Practical Difficulties

As briefly alluded to in the introduction, the investigator faces a number of difficulties in attempting to count the number of alveoli in the human lung. First of all, by virtue of the elastic nature of the lung, it is prone to collapse when taken out of the thoracic cavity, and thus volumetric information is lost in lung biopsy specimens. Furthermore, unless properly fixed, a thin section of the lung distorts the architecture. To perform structural analysis of the periphery of the lung, the specimen must first be fixed by instillation of fixative through the airways or the blood vessels (2). Therefore a complete lung or lobe is necessary to prepare samples for lung structure by morphometry. This, clearly limits the availability of lung specimen to postmortem specimen.

Attempting to assess alveolar number in childhood using morphometric analysis is problematic because lung specimens from healthy childhood are difficult to acquire, both because of the inherent low mortality rate in children over five years of age and because of the high incidence of respiratory morbidity and mortality associated with available specimens. In addition, changes in law have made it increasingly difficult to access pathologic specimens for research.

Assessment of peripheral lung development ideally requires serial measures in the same lung. The reliance on autopsy specimen means that serial measures of the anatomy of the lung periphery is not possible. Alveolarization was instead studied by calculating the alveolar numbers in different individuals, which introduced the problem of interindividual variability. Also, determining factors influencing growth and development of the lung periphery has only been possible by using animal models and surrogate markers.

Technical Issues

There have been numerous technical advances in the science of morphometry since Weibel’s pioneering work (19). These advances have surmounted various technical issues in morphometry. It is beyond the scope of this chapter to explore these in detail, but the reader is referred to the review by Weibel et al. (25), the published scientific debate between experts in the field (26–30), and the official policy statement of American Thoracic Society/European Respiratory Society for quantitative assessment of lung structure (2). I have detailed here some important issues that need to be understood for the evaluation of the published work on human alveolarization.

Compiling the results of the studies exploring alveolarization in children, it is evident that there is a wide variance between studies in both the measured alveolar number and the estimated age of completion of alveolarization (Figure 13-1). The preparation of pathologic specimen is markedly different in different studies. For example, Davies et al. (21) inflated lungs with buffered formalin at 75 cm water pressure, Angus and Thurlbeck (11,22) used inflation pressures of 25 cm water, while Weibel (20)used formalin steam instilled at pressures of 5–10 cm water while the lung was kept inflated by negative pressure. It follows that the degree of alveolar inflation will be different between studies. Despite this, several authors (10,11) have used Weibel’s value of 1.55 for the shape coefficient, β (see earlier), despite β being dependent on the relation between surface area and volume.

Figure 13-1.

Number of alveoli in the developing human lung estimated by morphometry from previously published studies. References: Dunnill 1962(10), Weibel 1962(9), Davies 1970(21), Angus 1972(22), Thurlbeck 1982(12), Hislop 1986(23).

Reprinted with permission of the American Thoracic Society. From Narayanan M et al. Alveolarization continues during childhood and adolescence: new evidence from helium-3 magnetic resonance. Am J Respir Crit Care Med. 2012 Jan 15;185(2):186–191. Official Journal of the American Thoracic Society. Copyright © 2014 American Thoracic Society.

Another limitation of the studies using morphometric techniques to determine endpoint of alveolarization is that the same inflation pressure was used to inflate lungs of children in different age groups. It has been noted that the range of lung volumes at which fixation occurs is between 50 and 70% of total lung capacity, with the actual value set by individually varying compliance of the thorax (31). This may change the relative degree of inflation of alveoli between the subjects, with a strong likelihood of bias (it is likely that compliance varies with age). The pronounced intersubject scatter (11,22) may also be partially explained by this phenomenon. The assumptions that the shape coefficient, β, and the distribution coefficient of alveoli (i.e., a coefficient relating to standard deviation of the size of individual alveoli) do not vary with age may also be flawed and may lead to a variability of about 20% and 10%, respectively in the results (11).

Measurements by classical morphometry were done on a very small sample (between 1:100000 to 1:1000000) of the alveoli (27). It is essential, in these circumstances, to ensure randomization of sampling. This has been achieved with newer morphometric techniques [e.g., design-based stereology as described by Hyde et al. (32,33)]. Unfortunately, the newer techniques (2) have not been used to determine the endpoint of alveolarization in humans.

New Histological Techniques to Determine Alveolar Number

Techniques that surmount the pitfalls mentioned have been developed following the development of the science of stereology and the description of the “disector” by Sterio (34). It is not the remit of this chapter to discuss this technique in detail, but interested readers are referred to excellent reviews on the subject (25,35,36). In brief, the process of counting the number of particles in a specimen starts by successively dividing the fixed specimen into blocks, from which a random number of blocks are selected. The selected blocks are then oriented in a random manner before subdivision into subblocks. A random fraction of these subblocks is then selected, and the process is repeated until sections that can be assessed under a microscope can be prepared. At this stage, random sets of two contiguous sections are assessed, viz., the “sampled section” and the “look-up section” (36). The number of particles that appear in the sampled section, but not the look-up section is calculated, and the number is then summed over all the sampled sections (Q). The number of particles in the whole specimen can then be calculated from Q and the fraction of the specimen assessed under the microscope. In case of counting alveoli in lung specimen, the fact that each alveoli have a single distinct opening is utilized in determining the so-called Euler characteristic of the network of alveolar openings in the periphery of the lung (37,38). It is clear that this technique does not require any assumption of shape or orientation of the alveoli and does not depend on the degree of inflation of the lung (25).

³Helium Magnetic Resonance

Over the last decade, tremendous progress has been made to develop safe, noninvasive markers of alveolar structure and/or dimension. One of the main developments is the technique of ³HeMR, which measures the self-diffusion of hyperpolarized ³Helium (³He) within the lung during a breath hold using magnetic resonance (MR). A simplified description of the technique is given in the following paragraph. However, readers are referred to the following resources for detailed explanation of the technique (17,18,39,40).

Magnetic resonance (MR) is based on the interaction of atomic nuclei with an unpaired spin (¹Hydrogen in conventional MR; ³Helium and ¹²⁹Xenon in hyperpolarized gas MR) with an external magnetic field (41). The technique utilizes a predetermined “sequence” of radiofrequency pulses to interact with these nuclei. As a result of this interaction, these nuclei emit radiofrequency pulses, which are measured as the “signal”. In diffusion weighted MR, the sequence employed “sensitizes” the nuclei to movement. In other words, the measured signal decreases with the degree of displacement of the nucleus from its original position. The diffusion coefficient of the nucleus (D) can be calculated from the signal. In the case of ³HeMR applied to human lungs, the MR signal is measured during a breath hold after inhalation of a bolus of ³He. The diffusion of ³He in this situation is constrained by alveolar walls, as alveoli are impermeable to the ³He (Figure 13–2). Therefore, the measured value of diffusion of these nuclei, the apparent diffusion coefficient (ADC), is a function of the degree of restriction of diffusion, which in turn depends on the size of the alveoli.

Figure 13–2.

Panel A. Hypothetical stationary molecule – Diffusion coefficient D = 0. Panel B. Freely diffusing ³He molecule in air, D (free diffusion coefficient) = 0.88 cm².sec^-1. Panel C and D. Diffusion restricted by constraints, that is, alveolar walls in case of inhaled helium. The measured (apparent) diffusion coefficient (ADC) is higher in panel D than panel C and can be used as a marker of alveolar dimension. This representation is a simplification, as in reality, alveoli are not completely spherical, and they are open to alveolar ducts. However, as long as the majority of the constraints on diffusion of ³He are alveolar walls, ADC would represent alveolar dimensions.

Since the initial description of this technique, many studies have been performed in adults, confirming its utility to detect alveolar damage in emphysema (18,42,43) and in asymptomatic smokers (44). Validation of ADC against histologic parameters has been carried out in elastase-induced emphysema in rats (45,46) and in rabbits (47) and in explanted COPD affected human lungs (comparing with lungs of donors that were unsuitable for transplant) (48).

Further developments in this field include calculating length scales from the diffusion coefficients of ³He utilizing differences in the measured signal due to a number of gradient pulses, each of which sensitize ³He to different degrees of diffusion. Yablonskiy et al. (49,50) used this technique of ³HeMR and a simplified mathematical model of cylindrical alveolar ducts surrounded by a uniform sleeve of alveoli to estimate the acinar airway diameter (R) and effective alveolar depth (h). These values were validated against histological methods in rats (51) and human lungs (50). Shanbhag described measurements of average displacement (x_rms) of the ³He nuclei using a diffusion probability profile (DPP) calculated from the technique of diffusion-weighted spectroscopy and q-space analysis (52). Two components of these measurements corresponded to diameter of the alveoli and length of airspaces, respectively.

Aerosol-Derived Airway Morphometry (ADAM)

Heyder (53) described a technique of estimating the size of airways using measurement of gravitational deposition of aerosols in airways during a breath-hold following inhalation of boluses of aerosols. This measurement was based on the principle that settling velocity of the aerosol was inversely related to the caliber of the airway in still air (54). Therefore, airway caliber could be estimated (effective airway diameter, EAD) from recovery of aerosol particles on exhalation after a timed breath hold (54,55). The smallest EAD, EAD_min, corresponding to the most peripheral zone of the lung, was found to be a reliable estimate of the size of the most distal airspace generation, that is, alveoli (55). Some variables derived from ADAM have been shown to roughly correlate with histologic measures in human and dog lung specimens (56,57).

Relative Merits and Demerits of the Noninvasive Techniques

Both of these noninvasive techniques have the potential to be applied for research into alveolarization as they do not involve ionizing radiation and are free from other similar ethical concerns. Both these techniques dispense with the problem of sampling, as they effectively sample the whole lung. The respiratory maneuver required for ³HeMR is easy, as it involves just a short breath hold of three to ten seconds after inhaling the bolus of ³He from functional residual capacity (FRC). In contrast, ADAM involves breathing in the aerosol to total lung capacity (TLC) followed by a timed breath-hold and exhalation at a constant exhalation velocity.

ADAM measures EAD_min, which is suggested to be equivalent to the alveolar diameter. This may be true if the lung is comprised of a perfectly symmetric branching tree, but the airway branching both at conducting level and at acinar level is nonsymmetric, both in terms of angles and relative cross-sectional areas of the daughter segments (58–60). Also, a review of physical principles behind gas mixing and aerosol mixing suggests that aerosol deposition depends on factors other than size of the airspaces (61). These factors are themselves dependent on developmental changes, including increased depth of alveoli and changes in relative flow (61). Therefore, ADAM may not be a suitable tool to evaluate development of alveoli in childhood and adolescence.

The technique of ³HeMR relies on far fewer assumptions. The extremely high diffusivity of ³He atoms minimizes problems with nonuniform mixing. Measurements from ³HeMR have been well validated against histologic measures in both animal and human lungs (see earlier discussion). However, it must be remembered that ADC is not a measure of length but of physical restriction to diffusion. Many calculations of physical dimensions from diffusion restriction of ³He depend on geometric models and are therefore reliant on the validity of those assumptions (50). x_rms does not depend on geometric assumptions (52), but gives a mean displacement of ³He atoms, which can only be approximated to physical dimensions of alveoli.

Another concept that can affect the interpretation of ADC is “diffusion time”. This is the time available for the ³He atoms to diffuse in the physically restricted environment of the peripheral lung. If the diffusion time is too short, the diffusion is not restricted, and ADC approximates D, the free diffusion of ³He atoms in air. If the diffusion time is too long, the helium atoms undergo minimal net displacement, and ADC tends to zero. Between these extremes (diffusion times of the order of a few milliseconds) the ADC is able to give information about dimensions of alveoli (62). The value of ADC depends on the selection of diffusion time and other factors such as the strength of the external magnetic field and the sequence and magnitude of the gradients employed. Therefore, a control group is necessary in most studies using ³HeMR. As long as the limitations are recognized, ³HeMR is a potent tool to explore the question of alveolarization in humans.

Early Studies of Alveolar Development Using ³HeMR and ADAM

Using ³HeMR, Altes et al. (63) measured ADC in twenty-nine healthy subjects ranging from four to thirty years. They reported an increase of ADC with age, which suggests increase in alveolar dimensions with age. Estimation of an expected increase in ADC in the absence of alveolarization was not attempted, and therefore this study did not fully address the question about age of completion of alveolarization.

Zeman et al. (64) used ADAM to determine EAD_min at TLC in fifty-three children and young adults age six to twenty-two years and fifty-nine adults. EAD_min increased with age, and TLC varied as the third power of EAD_min. They postulated that between ages of six and twenty-two, alveoli do not increase in number but expand to cause lung growth. However, the relation of TLC with EAD_min was determined after combining measurements of children and adults. There are also a few reservations with use of this technique to determine alveolar development (see paragraph on relative merits and demerits).

Indirect Measures of Alveolar Dimensions

Measurements of diffusing capacity of carbon monoxide (DL_CO), alveolar volume (V_A) and transfer coefficient (K_CO = DL_CO/V_A) are well known physiological measures of alveolar–capillary function. The technique and principles behind these measures are well described in several textbooks and are not elaborated here (65). Some authors have used these measures as surrogates of alveolar growth (66–68). These measures, however, could be affected by hemoglobin levels, permeability of the alveolar–capillary barrier, ventilation–perfusion mismatch, and differences in pulmonary perfusion (67) and therefore should be interpreted with caution in the context of alveolar development.

Another indirect estimate of average airspace dimension depends on the finding that pressure–volume curves during passive lung deflation were related to the mean size of peripheral airspaces (69). An index of pulmonary distensibility derived from the pressure–volume curves has been shown to be related to morphometrically derived mean linear intercept (70,71). The recoil of thoracic wall has not been taken into account in the derivation, and therefore it is difficult to extrapolate this relationship to measurements in live humans. Also, it is likely that relative contributions to the P–V characteristics may change with age, and therefore, this technique has not been used to evaluate alveolar development.

Alveolarization Following Pneumonectomy in Adult Animals

Hsia et al. (72) examined peripheral lung structure in the left lungs of five dogs using morphometric techniques five months and sixteen months following right pneumonectomy. Alveolar surface density progressively increases between five and sixteen months postpneumonectomy to reach values approximating the surface density in control dogs. This adaptive response was postulated to be due to initial expansion of alveolar airspaces to fill the thoracic cavity following pneumonectomy followed by septation of enlarged airspaces (i.e. formation of new alveoli). Fehrenbach et al. (73) used the new technique of design-based stereology to assess compensatory lung growth following left pneumonectomy in adult mice. They performed left pneumonectomy in eleven adult mice and determined alveolar numbers in the right lung at day 6 and day 20 postpneumonectomy. By day 20, the right lung had gained 49% of the total alveoli lost due to removal of the left lung. In the unique situation of pneumonectomy, the residual lung can “regrow” alveoli.

Alveolarization Through the Period of Growth in Rabbits and Rhesus Monkeys

Kovar et al. (16) determined alveolar number by Weibel’s morphometric methods in rabbits at various ages from birth to thirty-six weeks of life (adulthood). They found that the alveolar number increases progressively from birth to adulthood, though the rate of new alveolarization decreases with age. Hyde et al. (15) examined the lungs of twenty-six rhesus monkeys at various ages from 4 days to 7.6 years of life (i.e., neonatal period to adulthood: somatic growth complete by about six years) using design-based stereology. The number of alveoli increased significantly with age, throughout the period of somatic growth. Rhesus monkeys are more plausible as models for cessation of alveolarization in humans than rabbits.

Calorie-Related Changes in Alveolar Number

Karlinsky et al. (74) restricted calorie intake by 50% in a group of hamsters for a period of thirty days and compared morphometric data with control hamsters. They found increased mean linear intercept and decreased lung internal surface area in the starved hamsters, suggesting destruction of alveoli related to calorie restriction. Massaro et al. (75) restricted calorie intake in adult mice by 67%. They estimated alveolar number and alveolar dimensions in the calorie-restricted mice using newer histologic techniques (76) and compared alveoli with controls. Alveolar volume increased by 44% within seventy-two hours of calorie restriction. They allowed another group of mice to feed ad-libitum after fifteen days of calorie restriction. Histologic analysis just seventy-two hours after adlibitum feeding showed that alveolar dimensions and number were restored to values prior to calorie restriction. The molecular mechanisms related to these changes were investigated, and the pathway seemed to be associated with mediators associated with apoptosis. A surprising degree of alveolar plasticity in adult mice was revealed – new alveoli could be formed or destroyed based on caloric intake.

Possible Mechanisms of Postmaturity Alveolarization

Schittny et al. (77) determined the progress of alveolarization in Sprague-Dawley rats from four days of life to sixty days (adulthood in these rats) using design-based stereology techniques. They found that new alveolar septae were being formed well into adulthood. Using 3-D synchrotron radiation X-ray tomography, they showed local duplication of single capillary layers in areas of postmaturity septal growth, which indicated a potential mechanism for postmature alveolarization. These studies dispelled the notion that the immature double capillary layers in alveolar walls were a prerequisite for new septation (14,24). Taken together, this information from mammals supports alveolarization beyond early childhood. There is no reason why this could not happen in humans. In their paper, Hyde et al. (15) have called for reconsideration of previous reports of postnatal alveolar development in humans because the previous reports were based on bias-prone techniques. Unfortunately, there have not been any studies on alveolar development in humans using new stereologic techniques. However, recent studies based on noninvasive techniques suggest that new alveoli may continue to form through the period of lung growth in humans.

Noninvasive Measurements of Alveolar Dimension During Normal Lung Growth

Narayanan et al. (78) determined ADC and x_rms as surrogates of alveolar dimensions using two techniques of ³HeMR in 109 healthy subjects between seven and twenty-one years. Measurements were also done with different degrees of gentle inflation of the lung in selected subjects. Lung volumes were measured by plethysmography in all subjects. Changes of the ³HeMR measures during lung growth were compared to changes with lung inflation. Lung inflation was used as a model for lung enlargement without alveolarization, and the comparisons were carried out based on statistical methods. Both variables, ADC and x_rms, increased with lung growth, but at a rate significantly less than the expected increase in the absence of new alveolarization. Based on the statistical model, Narayanan et al. estimated that the observed 3.4-fold increase in FRC between seven and twenty-one years of age was accompanied by a 1.94-fold (95% CI, 1.64–2.30) increase in alveolar number and a 1.75-fold (95% CI, 1.48–2.07) increase in alveolar volume (78). This was the first direct evidence regarding alveolarization to adulthood in humans.

Alveolarization Following Pneumonectomy in Adult Human

Butler et al. (79) assessed measurements derived from ³HeMR in an adult woman fifteen years after undergoing right pneumonectomy for hilar adenocarcinoma at the age of thirty-three years. The radial dimensions of acinar airways (R) calculated by applying Yablonskiy’s model (50) on the ³HeMR measurements were found to be close to normal (330±20 μm ) as against the expected value of ~390 μm, implying an increase in the number of alveoli. They calculate that there was a 64% increase in the number of alveoli following pneumonectomy.

Recovery of Alveolar Structure Following Preterm Birth

³HeMR is an ideal tool to study recovery of lung alveoli following injury. Extreme preterm birth and neonatal chronic lung disease (CLD) are important factors that affect alveolar development. Many studies (80–83) have used histologic techniques to determine peripheral lung structure on lung specimens from children who have died of CLD. Apart from one child who survived up to 7.75 years in Husain’s series, all the other human histologic data regarding the lung structure in extreme preterm survivors are from infants who died before forty months of age. Overall, these studies suggest that in children born extremely preterm, disordered peripheral lung development and, consequently, deranged alveolar structure persists until at least three years of age. When considered with the previous concept that human alveolarization was complete by three years, it was assumed that deranged alveolar structure would be a lifelong feature in preterm survivors (84,85).

This reasoning could be challenged for two reasons. First, histologic data are necessarily limited to the fatal, severe cases of preterm CLD and therefore cannot be generalized to survivors. The second challenge is to the assumption that human alveolarization is complete at three years. Animal models were developed to answer the first challenge. The best known of the animal models was the preterm baboon model developed by Dr. Coalson’s team (84,86,87). Despite this pioneering work, there were no data on long-term survivors because the maximum survival reported in the preterm baboons was eight months – a human developmental equivalent of three years. Regarding the second challenge, the assumption has come under increasing scrutiny based on the results with animal models and humans. Narayanan et al. (88) published the first direct proof that alveolar damage sustained due to preterm birth may not be lifelong. They compared measurements related to alveolar dimensions using ³HeMR in 119 children from ten to fourteen years stratified into four groups (term born, mild preterm, extreme preterm without CLD, and extreme preterm with CLD). ADC was similar in all four groups and was not related to risk factors for CLD, which implied that any derangement in alveolar development due to extreme preterm birth or CLD could be compensated for within the first decade of life in survivors. The intrasubject spread of ADC (SD_ADC) was larger in the CLD group, suggesting some subtle residual damage (89). This study had adequate statistical power to detect even small differences in alveolar dimensions in the preterm group. These results strongly support the novel notion that human alveoli have a capacity to regenerate far beyond early childhood.