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The hypothesis that ventilation of emphysematous lungs would be enhanced by communication with the parenchyma through holes in the pleural surface was tested.
Fresh human lungs were obtained from patients with emphysema undergoing lung transplantation. Control human lungs were obtained from organ donors whose lungs, for technical reasons, were not considered suitable for implantation. Lungs were ventilated through the bronchial tree or transpleurally via a small hole communicating with the underlying parenchyma over which a flanged silicone tube had been cemented to the surface of the lung (spiracle). Measurements included flow‐volume‐time curves during passive deflation via each pathway; volume of trapped gas recovered from lungs via spiracles when no additional gas was obtainable passively from the airways; and magnetic resonance imaging assessment of spatial distribution of hyperpolarised helium (3He) administered through either the airways or spiracles.
In emphysematous lungs, passively expelled volumes at 20 s were 94% greater through spiracles than via the airways. Following passive deflation from the airways, an average of 1.07 litres of trapped gas volume was recoverable via spiracles. Regions were ventilated by spiracles that were less well ventilated via bronchi.
Because of the extensive collateral ventilation present in emphysematous lungs, direct communication with the lung parenchyma through non‐anatomical pathways has the potential to improve the mechanics of breathing and hence ventilation.
Hyperinflation and gas trapping are devastating consequences of severe emphysema. The increase in total lung capacity (TLC) compromises chest wall mechanics as the thorax approaches the limit of expansion. Gas trapping increases the residual volume (RV) to TLC ratio and reduces both the slow and forced vital capacity (VC and FVC, respectively). This in turn is a major cause of reduction in forced expiratory volume in 1 s (FEV1). The progressively narrowing gap between RV and TLC increases the work of breathing and continues to decrease ventilatory capacity until the patient becomes flow‐limited even while breathing at rest. Thus, a major objective of treatment must be to decrease the amount of trapped gas.
Collateral ventilation in emphysema greatly exceeds that in normal lungs, as demonstrated in lungs removed at necropsy by Hogg et al in 1969,1 confirmed using a different technique in patients by Terry et al in 19782 and reconfirmed more recently by Morrell et al.3 Macklem, in an editorial comment, stated: “… if collateral flow resistance is less than airway resistance … ventilation … through openings directly through the chest wall into the parenchyma should bypass the obstruction, decrease work of breathing, increase alveolar ventilation and improve dyspnea. Insects breathe through openings on their body surface … called spiracles.”4
Lausberg et al recently reported that the creation of fistulas between segmental bronchi and adjacent lung parenchyma increased FEV1 and FVC in explanted emphysematous human lungs.5 The present study was designed to test the hypothesis that ventilation of low resistance collateral pathways in emphysema via spiracles through the pleura will allow trapped gas to escape and increase passive flow and volume on deflation. Openings were made directly into the parenchyma through tubes glued to the pleural surface (spiracles) in order to measure flow and volume that traversed the spiracles. Emphysematous lungs explanted from lung transplant recipients were compared with nearly normal lungs obtained from donors but rejected for transplantation because of minor abnormalities.
Preliminary studies on four emphysematous lungs showed the feasibility of studying ventilation through transpleural communications. This allowed us to develop a protocol by which we measured: (1) volume‐flow‐time relationships during passive deflation through either the bronchial tree or the spiracles from full inflation; (2) the amount of trapped gas that could be removed via the spiracles after the lung was completely deflated passively through the airways; and (3) the distribution of ventilation as assessed by MRI scans of hyperpolarised helium (3He). The complete protocol was successfully carried out in two control lungs (1 and 2) from one donor whose lungs for technical reasons were rejected for implantation and from a consecutive series of five left lungs (3–7) explanted from five patients (three women and two men) with end‐stage emphysema undergoing double lung transplant surgery. In the preliminary studies we did not complete all three parts of the protocol in any of the four lungs. We report the complete data from lungs 1–7 and, where appropriate, limited measurements on the lungs from the preliminary studies.
The mean values of preoperative pulmonary function studies are shown in table 11.. The spiracle (Hood Laboratories, Pembroke, Massachusetts, USA) made of medical grade silicone (1.7 mm thick) was a quasi‐elliptical tube (9×18 mm externally) with a flange (33×21 mm) that was glued with tissue cement to the lung as shown in fig 11.. The pleura was incised through the lumen of the tube and a 3×10 mm area of pleura was removed. The lung parenchyma was thus accessed directly through the lumen of the spiracle. Spiracles were attached to both upper and lower lobes in each emphysematous lung while the control lungs each had only one spiracle.
Each main stem bronchus was securely fitted with a cannula. The lung was inflated to TLC as judged by visual inspection with a series of small volume bursts of pressure delivered manually from a compressible respirator bag. Aside from this, only gentle massage and repeated filling/emptying cycles with airway pressure limited to 20 cm H2O were used to achieve full inflation. A major difficulty in studying the mechanical properties of emphysematous lungs ex vivo is air leakage. To circumvent this problem, major vessels were ligated to avoid leakage from the vascular and perivascular spaces. Small tears or cuts on the surface were identified by immersion in isotonic saline solution and repaired by focal ligation or tissue cement. When the lung was considered fully inflated, the bronchial cannula was opened and the lung was allowed to deflate passively through the airways.
With the spiracles closed, the lung was re‐inflated via the bronchus to transpulmonary pressures of 8.1–15.1 cm H2O in the emphysematous lungs (14.0–20.6 cm H2O in control lungs) and allowed to deflate passively via the airway6 through a pneumotachometer (RSS100‐HR, Sensor Model 3700, Hans‐Rudolph, Kansas City, Missouri, USA; flow range 0–160 l/min that includes airway and auxiliary pressure transducers) with commercial software (RSS100‐HR Research Pneumotach System Version 3.0.7b; KORR Medical Technologies, Salt Lake City, Utah, USA). The lung was again re‐inflated to a roughly similar pressure (±1 cm H2O) through the bronchus. The bronchial cannula was then closed and flow and volume were measured during passive deflation through the spiracle(s). At least three passive flow‐volume curves were obtained through each pathway and the results were averaged. We also measured the volumes expelled passively at 1, 5, 10, 15, and 20 s and beyond, to or near completion through each pathway.
The lung was then fully re‐inflated through the bronchus (to a pressure of 10–15 cm H2O), the bronchus was opened and the lung allowed to expel as much air as possible by passive deflation through the airways. The time was not recorded but commonly exceeded 1 min and uniformly exceeded 30 s. The bronchial cannula was then clamped and the spiracle(s) were opened, allowing gas trapped behind closed airways to exit passively through the spiracles into a Mylar bag. A Y‐connector was used to collect gas from both lobes simultaneously in the emphysematous lungs. The volume of trapped gas expelled was measured from the bag into a calibrated syringe.
The breath by breath distribution of ventilation of hyperpolarised 3He (two control and five emphysematous lungs) was compared by MRI.7,8 Hyperpolarised 3He of nominal polarisation 40% was prepared with two locally constructed and one commercial polariser (Amersham Health, Chalfont St Giles, Buckinghamshire, UK). To prevent 3He depolarisation by contact with oxygen, we first ventilated the lung with 100% nitrogen for 20 min using an open circuit technique and stored the lung in an airtight plastic bag containing 100% nitrogen. With intrabronchial pressure set at 2–3 cm H2O, a tidal volume of approximately 300 ml of hyperpolarised 3He (P40%) was instilled via a gas syringe to either the bronchus or spiracle. The lung was tidally ventilated by closed circuit rebreathing with the same volume for up to 10 breaths. Images were obtained at the end of each inflation cycle on a Siemens Magnetom Vision whole body scanner at 48.47 MHz (3He frequency at a nominally 1.5‐T field). A home‐built, four‐turn, in‐parallel, solenoid‐like coil with high Q took advantage of the lack of saline and low radio frequency loss.
Following the last 3He deflation‐inflation cycle, 300 ml of lung gas were removed, replaced with 300 ml room air from the syringe, and open circuit washout of 3He imaging was performed for up to six cycles. 3He imaging was repeated at the end of each inflation. Regions of interest (ROI) were chosen in each lobe near where the spiracles were located, to represent a macroscopic gas exchange volume that was significantly more efficient when delivered via spiracles than via the bronchus. These ROI were hand drawn to encompass a region approximately 0.5 litres in volume in each lobe and generally encompassed three image slices. The total ROI signal (equivalent to the total magnetic moment in the region and thus the total volume of 3He, absent the minimal effects of T1 here) was integrated and fit to a linear function. After the first extraction of 300 ml gas and subsequent insertion of 300 ml room air, the ROI signal was again integrated.
Mean values are presented with standard deviation (SD). Differences in mean values were analysed with the Student's t test.9 Time constants were calculated for the mean volume‐time curves of each lung with the equations: Vexp,aw(t) = Vexp,aw [1 − exp(−t/T,aw)] or Vexp,sp(t) = Vexp,sp [1 − exp (−t/Tau,sp)] using the software Systat Version 11 (Systat Software Inc, Richmond, California, USA) where Vexp,aw(t) and Vexp,sp(t) are the volumes expelled via each route at each time point (t); Vexp,aw and Vexp,sp are the total volumes expelled by each route; exp is e, the base of the natural system of logarithm; −t is the time in seconds to total volume; and Tau is the time constant. The values for R2 were all 0.97 or greater.
A critical determinant of lung inflation is mean airway pressure. For this series of measurements in emphysematous lungs, mean (SD) initial pressure was 10.7 (2.6) cm H2O (n=30). For the bronchial curves it was 10.2 (2.3) cm H2O (n=15) and for the spiracle curves 11.3 (2.9) cm H2O (n=15). While this is perhaps more variation than ideal, it is evenly distributed between the two groups of observations and is unlikely to have distorted the results. Inflation pressures for the control lungs averaged 18.8 cm H2O (n=12). Curves for the bronchial route averaged 20.5 (2.8) cm H2O (n=6) and for the spiracle pathway 17.1 (3.9) cm H2O (n=6). Non‐linear regression was performed according to the equation described in the Methods section in order to obtain time constants (Tau) for the mean volume‐time curves of each lung.
Figure 22 compares volumes passively expelled from the bronchus and spiracles of lungs inflated as described above. In fig 2A2A the volumes are given as absolute values. In the control lungs (1 and 2) the rates and volumes expelled via the bronchus greatly exceeded the results via spiracles and the time constants were much shorter. In the emphysematous lungs (3–7) the absolute volume of gas expelled from the spiracles usually exceeded the rate and volume observed via the bronchus (table 22).). Table 22 also shows the mean initial airway pressure for the three curves studied and the length of time considered complete to total volume. These results varied from 26 to 47 s in the emphysematous lungs. Even so, explanted emphysematous lung airways continue to expel air (although slowly) beyond these periods. The mean length of time to total volume of the emphysematous lungs was 36 s via the bronchial route and 34 s via the spiracle(s). The mean (SD) total gas volume expelled from the emphysematous lungs at 20 s via the spiracle(s) was 194 (61)% of that via the bronchus (p=0.01, n=5).
Figure 2B2B shows the volumes normalised as a percentage of the total volume expelled. The data points are on (lungs 6 and 7) or close to (lungs 3 and 4) the line of identity for all emphysematous lungs except lung 5. Thus, in lungs 4, 6 and 7, the time constants for emptying were roughly similar for both pathways while in lung 5, which emptied faster through the bronchial tree than it did through the spiracles, the time constant for the bronchial pathway was much smaller than that for the spiracles. This was confirmed by the Tau values shown in table 33.. In the control lungs the Tau values were 9.3 and 3.9 times longer for emptying through the spiracles than through the airways. Lung 5 had the shortest Tau for emptying via the airways and the largest percentage difference between airway and spiracle Tau values for the emphysematous lungs; this lung showed an airway emptying pattern close to normal (fig 2B2B).). In the emphysematous lungs the difference between the two Tau values varied from 10% to 60% of the larger value. Figure 33 shows additional examples of flow‐volume and volume‐time curves passively expelled.
Table 44 shows the volume of gas recovered from upper and lower lobe spiracles simultaneously after full inflation and complete passive airway deflation of the emphysematous lungs. The mean volume was 1.07 litres (range 0.21–1.57). The fact that the trapped gas in the emphysematous lungs was expelled passively through the spiracles indicates that it was under positive pressure, that is, small airways close and trap gas prematurely when alveolar pressure is still positive. This gas did not communicate with the bronchial cannula when the lung was fully deflated. Table 44 also shows the recovery of trapped gas RV from five upper and five lower individual lobe spiracles: mean 0.69 litres (range 0.18–1.41), n=10. During the preliminary studies in one explanted emphysema lung, 1.49 litres of trapped gas was recovered from one spiracle; a preliminary report was published as an abstract.10
Figure 44 shows the breath by breath distribution of 3He in a slice of a control left lung (lung 1) and a slice of an emphysematous left lung (lung 6). In each panel the left hand column shows the 3He distribution for breaths 1, 3 and 5 via the bronchial tree whereas the right columns illustrate the distribution for the same breath numbers via the spiracles. In the control lungs the distribution of 3He gas was similar by both routes. This contrasts with the distribution of 3He in the explanted emphysematous lung. When ventilation occurred via the airways, most of the 3He entered the left lower lobe. The sharp line of demarcation extending toward the left and slightly downward is caused by the major fissure. Immediately above the fissure, the upper lobe remained essentially unventilated. The apex of the upper lobe received a small amount of 3He but, after five breaths, the entire upper lobe remained very poorly ventilated compared with the lower lobe. In contrast, when ventilation took place simultaneously via spiracles in both lobes, the distribution of 3He was more even. After five breaths, only regions bordering the fissure remained poorly ventilated and, even there, more 3He entered through the spiracles than through the bronchial tree. Figure 44 shows that (1) trapped gas regions accessed by spiracles tend to be large (size of segments and even lobes); (2) within them the ventilation distribution was reasonably uniform; and (3) gas was distributed via the spiracles to regions that were not as well ventilated by the bronchus. Although each emphysematous lung differed from the others in terms of regional heterogeneity, all lungs showed these three features (fig 44).). This indicates that spiracles can provide low resistance pathways for ventilatory flow to much of the emphysematous lung.
Similarly, tidal ventilation with room air using an open circuit technique via spiracles produced large areas of gas depletion that corresponded to the bright regions seen earlier on initial 3He inflation. ROI were selected near sites of spiracle placement to quantify gas depletion of specific volume. The mean ROI volume of 467 ml was depleted by an average of 55% of 3He on the first cycle. In contrast, only 9% of 3He was depleted in the ROI after a single cycle via the bronchial tree. Detailed results are shown in table 55 and fig 55.
Laennec11 described the handling of an emphysematous lung as that perceived when handling a pillow of down. Hogg et al1 suggested this sensation due to the ease with which air can be pushed from one area of an emphysematous lung to another. Thoracic surgeons are familiar with the fact that emphysematous lungs remain inflated after excision, except when the presence of a small puncture or tear in the pleura results in complete collapse. This feature can be attributed to the extensive collateral ventilation in emphysema. Can one imagine any way of destroying the delicate parenchyma of the lung without causing an increase in collateral ventilation?
Previous measurements of collateral ventilation in excised emphysematous lungs have shown that the resistance to collateral flow across an incomplete major fissure is less than the resistance to flow through the airways, whereas in normal lungs the opposite occurs.1,12 The first measurements in living patients with emphysema performed by Terry et al2 confirmed low resistance of collateral ventilatory pathways. Morrell et al3 devised an ingenious bronchoscopic method to demonstrate a functionally important correlation between increased collateral ventilation and increased oxygen tension in the peripheral lung parenchyma. When the patient (or subject) inspired heliox (79% helium, 21% oxygen), the concentration of helium distal to a blocked peripheral bronchus rose 10 times faster in patients with moderately severe emphysema than in those with healthy lungs. Compared with healthy lungs, emphysematous lungs regularly exhibit increased collateral ventilation.
Higuchi et al13 recently reported interlobar collateral ventilation in 15 of 23 explanted emphysematous lungs. The authors cannulated and ventilated the bronchus to one lobe and achieved active ventilation of a companion lobe that was not cannulated. They analysed the preoperative results of CT scans and V/Q scintigraphs in a carefully blinded manner to classify the emphysema of each lung as homogeneous or heterogeneous. Interlobar collateral ventilation was almost uniformly present in the lungs of patients with homogeneous emphysema while only 40% of patients with heterogeneous emphysema exhibited significant interlobar collateral ventilation. In an accompanying editorial, Cetti et al14 suggested that the range of anatomical changes in emphysema must be more complicated than the two categories allowed. The authors also pointed out that interlobar ventilation must be an advanced stage of collateral ventilation which is almost certainly a continuous variable in the spectrum of emphysema. Our group correlated the long range diffusion of hyperpolarised 3He to morphometric measurements of lung surface area/volume ratios in normal and emphysematous lungs by measuring the decay of spatially modulated longitudinal 3He magnetisation.15 This technique assesses collateral ventilation with a greater sensitivity than that of interlobar ventilation. We agree with Cetti et al14 that understanding collateral ventilation is important for planning bronchoscopic methods of treatment for patients with advanced emphysema.
The lungs used in the present study were typical of those from patients undergoing transplantation for emphysema at our centre (table 11).). Mean values of FEV1 of 15% and RV of 314% of predicted normal clearly demonstrate severe expiratory flow limitation with marked hyperinflation characteristic of advanced emphysema. The subjects in the present study had more severely impaired preoperative pulmonary function than those in the group studied by Morrell et al.3 Dramatically increased collateral ventilation can be safely predicted in the lungs used in the present study, but it remains to be seen whether the functional benefits observed would also be found in lungs with less severe functional abnormalities or in living patients.
The main finding of this study is that transpleural ventilation via spiracles communicates with areas of the parenchyma that do not communicate with the trachea at RV. As a result, our hypothesis that the introduction of spiracles would decrease trapped gas, increase VC and expiratory flows proved to be correct. Measured preoperatively, the mean RV in this series of patients with emphysema was 6.40 litres. We recovered 17% of this amount (1.07 litres) via transpleural spiracles after the completion of passive bronchial deflation from one lung. While the amount might seem small, it approaches one third of RV for both lungs and would be highly significant for a patient with chronic obstructive pulmonary disease.
We believe that our results shed interesting new information on the functional abnormalities of emphysema that warrants a detailed consideration of the pathophysiology. Lung mechanics have been modelled for several decades using electrical analogues. In these models, capacitors represent the elastic properties of the lung and its compliance (Cl), whereas resistors are analogous to the flow resistance of the airways. Expressed as conductances, the airway conductance (Gaw) and the spiracle conductance (Gsp) sum (Gaw + Gsp) to express the total conductance when breathing takes place through both pathways simultaneously. The time constant for emptying of the lung through the tracheobronchial tree is then given by Cl/Gaw, while that for emptying through the spiracle is Cl/Gsp. If emptying occurs through both pathways, the time constant is given by Cl/(Gaw + Gsp). Alveolar pressure (Pa) is the pressure producing flow (Pfr) and is analogous to the voltage across the resistors. Pa relative to pleural pressure (Ppl) or lung elastic recoil pressure (Pa − Ppl = Pel) is analogous to the voltage across the capacitors. When Ppl is atmospheric (as in our experiments), Pfr and Pel are identical. Furthermore, Pfr is common to both airways and spiracles and the resulting flow is the product of Pfr =Pa = Pel and the appropriate conductance. If one assumes that a patient with severe emphysema has a Gaw of 0.1 l/s/cm H2O and a Gsp of 0.3 l/s/cm H2O, then flow rates would be threefold faster through the spiracle than the airways and fourfold faster through both pathways than through the airways alone.
In one emphysematous lung (lung 7) we measured the flow‐volume relationship (fig 6A6A)) and volume‐time relationship (fig 6B6B)) during passive deflation through the airways, through both spiracles simultaneously, and through both spiracles and the airway simultaneously. Flows and volumes were greater through both spiracles and airways together than with either pathway alone. This simulates the case of a living patient breathing through both spiracles and the tracheobronchial tree. The time constants via the bronchus and the spiracles were similar at 5.8 s and 5.2 s, respectively, while the time constant emptying through all airways was 2.5 s. This result might suggest that conductance through each pathway (bronchial and spiracle) is equal. This corroborates the graphic presentation in fig 66 and fits the electrical analogy as a capacitor discharging through two resistors in parallel.
It is reasonable to assume that, during passive deflation, both the bronchial tree and the spiracles share the same lung compliance—the capacitance of the model. If so, the driving pressure for flow through both pathways is the recoil pressure of the lung; any difference in flow between the two routes must be due to differences between Gaw and Gsp. Since the time constants in most of the emphysematous lungs were very similar by both routes, Cl might have been greater when emptying through the spiracle than through the bronchial tree. This could be explained if the spiracles communicate with a greater volume of the lung parenchyma than the tracheobronchial tree.
This means that there were regions of trapped gas within the lung that communicate rapidly with the spiracles but do not communicate with open airways (or do so very slowly). As compliance is proportional to the total volume of communicating parenchyma, the lower resistance of the spiracle pathway would be counterbalanced by the higher compliance of the communicating parenchyma, so that the time constant of emptying via the spiracles could be similar to that via the airway. This would explain why more gas emptied via the spiracles than via the bronchial tree while the time course for emptying was almost identical for both pathways. The implication of this explanation is that gas trapping is not simply a phenomenon of small airways closing as RV is approached, but that the gas remains effectively trapped at nearly all lung volumes.
If these ideas are correct, the bronchial tree in emphysema does not communicate directly with all of the parenchyma except perhaps at volumes near TLC. The non‐communicating parts presumably receive most of their gas from collateral channels. However, these channels must either be sufficiently slow so that emptying through them into the bronchial tree takes a longer time than is available during an expiration, or they must be closed at the lung volumes over which the expiration takes place. As a result, gas is effectively trapped with serious adverse effects on lung function. The amount of trapped gas that can escape from these regions via artificial airways through the pleural or bronchial wall5 is substantial and might lead to clinical benefit.
The initial 3He distribution in the control lungs was focal and irregular but generally similar via both the bronchial and spiracle routes. This probably relates to the fact that the tidal volume of 300 ml was imposed on the lung through the spiracle. Being normal, the lung elastic properties were uniform. Thus, the 3He would not remain localised to a region of parenchyma close to the spiracle, but would be forced through high resistance pathways to more central airways and then back down to the parenchyma subtended by these central airways. In emphysema, on the other hand, the 3He was probably distributed by low resistance collateral channels, so there was no necessity for the gas to travel to central airways and then back down to the parenchyma. In any event, after a few breaths the 3He distribution via airways and via spiracles was not strikingly different between the control and emphysematous lungs. Abnormalities in the distribution of ventilation in emphysema occurred over large macro regions on the scale of segments or even lobes. Within these regions the distribution was relatively homogeneous. 3He distribution via spiracles tended to fill regions which were poorly ventilated by the bronchial tree even after several breaths. This further supports the evidence that the bronchial tree communicates poorly with large volumes of parenchyma that are accessed by spiracles. If breathing had taken place through both airways and spiracles simultaneously, the distribution would be similar to a superimposition of the left and right panels of fig 44.. In all instances this would have provided a more even distribution of 3He in emphysema.
The present data are in agreement with the results of Lausberg et al5 obtained by stent‐supported fenestration through airway walls directly into the lung parenchyma in a control lung and 12 explanted emphysematous lungs inflated with 10 cm H2O negative pressure in a chamber. Chamber pressure was rapidly converted to 20 cm H2O positive pressure for measurement of the forced expiratory flow‐volume curve. Forced expiratory curves in the control lung were not changed by placement of transbronchial stents but, in the emphysematous lungs, the mean (SD) FEV1 was 245 (107) ml before placement of the transbronchial stents (3 mm diameter), 447 (199) ml after three stents (n=12) and 666 (284) ml after five stents (n=6). Similarly striking increases also occurred in total FVC in emphysematous lungs. Careful analysis of forced and passive expiration from full lung inflation in healthy subjects showed no difference in the rate of flow over most VC.6 The forced curves differed only by having an earlier onset of about 0.2 s. It may seem counterintuitive that the trapped gas RV of an emphysematous lung would be reduced equally well by small openings in either the bronchi or the pleura, but the data strongly support this. If the same trapped gas can be accessed both through the pleural surface and an airway, non‐anatomical collateral channels must connect distant regions of trapped gas. It seems feasible to take advantage of this pathophysiology to develop effective treatment.
We conclude that supplementing the bronchial tree with additional parallel pathways to the lung parenchyma deserves further evaluation as a treatment for severe emphysema. Access to collateral ventilatory channels has the ability to diminish RV/TLC, increase expiratory flow rates and VC, and improve distribution of ventilation. This technique may have therapeutic potential for relief of symptoms and improvement of lung function in patients with severe chronic obstructive pulmonary disease (GOLD stage 4).
The authors thank Drs G Alexander Patterson and Bryan F Meyers for their valuable support, Kathryn Cook and Diane Toeniskoetter for their technical assistance, Dawn Schuessler for editorial assistance, Dr David S Gierada for reviewing the radiographic data, Amersham Health (now General Electric) for the loan of a hyperpolariser apparatus and Broncus Technologies Inc (Mountain View, California, USA) for technical support.
Cl - lung compliance
FEV1 - forced expiratory volume in 1 s
FVC - forced vital capacity
Gaw - airway conductance
Gsp - spiracle conductance
Pa - alveolar pressure
Pel - elastic recoil pressure
Pfr - pressure producing flow
Ppl - pleural pressure
ROI - region of interest
RV - residual volume
TLC - total lung capacity
VC - vital capacity
Partial funding for this study was provided by NIH grant R01 HL62194.
Competing interests: None.
The Institutional Review Board for human studies approved the protocol (approval number 90‐0510) and informed written consent was obtained from each subject.