Abstract
A serial lung model with a compressible segment has been implemented to simulate different types of lung and airway disorders such as asthma, emphysema, fibrosis and upper airway obstruction. The model described can be used during normal breathing, and moreover the compliant segment is structured according to more recent physiological data. A parameter estimation technique was applied and its reliability and uniqueness were tested by means of sine wave input signals. The characteristics of the alveolar pressure/flow patterns simulated with the model agree to a great extent with those found in the literature. In the case of absence of noise the parameter estimation routine produced unique solutions for different simulated pathologic classes. The sensitivity of the different parameters depended on the values belonging to each class of pathology. Some more simplified models are presented and their advantages over the complex model in special types of pathology are demonstrated. Noise added to the simulated flow appeared to have no influence on the estimated parameters, in contradiction to the effects with noise added to the pressure signal. In that case effective resistance was accurately estimated. Where parameters had no influence, as for instance upper airway resistance in emphysema or peripheral airway resistance in upper airway obstruction, the measurement accuracy was less. In all other cases, a satisfactory accuracy could be obtained.
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Abbreviations
- C :
-
compliance of the lung, litre kPa−1
- EE :
-
square error
- K 1 :
-
linear resistance of the large airways, kPa litre−1 s
- K 2 :
-
turbulent resistance of the large airways, kPa litre−2s2
- K 3 :
-
linear resistance parameter model 2, kPa litre−1s
- K4,K5:
-
linear resistance parameters model 3 for inspiration and expiration, respectively, kPa litre−1s
- K6,K7:
-
linear resistance parameters model 4 for inspiration and expiration, respectively, kPa litre−1s
- K8,K9:
-
turbulent resistance parameters model 4 for inspiration and expiration, respectively, kPa litre−1 s2
- R eff :
-
effective resistance, kPa litre−1s
- R c :
-
linear resistance of the compressible segment, kPa litre−1s
- R c 0 :
-
weighting constant (see text), kPa litre−1s
- R p :
-
resistance line trough extreme pressure points, kPa litre−1s
- R s :
-
linear resistance of the small airways, kPa litre−1s
- R u :
-
total resistance of the upper airways, kPa litre−1s
- P A :
-
alveolar pressure, kPa
- P L :
-
elastic lung recoil, kPa
- P L, FRC :
-
elastic lung recoil at FRC, kPa
- P tm :
-
transmural pressure, kPa
- P pl :
-
pleural pressure, kPa
- P s :
-
pressure drop over the small airways, kPa
- V A :
-
alveolar volume, litre
- V L :
-
alveolar volume+volume of the airways, litre
- V c :
-
volume of the compressible segment, litre
- V cN :
-
maximum volume of the compressible segment for normals, litrs
- V′ A :
-
flow into the alveolar space, litre s−1
- V′ m :
-
flow at the mouth, litre s−1
- V c0 :
-
weighting constant (see text), litre
- P tms :
-
point of curvature for the compressible segment, kPa
References
Benerjee, M., Evans, J. N. andJaeger, M. J. (1976) Uneven ventilation in smokers.Respirat. Physiol.,27, 277–291.
Bekey, G. A. andBeneken, J. E. W. (1978) Identification of biological systems: a survey.Automatica,14, 41–47.
Bogaard, J. M., Pauw, K. H., Versprille, A., Stam, H., Verbraak, A. F. M. andMaas, A. J. J. (1987a) Maximal expiratory and inspiratory flow-volume curves in bilateral vocal-cord paralysis.ORL,49, 35–41.
Bogaard, J. M., Pauw, K. H. andVersprille, A. (1987b) Flow limitation in upper airway obstruction (theoretical analysis), —Ibid.,49, 42–47.
Cettl, L., Dvorak, J., Felkel, H. andFeuereisl, R. (1979) Results of simulation of nonhomogeneous ventilatory mechanics for a patient-computer arrangement.Int. J. Bio-Med. Comput.,10, 67–74.
Cotes, J. E. (1975)Lung function. Assessment and application in medicine. Blackwell Scientific Publications.
Dubois, A. B., Botelho, S. Y. andComroe, J. H. Jr. (1956) A new method for measuring airway resistance in man using a bodyplethysmograph values in normal subjects and in patients with respiratory disease.J. Clin. Invest.,35, 327–335.
Feinberg, B. N., Chester, E. H. andSchoeffler, J. D. (1970) Parameter estimation: a diagnostic aid for lung diseases.Instrum. Technol., 40–46.
Feinberg, B. N. andChester, E. H. (1972) A dynamic model of pulmonary mechanics to simulate a panting maneuver.Bull. Physio-path. Respirat.,8, 305–322.
Golden, J. F., Clark, J. W. Jr., andStevens, P. M. (1973) Mathematical modeling of pulmonary airway dynamics.IEEE Trans.,BME-20, 397–404.
Guyatt, A. H., Alpers, J. H., Hill, I. D. andBramley, A. C. (1967) Variability of plethysmographic measurements of airway resistance in man.J. Appl. Physiol.,22, 383–389.
Holland, W. P. J., Verbraak, A. F. M., Bogaard, J. M. andBoender, W. (1986) Effective airway resistance: a reliable variable from bodyplethysmography (A theoretical analysis and an application in COLD patients).Clin. Physics & Physiol. Meas.,7, 319–331.
Hyatt, R. E. andFlath, R. E. (1966) Influence of lung parenchyma on pressure-diameter behaviour of dog bronchi,J. Appl. Physiol.,21, 1448–1452.
Hyatt, R. E. (1983) Expiratory flow limitation.J. Appl. Physiol.: Respirat. Environ. Exercise Physiol.,55, 1–8.
Lambert, R. K., Wilson, T. A., Hyatt, R. E. andRodarte, J. R. (1982) A computational model for expiratory flow. —Ibid.52, 44–56.
Macklem, P. T. andMead, J. (1968) Factors determining maximum expiratory flow in dogs.J. Appl. Physiol.,25, 159–169.
Marquardt, D. W. (1963) An algorithm for least-squares estimation of nonlinear parameters.SIAM J.,11, 431–441.
Martin, H. B. andProctor, D. F. (1958) Pressure-volume measurements on dog bronchi.J. Appl. Physiol.,13, 337–343.
Martin, C. J., Young, A. C. andIshikawa, K. (1965) Regional lung mechanics in pulmonary disease.J. Clin. Invest.,44, 906–913.
Matthys, H. (1971) Ganzkörperplethysmographie.Pneumonology I,146, 216–231.
Matthys, H., Fischer, J., Ulrichs, H.Ch. andRühle, K. H. (1979) Functional patterns of different lung diseases for computer-assisted diagnostic procedures.Progr. Respirat. Res.,11, 188–201.
Mead, J., Turner, J. M., Macklem, P. T. andLittle, J. B. (1967) Significance of the relationship between lung recoil and maximum expiratory flow.J. Appl. Physiol.,22, 95–108.
Murtagh, P. S., Proctor, D. F., Permutt, S., Kelly, B. L. andEvering, S. (1971) Bronchial mechanics in excised dog lobes. —Ibid.,31, 403–408.
Otis, A. B., McKerrow, C. B., Bartlett, R. A., Mead, J., McIlroy, M. B., Selverstone, N. J. andRadford, E. P. Jr (1956) Mechanical factors in distribution of pulmonary ventilation.J. Appl. Physiol.,8, 427–443.
Pride, N. B., Permutt, S., Riley, R. L. andBromberger-Barnea, B. (1967) Determinants of maximal expiratory flow from the lungs. —Ibid.,23, 646–662.
Pride, N. B. (1971) The assessment of airflow obstruction (role of measurements of airway resistance and of tests of forced expirations).Br. J. Dis. Chest.,65, 135–169.
Reinert, M., Heise, D. andTrendelenburg, F. (1975)_Zum Auswertemodus phasenverschobener Resistancekurven.Pneumologie,152, 147–156.
Rohrer, F. (1915) Der Strömungswiderstand in der menschlichen Atemwegen und der Einfluss der unregelmässigen Verzweigung des Bronchialsystems auf der Atmungsverlauf in verschieden Lungenbezirken.Pflügers. Arch. Ges. Physiol.,162, 225–259.
Smidt, U., Finkenzeller, P. andRennings, C. (1975) On-line Computereinsatz in der Ganzkörperplethysmographie zur Berechnung der mittleren Resistance.Pneumologie,151, 223–231.
Ulmer, W. T. andReif, E. (1965) Die obstruktiven Erkrankungen der Atemwege. Klinische Bedeutung und objektiver Nachweis mit der Ganzkörperplethysmographie.Dtsch. Med. Wschr.,90, Jg. 41.
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Verbraak, A.F.M., Bogaard, J.M., Beneken, J.E.W. et al. Serial lung model for simulation and parameter estimation in body plethysmography. Med. Biol. Eng. Comput. 29, 309–317 (1991). https://doi.org/10.1007/BF02446714
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DOI: https://doi.org/10.1007/BF02446714