the lung, with greater values often associated with more heterogeneity. Damping is associated with energy dissipation in the respiratory system, while H reflects the potential elastic energy storage (elastance).³⁰ Curves fitting of the IrOr and FrOr models was performed using the ModeLIB program, which was also developed in our laboratory. This program employs the Levenberg-Marquardt algorithm to determine the set of parameters of the model that best represent the input dataset in terms of least squares. Together with the model estimates, this analysis also provides the calculated total error value (MSEt), an overall measure of the “goodness of fit” of the model. The square root of the sum of the real (MSEr) and imaginary (MSEx) impedance estimation errors is used for this purpose.

Statistical analysis

The results are presented as the means ± SDs. The Shapiro–Wilk normality test was performed first. One-way ANOVA corrected by Tukey’s test was used when the data exhibited a normal distribution. When the data were not normally distributed, a non-parametric test (Kruskal–Wallis) combined with the Mann–Whitney U test was used. The results were considered significant at P<0.05.

To calculate the sample size, we used preliminary results obtained from 31 controls, 26 smokers and 22 patients with mild COPD.⁴¹ The criterion was the comparison of areas under the curve (AUCs), with the aim of showing that an AUC of 0.8 (adequate diagnostic accuracy) was significantly different from the null hypothesis value of 0.5 (meaning no discriminating power). A type I error of 0.01 and a type II error of 0.01 were considered, which resulted in a minimum of 36 volunteers per group. This analysis was performed using MedCalc 13 (MedCalc Software, Mariakerke, Belgium).

The study follows the STARD requirements for reporting studies of diagnostic accuracy.⁴² The values of sensitivity and specificity were obtained based on the optimal cut-off point, as determined from the Receiver Operating Characteristic (ROC) curve analysis.⁴³ ROC curves with AUCs ≥0.80 were considered adequate for diagnostic use, while AUCs between 0.90 and 1.00 were considered indicative of a high diagnostic accuracy.^43,44 Comparisons of the AUC among the best parameters obtained from traditional FOT analysis and from eRIC and FrOr modeling were done using MedCalc 13, according to the theory described by Hanley and McNeil.⁴⁵

The associations among the FOT and spirometric parameters were evaluated using Spearman’s correlation coefficients. These analyses were performed using GraphPad Prism 7, and the interpretation of these results was based on the classification proposed by Dawson et al:⁴⁶

• Small or no correlation: between 0 and 0.25 (or −0.25);
• Reasonable correlation: between 0.25 and 0.50 (or −0.25 to −0.50);
• Moderate to good correlation: between 0.50 and 0.75 (or −0.50 to −0.75);
• Very good to excellent correlation: greater than 0.75 (or −0.75).

Results

The anthropometric and spirometric characteristics of the studied groups are described in Table 1.

Table 1 Anthropometric, spirometric and traditional FOT measurements of the groups studied Notes: aP<0.05. bP<0.01. cP<0.001, ****P<0.0001, compared with the control group. Abbreviations: FEV1/FVC, Tiffeneau index; FOT, forced oscillation technique; n, number of evaluated patients; ns, not significant.

Respiratory modeling

Figure 3 shows typical respiratory impedance measurements and the associated model adjustments that were obtained in normal subjects with constant (A) and slightly increasing resistance values (B), the smokers (C) and the mild COPD patients (D).

Figure 3 Typical results obtained during the eRIC (red) and FrOr (blue) models adjustment in the resistance (closed circles) and reactance (open circles) of normal subjects (A) normal subjects with increasing resistance (B), smokers (C) and mild COPD patients (D).

Figure 4 describes the results obtained using the eRIC model in the studied groups. The Rt values increased significantly in the smokers and mild COPD patients, while C was reduced in the mentioned groups.

Figure 4 Changes in the eRIC model parameters in the studied groups. Notes: Central airway resistance (R; A), peripheral resistance (Rp; B), total resistance (Rt; C), pulmonary inertance (I; D), and alveolar compliance (C; E). *P<0.05; **P<0.01; ****P<0.0001; in relation to control. Abbreviations: COPD I, mild COPD; ns, not significant.

On examining the parameters obtained with the FrOr model, significant increases in FrL, damping factor and hysteresivity were observed. The changes in α and FrC were not significant, while β and elastance showed significant decreases (Figure 5).

Figure 5 Changes in the fractional order model parameters in the studied groups. Notes: Fractional inertance (FrL; A), Fractional inertance exponent (alpha; B), Fractional compliance (FrC; C), fractional compliance exponent (beta; D), Damping factor (G; E), Elastance (H; F). ***P<0.001; **P<0.01; ****P<0.0001; in relation to control. Abbreviations: COPD I, mild COPD; ns, not significant.

Table 2 presents the error values observed in the adjustments in the real and imaginary parts of the impedance, as well as the mean relative distances for the studied models.

Table 2 Errors in the integer and FrOr models used for control individuals, smokers and patients with mild COPD Note: The smallest errors in the comparisons of the evaluated models are indicated in bold. Abbreviations: eRIC, extended resistance-inertance-compliance model; FrOr, fractional-order model.

Correlation of traditional FOT, eRIC and FrOr model parameters with spirometry

These analyses are described in Tables 3–5, respectively. In general, the degree of the associations among traditional FOT and spirometric parameters were reasonable to good. Considering the traditional parameters, the strongest correlations were presented by Xm, showing good and direct (positive) correlations with FEV₁ (L) and FVC (L).

Table 3 Correlation analysis among traditional forced oscillation parameters and spirometric results Note: The two strongest correlations for each FOT parameter are indicated in bold. Abbreviations: FEF, Forced expiratory flow; FEV1/FVC, Tiffeneau index.

Table 4 Correlation analysis among eRIC model parameters and spirometric results Note: The two strongest correlations for each eRIC parameter are indicated in bold. Abbreviations: eRIC, extended resistance-inertance-compliance model; FEF, Forced expiratory flow; FEV1/FVC, Tiffeneau index; ns, not significant.

Table 5 Correlation analysis among FrOr model parameters and spirometric results Note: The two strongest correlations for each FrOr parameter are indicated in bold. Abbreviations: FEF, forced expiratory flow; FEV1/FVC, Tiffeneau index; FRC, frequency-dependent fractional compliance; FrOr, fractional-order model; FrL, frequency-dependent fractional inertia; ns, not significant.

Smaller correlations were observed among the eRIC model and spirometric parameters (Table 4). R was not correlated with the spirometric parameters. The strongest correlations were found between Rp and FEV₁ (%) and between C and FEV₁ (L).

For the FrOr parameters, it was observed that FrC and H were almost not correlated with the spirometric parameters (Table 5). The strongest correlations were presented by β and η, which showed good direct and inverse correlations, respectively, with FEF25–75 (%).

Diagnostic accuracy of traditional FOT, eRIC and FrOr parameters

ROC analysis of the studied groups revealed that Rm was the best traditional forced oscillation parameter in smokers [Table 6; AUC=0.821 (95% CI: 0.719–0.897), Se=77.5 (61.5–89.2), Sp=75.0 (61.5–89.2)]. Similarly, Rt was the more discriminative parameter when the eRIC model was used [AUC=0.830 (0.750–0.905), Se=80.0 (64.4–90.9), Sp=75.0 (61.5–89.2)]. For the use of the FrOr model, Table 6 shows that β and η were the more accurate parameters for smokers [AUC=0.903 (0.816–0.958), Se=82.5 (67.2–92.7), Sp=85.0 (70.2–94.3)]. Traditional FOT and eRIC modeling achieved appropriate values for clinical use (AUC >0.80), while the FrOr modeling AUC value was considered of high diagnostic accuracy (AUC >0.90).^43,44

Table 6 Diagnostic accuracy, sensitivity, specificity and cut-off point for the traditional, eRIC and FrOr parameters in detecting respiratory alterations in smokers Note: Bold values indicate the highest accuracy for each class of FOT. Abbreviations: AUCs, areas under the curve; FRC, frequency-dependent fractional compliance; FrL, frequency-dependent fractional inertia; FrOr, fractional-order model.

A similar analysis performed in patients with mild COPD revealed that Cdyn was the best traditional forced oscillation parameter [Table 7; AUC=0.763 (0.654–0.851), Se=67.5 (50.9–81.4), Sp=65.0 (48.3–79.4)].

Table 7 Diagnostic accuracy, sensitivity, specificity and cut-off point for the traditional, eRIC and FrOr parameters in detecting respiratory alterations in patients with mild COPD Note: Bold values indicate the highest accuracy for each class of FOT. Abbreviations: AUCs, areas under the curve; FrL, frequency-dependent fractional inertia; FrOr, fractional-order model.

For the eRIC model, similar to the results for smokers (Table 3), Rt was the more discriminative parameter [AUC=0.827 (0.726–0.902), Se=80.0 (64.4–90.9), Sp=72.5 (61.5–89.2)]. This model achieved an appropriate value for clinical use (AUC >0.80).⁴³ The evaluation of the fractional-order parameters showed that FrL was the more accurate parameter in mild COPD, achieving a high diagnostic accuracy (Table 4; AUC >0.90) [AUC=0.953 (0.881–0.988), Se=92.5 (79.6–98.4), Sp=92.5 (79.6–98.4)].^43,44

A detailed description of the ROC curves for the most accurate parameters for the traditional analysis and the studied eRIC and FrOr models in smokers and mild COPD is provided in Figure 6. The comparative analysis among the AUCs showed that, despite the visually observed difference, the accuracy obtained using traditional parameters and eRIC and FrOr model parameters in smokers was statistically similar (Figure 6A and B). In contrast, the diagnostic accuracy obtained by the fractional inertance was significantly higher than that observed for the best traditional FOT parameter (Cdyn; P=0.0001) and the eRIC model parameter (Rt; P<0.05) in patients with mild COPD (Figure 6C and D).

Figure 6 ROC curves for the most accurate traditional FOT, eRIC and FrOr parameter in smokers (A) and mild COPD patients (C). Associated comparative analysis of these AUCs and the standard errors in smokers (B) and mild COPD patients (D) are also described. Abbreviations: AUCs, areas under the curve; FOT, forced oscillation technique; FrOr, fractional-order model; ns, not significant; ROC, receiver operating characteristic.

Discussion

This study evaluated the hypothesis that FrOr respiratory system modeling may improve the diagnostic accuracy of FOT in smokers and mild COPD patients. Four major findings were obtained: 1) Initially, the traditional FOT parameters, the eRIC model, and the studied FrOr model provided a consistent description of the COPD pathophysiology; 2) these parameters were correlated with spirometry results; 3) the FOT parameters and eRIC modeling may adequately identify early abnormal changes; and 4) the use of FrOr modeling further improved this process, allowing the early diagnosis of smokers and mild COPD patients with high accuracy.

There were no significant changes between the weight and height in the studied groups, and age exhibited a small significant increase among the investigated groups (Table 1). However, the analyzed groups can be considered homogeneous because aging does not significantly change the FOT parameters. Height was the most influential parameter in this analysis.⁴⁷ The observed reductions in the spirometric parameters were consistent with the classification values for the severity of airflow limitation in COPD.⁴⁸

In line with previous FOT results in smokers and mild COPD patients, and in contrast with the study of Di Marco et al, the resistive parameters presented a highly significant increase (R0, R4, Rm; Table 1).^6,13,49–51 In the study of Shinke et al approximately 60% of the studied smokers showed elevated resistance.⁵² Using an impulse-oscillation system, Frantz et al and Elbehairy et al showed that pulmonary resistance can indicate abnormalities earlier than conventional spirometric parameters, while Crim et al found increased resistance values in subjects with mild COPD.^9,53,54 Reasonable relationships were observed among the resistive parameters and the spirometric indices (Table 3), mainly the indices associated with airway obstruction. These observations are consistent with the results of previous studies.⁵⁵ The resistive changes in Table 1 reflect the worsening airway obstruction in COPD, which further supports this interpretation as a deterioration of the pathophysiological process.

In the present study, the mean values of S, Xm and fr did not change significantly in smokers and mild COPD (Table 1). These findings are consistent with previous results in smokers and mild COPD patients, providing additional evidence that these parameters are not useful as an index for the initial effects of COPD.^5,13,51 In contrast, studies using impulse oscillometry described significant changes in the frequency dependency of the resistive values and the fr in mild COPD.⁵³ The presence of smoking and mild COPD resulted in lower average values of Cdyn and increased values of Ax and Z4 (Table 1). These results are in close agreement with those described in previous studies in smokers and mild COPD patients, and suggest that these parameters might be useful in detecting early changes in COPD.^6,13,50,51 The increase in Z4 is in close agreement with previous works showing that smokers with small airway dysfunction may be faced with combined increases in resistive and elastic loading, and that subjects with mild airflow limitation due to COPD require a significantly higher total amount of work to breathe.^26,54 Statistically significant correlations were observed between reactive and spirometric parameters (Table 3). It is interesting to note that in general, these correlations were higher than that observed in resistive parameters (Table 3), in agreement with previous results.⁵⁵

The changes in the parameters of the eRIC model are described in Figure 4. Similar increases in R were observed in the smoking and mild COPD groups relative to control (Figure 4A). This parameter is related to increased secretion and changes in the pulmonary parenchyma.⁴⁸ Similarly, Rt increased with disease severity (Figure 4C). This resistance corresponds to the amount of obstruction in the entire respiratory system, that is, the sum of the factors R and Rp.⁵⁶ Considering that Rp is associated with peripheral airways, these results are consistent with the presence of smoking.⁵⁷ It is known that the dysfunction of small airways is a nonspecific disorder often related to smoking. In line with these interpretations, the resistive parameters obtained from the eRIC model (Rp and Rt) were significantly associated with the spirometric indices of central and peripheral airway obstruction (Table 4).

While the changes observed in I were not significant in any of the studied groups (Figure 4D), C presented similar reductions in smokers and mild COPD (Figure 4E). In line with these results, Table 4 shows that I and C were related to the airway obstruction and lung volumes and that higher associations were observed for C. This behavior could be associated with a reduction in the respiratory system compliance or with an increase in the peripheral airway resistance.⁵⁸

Figure 5A shows that tobacco use and the presence of mild COPD in the studied groups were associated with an increase in FrL. This increase is related to the resistive properties, which are captured in this model from the real part of the fractional inertance. The significant inverse correlations of FrL and α with FEV₁ and FEF25%–75% (Table 5) link these parameters to airway obstruction. This result is consistent with the pathophysiology because during disease progression, airway resistance increases due to increased secretion and changes in the pulmonary parenchyma.⁵⁹ In line with this proposition, we found that α decreased in subjects with mild COPD (Figure 5B). This finding reflects an increased influence of FrL in the resistive properties of the respiratory system (Figure 2), which is necessary, to adequately describe the underlying abnormal physiological process.

The comparative analysis showed that the FrC values were similar in the controls, smokers and mild COPD patients (Figure 5C). Interestingly, the associated fractional exponent presented a highly significant reduction in smokers and a further reduction in mild COPD patients (Figure 5D). This result closely describes the experimentally observed increase in respiratory resistance at lower frequencies in mild COPD patients (Figure 3D). Another finding supporting this interpretation was the association of α with the spirometric parameters of small airway obstruction (Table 5; FEF25%–75%).

G reflects the energy dissipation in the respiratory system. In agreement with previous findings in patients with asthma, increased values were found with smoking and mild COPD (Figure 5E).²⁷ We can suppose that this increase may be explained, at least in part, by the proportional increase in airflow heterogeneity throughout the lung, due to changes in peripheral compliance and resistance. In line with this interpretation, extensive small airway (<2 mm in diameter) inflammation has been described in smokers who do not fit the conventional diagnostic criteria for COPD; this inflammation resulted in increased airflow resistance, which was associated with delayed mechanical time constants.⁵⁴ Another possible explanation is related to the increase in parenchymal deformity.²⁷ In agreement with these interpretations, inverse associations between G and spirometric indices were observed, including those related to peripheral obstruction [Table 5, FEV₁ (L) and FEF25%–75%].

The reduction in H, described in Figure 5F, may also be explained by the increase in parenchymal deformity.²⁷ Ionescu et al showed decreased H values in patients with severe COPD, which may be associated with decreased elastance of lung parenchyma.²⁸ The results described in Figure 5 clearly provide additional support to this hypothesis, extending these findings to patients with mild COPD and smokers. It is interesting to note that the decrease in H in Figure 5 is in contrast with the increase in H observed in a recent study of Faria et al, in which the effect of increased values of airway obstruction in asthmatic subjects was investigated.²⁷

The increase in hysteresivity in smokers (Figure 6G) reflects the increase in heterogeneity and changes in pulmonary structure. As pointed out previously, smokers with a relatively preserved FEV₁ value and conventional spirometric parameters within normal limits may have extensive small-airway impairment related to hypersecretion and inflammation.^26,54 The increase in hysteresivity is even more evident in the presence of mild COPD. This result is in close agreement with typical COPD pathology and may also be associated with a proportional increase in airflow heterogeneity throughout the lung with increasing tobacco use (Table 1).¹ As seen in Table 5, η was associated with several spirometric parameters, mainly parameters associated with central and peripheral airway obstruction. In close agreement with our results in smokers and mild COPD patients, Ionescu et al observed increased damping, elastance and hysteresivity using fractional-order models in patients with more advanced COPD [FEV₁(%)=43±9].²⁹

A recent document from the scientific societies of five European countries thoroughly discussed COPD with “mild” airflow limitation, and directed the attention of the scientific community to this condition.²⁶ It was pointed out that for patients with mild airflow limitation, exclusive reliance on spirometry may result in underestimation of clinically important physiologic impairments. The results of the present study are in line with this proposition, and with previous works showing that marked impairments were observed in subjects with mild airway obstruction and symptomatic smokers with borderline spirometry.^8,49

The current study shows that FOT can adequately detect abnormal changes in the respiratory mechanics of smokers and patients with mild COPD (Tables 6 and 7). Previous studies suggested that measurement of impedance with FOT has the potential to assess mild COPD; these studies also provided clear evidence suggesting that FOT may detect changes in distal airway function earlier than conventional spirometry, even in the setting of normal spirometric parameters.^9,26,60,61 These findings are, therefore, providing a further step towards diagnostic validation of FOT in the analysis of the early effects of COPD. To the best of our knowledge, this is the first study directly examining the use of FrOr modeling to perform this important task. Notably, we observed a nearly complete discrimination when this methodology was used (Table 7). In smoker subjects, a high diagnostic accuracy was obtained (AUC >0.9) using the best FrOr parameter, while traditional FOT and eRIC modeling achieved only adequate diagnostic accuracy (AUC >0.8) (Figure 5A and B). The comparative analysis of the AUCs, however, showed no significant differences. For patients with mild COPD, the best FrOr parameter was significantly more accurate than traditional FOT and eRIC modeling parameters (Figure 5C and D). This finding represents an important improvement in the diagnostic accuracy of early changes due to smoking and COPD. The finding that the highest accuracy values were obtained with the FrOr model is consistent with previous results in subjects with mild asthma and in workers exposed to asbestos.^27,62 This finding can be explained by the capacity of the FrOr models to adjust to fractional values of 20 dB/dec; in contrast, integer-order models are limited to integer multiples of 20 dB/dec. The inclusion of a real part that is dependent on frequency may have contributed to a more accurate description of the dynamic response of the respiratory system and to the consequent increase in the diagnostic accuracy. This improved accuracy is described in Figure 3, mainly when increasing resistance is observed (Figure 3B).

Since the first studies in the 1960s, FOT has emerged as a powerful method not only to provide insight into the mechanisms responsible for smoking-induced respiratory diseases but also to provide clinically relevant information.⁶³ Several recent improvements in the areas of sensors and signal processing have allowed FOT to achieve a high level of sophistication. A recent meta-analysis suggested a potential role for FOT in the diagnosis of COPD but indicated that further studies in large groups of patients and subjects were required to confirm these findings.⁶⁴ This method is particularly attractive for CPOD from a clinical point of view since FOT is measured during normal tidal breathing. Plethysmography is cumbersome and requires significant coordination and cooperation from the patient. FOT may therefore be an appropriate alternative for the management of COPD since these patients are often older and may find plethysmography difficult to perform. In this sense, a recent study concluded that FOT was useful as a simple and accurate tool in patients with geriatric COPD who have difficulties performing conventional lung function tests.⁶⁵ Given the high clinical relevance of the identification of the silent but destructive progression of the airway disease in COPD in vulnerable populations, this paper provides evidence that changes in impedance parameters might indicate early pathophysiological changes in the airways of smokers and mild COPD.

Conclusion

We hypothesized that modeling the respiratory impedance measurements using a FrOr model may offer a more sensitive indicator of the initial changes in respiratory mechanics, providing an additional tool to diagnose early COPD. Initially, it was observed that the pathophysiology of COPD was adequately described by the traditional FOT parameters, the eRIC model, and the studied FrOr model. These results provide physiological insight into the initial effects of smoking on lung mechanics. The diagnostic accuracy analyses indicate that FOT parameters and eRIC modeling may adequately identify these changes. More importantly, the use of FrOr modeling significantly improved this process, allowing the early diagnosis of smokers and patients with mild COPD with high accuracy. This result indicates that FrOr parameters may play an important role in the early diagnosis of COPD, which is crucial in improving the clinical management of the disease.

Acknowledgments

The Brazilian Council for Scientific and Technological Development (CNPq) and Rio de Janeiro State Research Supporting Foundation (FAPERJ) supported this study. This study was financed in part by the Coordenação de Aperfeiçoamento de Pessoal de Nível Superior – Brasil (CAPES) – Finance Code 001.

Disclosure

The authors report no conflicts of interest in this work.

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Supplementary material

Supplementary data S1

Instrumentation

FOT measurements were performed using an instrument developed in our laboratory and were characterized by low pressure oscillations in the frequency range between 4 and 32 Hz with an amplitude of 1 cm H₂O.¹ This signal was produced by a speaker and transmitted to the respiratory system by a mouthpiece. The resulting flow and pressure signals were measured near the mouth by a pneumotachometer and a pressure transducer, respectively. After amplification, these signals were processed using the Fourier transform (F) to estimate the respiratory impedance (Zrs) by the ratio between the pressure (P) and respiratory flow (V´) signals [Zrs=F(P)/F(V´)]. During the FOT tests, three trials of approximately 16 seconds were performed with the individuals sitting with their trunk and their head in the neutral position and using a nasal clip. The subjects breathed quietly through a silicone mouthpiece and held their cheeks with their hands.

Reference

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