Measuring the lung function in the mouse: the challenge of size
© The Author(s) 2003
Received: 30 August 2002
Accepted: 14 January 2003
Published: 15 May 2003
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© The Author(s) 2003
Received: 30 August 2002
Accepted: 14 January 2003
Published: 15 May 2003
Measurement of the effects of drugs, mediators and infectious agents on various models of lung disease, as well as assessment of lung function in the intact mouse has the potential for significantly advancing our knowledge of lung disease. However, the small size of the mouse presents significant challenges for the assessment of lung function. Because of compromises made between precision and noninvasiveness, data obtained may have an uncertain bearing on the mechanical response of the lung. Nevertheless, considerable recent progress has been made in developing valid and useful measures of mouse lung function. These advances, resulting in our current ability to measure sophisticated indices of lung function in laboratory animals, are likely to lead to important insights into the mechanisms of lung disease.
Much of our current understanding of the normal functioning of the lung and mechanisms of lung disease comes from studies utilizing animals. As one clear example, animal systems of a wide variety of species, including humans, provided the essential mechanistic proof of a link between inflammation and airways hyperresponsiveness that set the stage for current anti-inflammatory therapy . Mice are now widely employed in lung research because of certain advantages this species is thought to provide . Advantages of using mice include a well-understood immunologic system, the vast array of available reagents, a short reproductive cycle, a well-characterized genome, the advent of transgenic technology, and economic factors [2–4]. Using mice as models of human disease, in particular asthma, has certain shortcomings [2, 5] only some of which will be covered in this review. For any animal system to yield useful and valid insights into disease it must exhibit an appropriate phenotype. It has become apparent that the valid assessment of lung function in an animal as small as the mouse requires that a number of technical challenges be overcome.
The paucity of information on the measurement of lung function in the mouse has largely reflected the difficulty of measuring the necessary respiratory signals of flow, volume and transpulmonary pressure. This applies particularly to the small gas flows involved [6, 7]. However, the work of Martin et al in 1988 demonstrated that measurements of pulmonary resistance and compliance could be made in this small species . At about the same time, Levitt and Mitzner clearly illustrated the utility of using mice to explore the genetics of hyperresponsiveness [9, 10]. Since these studies, the use of mice to study lung disease has increased dramatically and a number of approaches have been developed in the ensuing years for measuring lung function in mice in vivo. In this review we examine these various methods and discuss their respective attributes. Each approach represents a compromise between accuracy, non-invasiveness, and convenience .
The viscoelastic model in Fig. 2B does a substantially better job of describing frequency-dependent nature lung mechanics than the model in Fig. 2A. Nevertheless, the simple model in Fig. 2A still serves as the conceptual platform for most studies of lung mechanics and bronchial responsiveness. The mechanical behavior of this model is described by its equation of motion. This equation is based on simple physics and states that the force (pressure) applied to the model is equal and opposite to the opposing force (pressure) the model generates. The applied pressure, P, is that supplied either by the respiratory muscles or a mechanical ventilator. The opposing pressure is made up, in general, of three components: a resistive pressure (P res ), an elastic pressure (P el ), and an inertive pressure (P in ).
P res is described by Ohm's law:
where R is the resistance of the lung and is flow of gas. P el is described by Hooke's law:
where E is lung elastance (equal to the inverse of compliance, C) and V is lung volume relative to functional residual capacity. P in comes into play only at frequencies well above those of normal breathing, while both P res and P in become negligible when frequency is extremely low. Thus, the equation of motion relevant to normal breathing is
The parameters R and E are both profoundly dependent on breathing frequency and lung volume.
The volume of the lungs has an important influence on its pressure-flow relationships. For example, an increase in lung volume stretches the airways open and so causes airway resistance to fall (tethering). This also makes it more difficult for the airways to narrow when the airway smooth muscle contracts, and represents an important mechanism by which the challenged lung can defend airway caliber [18, 22]. Unlike larger laboratory animals, the measurement of lung volume in the mouse is particularly problematic due to its small size. For example, when thoracic gas volume is measured using the conventional Boyle's Law technique, the volumes of air in the transducers used to measure plethysmographic and airway-opening pressures must be small relative to the lung volume, or significant measurement errors will occur. It has only recently been reported that measurement of functional residual capacity (FRC) by this approach is at all feasible . The measurement of FRC with gas dilution is equally difficult, again due to the small size of the mouse lung, and there are only a few reports in the literature on the use of this technique . Other studies of mouse lung volume have used a buoyancy approach , a degassing approach [26, 27], and even a CT scanner method has been reported . None of these, however, is particularly practical for most study designs. Better techniques for measuring lung volumes in mice are certainly needed, so this will be a fruitful area for future research.
The component of the transpulmonary pressure loss that is out of phase with flow and in phase with volume, as well as the recoil pressure exerted by the lung under static conditions, are caused by the elastic forces within the lung. The loss of elastic recoil within the lung defines emphysema while an increase defines restrictive processes [18, 25]. The chest walls and other thoracic structures in mice are extremely compliant, so most elastic recoil measured in an intact animal can be attributed specifically to the lung. Moreover, the elastic recoil of the lung shows considerable genetic variability that needs to be taken into account in study designs . The elastic recoil of the lung is conveniently assessed in terms of the quasi-static pressure-volume (PV) curve measured by inflating and deflating the lung in a step-wise fashion. The inspiratory limb of the curve traverses a path through values of P that are higher than those of the expiratory limb, the difference between the two limbs being termed hysteresis. Changes in the inspiratory limb of the PV curve that cause an increase in hysteresis are taken to indicate enhanced airway closure, such as that observed in humans after dry cold gas inhalation  and recapitulated in mice with allergic inflammation . These changes in PV characteristics can be sensitive indicators of lung dysfunction and contribute to the genesis of hyperresponsiveness. The shape of the pressure volume relationship is one manifestation of the nonlinear characteristics of lung mechanics in the normal, unperturbed lung. Airflow resistance also exhibits alinear behavior as the airflow reaches high rates of flow as sudden changes in lumenal dimensions occur (e.g. vocal chords). The mouse lung exhibits alinear elastic (compliance) behavior that increases following antigen challenge, a change that is most consistent with reopening airways that were closed [29, 30]. Airflow is not alinear (i.e. laminar flow regimes) in either condition as it is highly unlikely turbulent flow occurs in mouse lungs due to the small airway diameters, unlike humans where turbulent flow is a common occurrence , pointing to a clear limitation of this species in exploring complex airflow conditions.
This approach to assess lung function involves placing the subject into a small closed box and measuring the pressure changes within the box that occur as the animal breathes [7, 11, 32]. The animal is conscious and unrestrained. This technique currently enjoys wide popularity (for example see ) because 1) it is simple and 2) the mouse remains unharmed after the experiment. The endpoint is the heuristic variable known as Penh, which stands for 'enhanced pause'. It is important to note that there is no linkage between Penh and other variables that are derived from mechanical principles – Penh is merely an empirical derivative of the respiratory variations in box pressure . While an earlier publication demonstrated reasonable correlations between Penh and invasive measures of lung mechanics , recent publications draw into serious question the validity of using Penh to measure lung function [7, 11, 34].
The pressure changes occurring within the box as the mouse breathes are derived first from gas compression and decompression within the thorax – an event linked to the state of lung mechanics – and second from humidification and warming of inspired gas – an event unrelated to lung mechanics. During bronchoconstriction, both components increase , but much of this increase is likely due to the increased stimulation to breathe that would arise from chemoreceptor receptors in the lung. Hence box pressure changes should be influenced by chemoreceptor sensitivity and genetics that control responses to chemo- or irritant- receptor stimulation and integration [11, 35]. Recent studies show that changes in Penh depart from mechanical changes during a state of increased box temperature [7, 34] in an exactly opposite way during exposure to hyperoxic conditions [34, 35] and temporarily . These findings show that Penh is not a valid measurement of the lung function of the mouse except as a measure of patterns of respiration, and it has been known for a long time that patterns of respiration usually have little bearing on lung mechanics. Finally, a response in Penh may also be due to changes in nasal cavity resistance, as the upper airways are very significant contributors (50%) to total lung resistance and their contribution is likely to change depending on the experimental situation .
The next step on the phenotyping uncertainty continuum (Figure 3) is the measurement of the magnitude of respiratory system or lung impedance. Lung impedance is a complex quantity having both real and imaginary parts (see section 'Forced oscillations and the constant phase model'), and its calculation requires rather sophisticated methods. The magnitude of impedance (|Z rs |), however, is easily determined simply as the ratio of the absolute value of the swing in pressure (ΔP) to the absolute value of the swing in flow (Δ ) occurring over a breath, thus
The major disadvantage of this technique is that even though a direct measure of lung function is made, no insight is obtained as to where in the lung an abnormality might be located. This is a significant limitation if one wishes to explore the mechanisms of bronchoconstriction and whether it reflects, for example, central versus peripheral airways dysfunction. Nevertheless, this simple approach has produced significant advances in our understanding of the genetics of hyperresponsiveness [3, 9, 10].
A classic approach to assessment of lung mechanics in animals is the measurement of dynamic lung resistance (R L ) and compliance (C dyn or C L ) [3, 8, 20, 38–40]. In the past, this approach was often used to assess central versus peripheral alterations in lung mechanics – a topic of considerable current interest. The calculation of R L and C dyn requires the measurement of intrathoracic pressure that, in larger animals, is obtained with an esophageal balloon or pleurel catheter, but in a mouse is obtained either by opening the chest or by making the reasonable assumption that the chest wall presents little mechanical load compared to that of the lung [26, 41, 42]. Flow is usually obtained with a pressure transducer but this approach is problematic when miniaturized to the mouse [7, 43]. Accordingly, flow is commonly derived from the differentiation of a volume signal, usually obtained from a body plethysmograph [8, 40]. The values of R L and C L are then derived by fitting the equation of motion (Equation 4) to measurements of pressure, flow and volume.
The measurement of R L and C L , while technically challenging, does yield additional insight into the mechanisms of bronchoconstriction over that provided by |Z rs |. Generally speaking, an increase in R L reflects both narrowing of the conducting airways and alterations in the lung periphery (heterogeneous narrowing or closure of distal airways together with changes in the intrinsic mechanical properties of the parenchyma). Decreases in CL, on the other hand, reflect only events in the lung periphery, particularly airway closure leading to lung unit derecruitment . If the response to an intervention is limited largely to R L , then a relatively proximal location is implicated for the effect. By contrast, a selective change in C L is indicative of a more distal site of action [3, 8, 45]. As an example of this approach, R L and C L were clearly shown to be independent variables in mice treated with an antibody agonist for VLA-4, an adhesion protein of the eosinophil . Furthermore, the genetic dependence of these variables suggests that the factors that control central airway function (reflected in R L ) are different from those that control peripheral airway function (reflected in C L ) .
The key advantage of this approach, as compared to the determination of R L and C L or |Z rs |, is that Z rs can be fitted to a more complex model of the lung known as the constant-phase model  which makes a clearer distinction between central and peripheral events in the lung. The equation of motion of the constant-phase model is
where R aw is the resistance of the airways that are attached to the constant phase element, I aw is the inertance of the gas in the airways (which has negligible effect in the mouse below 20 Hz and can be ignored ), G ti is tissue resistance or damping, H ti is tissue elasticity, and i is . As R aw is a measure of central airways resistance, it would be expected to change if the airways are significantly narrowed. By contrast, G ti reflects either changes in tissue physical properties or regional airways heterogeneity. If changes in R aw are small, then any changes in G ti most likely represent changes in the parenchyma or very small airways. Acute changes in H ti are likely to reflect lung derecruitment (airway closure) , whereas chronic changes in H ti would be expected to reflect changes in the intrinsic mechanical properties of the parenchyma. This technique is now being successfully and extensively used to assess lung mechanics of the mouse [17, 33, 50].
We believe that the well-founded theoretical basis of the FOT, and its rigorous application in mice, will lead to considerable insight into the functioning of mouse models of lung disease.
Measurement of lung function in a creature as small as the mouse presents considerable technical challenges. However, with the exception of the measurement of absolute lung volume and the analysis of blood gases, we have now conquered the challenge of miniaturizing the instrumentation necessary for mouse lung function assessment. Application of advanced techniques such as the FOT coupled with constant-phase model analysis hold particular promise for improved characterization of lung responses to intervention and pathology. With these approaches, we can now unravel the mechanisms of airways dysfunction, the influence of genetics and the immunological factors that define the physionome of the mouse.
breaths per minute
forced oscillation technique
functional residual capacity
tissue damping or tissue resistance
mean linear intercept
total lung capacity
impedance of the respiratory system
Magnitude of impedance
The authors would like to acknowledge the support of NIH NHLBI grants HL 56638, HL 60793, PO1 HL 67004 and NCRR COBRE program PO1 RR-15557.