Dynamic profiles of volatile organic compounds in exhaled
breath as determined by a coupled PTR-MS/GC-MS study
J King1,2, P Mochalski2,3, A Kupferthaler1,2, K Unterkofler4,2,
H Koc4,2, W Filipiak1,2, S Teschl5, H Hinterhuber6,2 and A Amann1,2,*
1
Univ.-Clinic for Anesthesia, Innsbruck Medical University, Anichstr. 35, A-6020 Innsbruck, Austria
2
Breath Research Institute, Austrian Academy of Sciences, Dammstr. 22, A-6850 Dornbirn, Austria
3
Institute of Nuclear Physics PAN, Radzikowskiego 152, PL-31342 Kraków, Poland
4
Vorarlberg University of Applied Sciences, Hochschulstr. 1, A-6850 Dornbirn, Austria
5
University of Applied Sciences Technikum Wien, Höchstädtplatz 5, A-1200 Wien, Austria
6
Department of Psychiatry, Innsbruck Medical University, Anichstr. 35, A-6020 Innsbruck, Austria
* Corresponding author: Anton Amann, Univ.-Clinic for Anesthesia, Anichstr. 35, A-6020 Innsbruck,
Austria, email: anton.amann@i-med.ac.at, anton.amann@oeaw.ac.at.
Abstract. In this phenomenological study we focus on dynamic measurements of volatile organic
compounds (VOCs) in exhaled breath during exercise conditions. An experimental setup efficiently
combining breath-by-breath analyses using proton transfer reaction mass spectrometry (PTR-MS) with data
reflecting the behaviour of major hemodynamic and respiratory parameters is presented. Furthermore, a
methodology for complementing continuous VOC profiles obtained by PTR-MS with simultaneous
SPME/GC-MS measurements is outlined. These investigations aim at evaluating the impact of breathing
patterns, cardiac output or blood pressure on the observed breath concentration and allow for the detection
and identification of several VOCs revealing characteristic rest-to-work transitions in response to variations
in ventilation or perfusion. Examples of such compounds include isoprene, methyl acetate, butane, DMS
and 2-pentanone. In particular, both isoprene and methyl acetate exhibit a drastic rise in concentration
shortly after the onset of exercise, usually by a factor of about 3 to 5 within approximately one minute of
pedalling. These specific VOCs might also be interpreted as potentially sensitive indicators for fluctuations
of blood or respiratory flow and can therefore be viewed as candidate compounds for future assessments of
hemodynamics, pulmonary function and gas exchange patterns via observed VOC behaviour.
Key words: exhaled breath analysis; volatile organic compounds (VOCs); exercise; proton transfer
reaction mass spectrometry (PTR-MS); gas chromatography mass spectrometry (GC-MS); solid phase
micro-extraction (SPME);
Abbreviations used: volatile organic compound (VOC); proton transfer reaction mass spectrometry
(PTR-MS); selected ion flow tube mass spectrometry (SIFT-MS); gas chromatography mass
spectrometry (GC-MS); solid phase micro-extraction (SPME); multiple inert gas elimination technique
(MIGET);
This article has been published in Physiological Measurement.
1
1. Introduction
Exhaled breath contains a number of blood-borne volatile organic compounds (VOCs) with great
potential for medical diagnosis and therapeutic monitoring (Miekisch et al., 2004; Amann et al., 2004;
Amann and Smith, 2005; Bajtarevic et al., 2009). These endogenous VOCs may result from normal
metabolic activity as well as from pathological disorders. Exhaled breath analysis is non-invasive, and
breath may be sampled as often as it is desirable, even under challenging conditions such as during
operations or at an intensive care unit (Pabst et al., 2007). It may also provide information on
infections, e.g., of the lungs or the sinuses, by detecting specific volatiles released by bacteria (Preti et
al., 2009). Therefore, breath analysis could be of great clinical value in the future, introducing
valuable diagnostic indices that are complementary to those gained by using more invasive methods
(Risby, 2002; Schubert et al., 2005; Amann et al., 2007).
The concentrations of certain compounds in exhaled breath during exercise may change rapidly
(Senthilmohan et al., 2000; Karl et al., 2001; King et al., 2009). Real-time investigations in this
context have mainly been based on direct mass spectrometric methods allowing breath-to-breath
resolution, such as Proton Transfer Reaction (PTR) Mass Spectrometry (Lindinger et al., 1998a;
Lindinger et al., 1998b) or Selected Ion Flow Tube (SIFT) Mass Spectrometry (Smith and Spanel,
1996; Spanel and Smith, 1996). These analytical techniques permit one to detect and quantify very
quick changes in breath composition and hence ensure an efficient tracking of possibly short-lived
variations in the acquired concentration profiles. Efforts in the context of real-time breath
measurements so far have therefore been limited to breath constituents which can be reliably measured
by these devices, such as isoprene, acetone or ammonia.
Isoprene (CAS number 78-79-5) certainly holds a distinguished status, since it can be regarded as the
prototype of an exhaled breath VOC exhibiting pronounced rest-to-work transitions (Karl et al., 2001;
Turner et al., 2006; King et al., 2009). We recently demonstrated that end-tidal isoprene abruptly
increases during moderate workload ergometer challenges at 75 W, reaching a peak value within about
one minute of pedalling. This maximum can differ from the end-tidal steady state concentration at rest
by a factor of up to 4 (King et al., 2009). Since endogenous isoprene synthesis has mainly been
attributed to pathways with much larger time constants (Stone et al., 1993), we do not expect that the
aforementioned rise in isoprene concentration is due to an increased production rate in the body, but
rather due to changes in pulmonary function or changes in hemodynamics.
With this illustrative example in mind, we may thus expect that the sampling of exhaled breath, even
under resting conditions, can strongly be influenced by specific physiological parameters (Cope et al.,
2004). Hence, the impact of breathing rate, breathing volume, cardiac output or blood pressure on the
concentration dynamics of specific compounds in exhaled breath generally merits further
investigation. A paradigmatic example within this framework is the small inorganic molecule nitric
2
oxide (NO) (Kharitonov et al., 1997; Dweik et al., 1998; Bush, 2000; Gustafsson, 2005; Horvath et
al., 2003). NO arises in almost every human organ, has a short half-life and may change its
concentration quickly. It is also produced in the lungs, the nasal cavity and the sinuses. In the latter it
acts by its bactericidal effect (Bush, 2000). The concentration in the nasal cavity and the paranasal
sinuses is usually much higher than in the lungs, and actually increases in concentration within a few
seconds during humming (Lundberg et al., 2004; Maniscalco et al., 2004). The use of NO for the
therapeutic monitoring of asthma relies on the amount released in the airways. Hence, appropriate
measurements of airway released NO are important for its clinical use and therefore careful sampling
of breath under controlled conditions is necessary. This led to joint guidelines of the American
Thoracic Society (ATS) and the European Respiratory Society (ERS) for the protocol to be used for
NO measurements in exhaled breath ((ATS), 1999; (ATS/ERS), 2005). We expect that a careful
choice of conditions and sampling protocol will be important not only for NO, but also for various
other volatile molecular species.
Within this context, the primary motivation for the present work was to scan exhaled breath actively
for trace gases showing pronounced changes in response to variations in ventilation and perfusion.
While on the one hand such compounds would evidently require special attention regarding their
sampling procedure, they can also be thought of as sensitive indicators for fluctuations in
respiratory/hemodynamic flow. In the same spirit, they might therefore serve as candidate compounds
for assessing pulmonary gas exchange patterns via observed VOC profiles. Consequently, a secondary
aim also was to supplement and support continuing efforts to base MIGET (Multiple Inert Gas
Elimination Technique (Wagner, 2008; Wagner et al., 1974)) on endogenous VOCs rather than
exogenously administered gases, thereby circumventing invasive infusion and improving patient
compliance (Anderson and Hlastala, 2010). Furthermore, our measurements are intended to place
previous measurements of breath isoprene and acetone in a broader context by comparing their
dynamic behaviour during distinct physiological states with synchronized profiles of VOCs expected
to show similar exhalation kinetics.
2. Methods
2.1. Sampling procedures
Recently, an experimental setup efficiently combining PTR-MS measurements with continuous data
streams reflecting a series of hemodynamic and respiratory factors was developed in our group (King
et al., 2009). This setup serves to assess the behaviour of exhaled breath components in conjunction
with decisive physiological driving forces during rest and ergometer-induced workload schemes in
real-time. While its main purpose is to monitor specific, predefined molecular species, the
identification problem stated above can only be tackled with alternative analytical techniques, giving
detailed information on the composition of the exhaled breath sample. Gas Chromatography Mass
3
Spectrometry (GC-MS) coupled with solid phase micro-extraction (SPME) as a pre-concentration
method can be regarded as gold standard within this framework (Amorim and de, 2007; Bajtarevic et
al., 2009; Ligor et al., 2008; Pawliszyn, 1997; Schubert et al., 2005; Miekisch et al., 2008; Schubert et
al., 2003; Ligor et al., 2009). SPME/GC-MS represents a good trade-off between high resolution of
individual breath components with low detection limits and rapid sampling. The main advantages of
SPME are its ease of operation and the small amounts of sample gas – usually between 10 and 20 ml –
required to perform extraction. An additional benefit from the usage of SPME/GC-MS techniques is
the possibility to detect and quantify compounds that cannot be measured by the PTR-MS (e.g.,
alkanes). A suitable choice of specimen storage vessels guarantees high recoveries of the target
compounds and ensures reliable GC-MS analyses of breath samples taken within a relatively short
period of time. In the following, a methodology for complementing continuous VOC profiles obtained
by PTR-MS with simultaneous SPME/GC-MS measurements under workload conditions is developed.
A detailed description of the entire experimental setup used for acquiring hemodynamic and
respiratory data in conjunction with PTR-MS variables is given elsewhere (King et al., 2009). Here we
will only discuss the parts that are relevant for the analysis of exhaled breath samples by GC-MS. The
test subject freely inhales/exhales through a flow transducer mouthpiece, which is connected to a
silicone head mask covering mouth and nose, see figure1.
Figure 1
From the mouthpiece, gas samples are directed to the PTR-MS via a heated Teflon sampling line.
Moreover, respiratory flow is obtained by means of a differential pressure sensor as explained in Ref.
(King et al., 2009). Breath samples for the GC-MS analyses were taken using a 20 ml gas-tight glass
syringe (Roth, Germany) equipped with a replaceable needle. For sampling purposes an additional
rubber septum (Supelco, Canada) was installed in the wall of the flow transducer mouthpiece
approximately 3 cm from the lips. Sampling was achieved manually by piercing the septum and
drawing a volume of 18 ml during one single end-tidal exhalation segment. Care was taken to ensure
that the needle tip is located in the centre of the axial mainstream. In order to avoid possible losses of
hydrophilic compounds due to condensation, needle and syringe were preheated to about 60 °C shortly
before the sampling procedure.
Filling of the syringe was timed according to the automatic real-time procedure for the selective
sampling from specific exhalation phases as described in Ref. (King et al., 2009). Adequate
algorithmic processing of measured respiratory flow allows for a reliable breath-by-breath detection of
each end-tidal segment, with its start and end being marked by an acoustic signal. In order to prevent
gas samples from being diluted or contaminated with (fresh) room air at the onset of the next
inhalation, the entire sampling process including pressure equilibration within the syringe has to be
completed within this time window. Test subjects were therefore asked to slightly prolong their
4
exhalation to about 4 s in the respective breath cycle. Such a procedure extended the length of the endtidal phase and turned out to be satisfactory for all test subjects. Some bias might be introduced by this
protocol due to the fact that VOC breath concentrations have been demonstrated to increase with the
duration of the end-tidal phase (Anderson et al., 2003; O'Hara et al., 2008). However, after an
examination of the PTR/GC-MS overlays for acetone and isoprene associated with preliminary single
expirograms, we decided that the corresponding error will only have a minor impact on quantification.
In particular, since the extraction of PTR-MS gas samples is triggered by the same detection
mechanism as described above, applying the aforementioned sampling protocol ensures that both
probes are drawn from the same portion of exhaled breath.
Immediately after sampling the syringe content was injected into an evacuated SPME vial (20 ml in
volume, Gerstel, Germany) sealed with a 1.3 mm butyl/PTFE septum (Macherey-Nagel, Germany).
Since the SPME vials also served as storage containers, the type of septa was carefully selected with
respect to background and recovery of the compounds of interest. The applied material guaranteed
recoveries better than 90% within the first 12 hours of storage. Finally, pressure in the vial was
balanced with high-purity nitrogen (of quality 6.0, i.e., with a purity of 99.9999 %).
2.2. GC-MS analysis
The gas chromatographic analyses were performed using an Agilent Techn. (USA) type 7890 gas
chromatograph equipped with a mass selective detector (MSD) (type 5975C, Agilent, USA). SPME
was performed automatically (auto sampler MPS2, Gerstel, Germany) by inserting the SPME fibre
coated with 75 µm CAR-PDMS (Supelco, Canada) into the vials and exposing the fibre to the sample
for 10 minutes. The sample temperature during the extraction was kept at 40 °C to avoid the
condensation of water vapour. Subsequently, the fibre was immediately introduced into the injector of
the gas chromatograph, with thermal desorption at 290 °C in a splitless mode (1 min). The fibre was
conditioned at 290 °C for 15 minutes prior to each analysis.
Analytes under study were separated using a PoraBond Q column (25 m x 0.32 mm, film thickness 5
µm, Varian USA) working in a constant flow mode (1.7 ml/min). The column temperature program
was chosen as follows: 90 °C for 7 min, increase to 140 °C at a rate of 10 °C/min, constant
temperature of 140 °C for 7 min, increase to 260 °C at a rate of 15 °C/min and 260 °C for 6 min. The
mass spectrometer worked in a combined SCAN/SIM mode. The SCAN, with an associated range set
from m/z 35 to m/z 200, was used for the identification of potential target compounds as well as for
the quantification of isoprene and acetone. Additionally, major study compounds as discussed below
were quantified using SIM (selective ion monitoring mode), with the corresponding m/z ratios and
dwell times being presented in table 1.
Table 1
5
Calibration graphs and standard retention times were created on the basis of analyses of calibration
mixtures prepared from pure compounds. Isoprene (99.5 %), methyl acetate (99.5%) and butane (15
ppm C1-C6 hydrocarbon standard) were obtained from Sigma-Aldrich (USA), dimethyl sulfide (99%)
from Fluka (USA), 2-pentanone (97%) from Acros Organics (Belgium) and acetone (99.5 %) was
purchased from Merck (Germany). A primary gas standard was prepared in a 1-Liter glass bulb
(Supelco, Canada) by injecting 0.5 to 2 µl (depending on the target concentration) of pure compound
into the evacuated bulb. Next, the bulb was heated to 80 °C for 15 minutes in order to ensure
evaporation and subsequently balanced with high-purity nitrogen (6.0 – 99.9999%). The primary
standard was used to prepare six calibration mixtures with concentrations ranging from 20 ppb to 1000
ppb in case of acetone and isoprene, and 0.1 to 20 ppb for the other species. This was accomplished by
transferring 0.05 to 1 ml of primary standard into 3-Liter Tedlar bags (SKC Inc., USA) filled in
advance with 1500 ml of nitrogen. Final humid calibration mixtures were created in the SPME vials.
For this purpose, vials were evacuated with a membrane pump (Vacuubrand, Germany) and heated to
45 °C for 2 minutes. Next, an amount of 0.8 µl of distilled water – corresponding to the maximal water
content in 18 ml of breath (100 % relative humidity at 37 °C) – was injected. After 1 minute (the time
necessary for complete water evaporation), an appropriate volume of dry mixtures was introduced into
the vials. During the whole process the vial temperature was maintained at 45 °C to avoid
condensation.
Validation parameters were estimated using the calibration graphs. Limits of detection, defined as a
signal-to-noise ratio of 3:1 are presented in table 1. The system response was found to be linear with
correlation coefficients ranging from 0.996 to 0.999. The relative standard deviations (RSDs) were
calculated based on consecutive analyses of five separate breath samples taken within 1 minute from a
single volunteer who had been resting for 15 minutes. Such a procedure was necessary to include the
influence of manual sampling on the RSD values. The estimated RSDs are summarized in table 1.
2.3. Test subjects and protocols
A cohort of seven healthy normal volunteers (4 male, 26-28 ys.; 3 female 21-28 ys.; 2 smokers) were
recruited to participate in a single moderate exercise ergometer challenge consisting of an initial
resting phase of 5 to 10 minutes, followed by a constant workload segment of 75 W for 15 minutes.
The regime ends with a further resting phase of 5 minutes. No test subject reported any prescribed
medication or drug intake. The study was approved by the Ethics Commission of Innsbruck Medical
University.
The test subjects were all measured in the morning with an empty stomach. The only exception was
drinking of water. Smokers were asked to refrain from smoking on the day of measurement.
Volunteers were required to rest at least 15 minutes prior to analysis. Within this time, they were given
6
general information regarding the experimental protocol and received some training in order to
reliably provide a triggered exhalation as discussed in the previous sections. Additional
instrumentation and protocols closely followed the general procedure reported in Ref. (King et al.,
2009).
Regarding real-time VOC analysis, we focused on two major exhaled breath constituents: acetone and
isoprene, which can be measured by PTR-MS in their protonated forms at mass-to-charge ratios 59
and 69, respectively (Arendacká et al., 2008; Schwarz et al., 2009b). For a series of single experiments
we also included m/z 63 (tentatively DMS) as well as m/z 75 (tentatively methyl acetate). For
purposes of normalization and quality control we additionally monitor m/z 21 (isotopologue of the
primary hydronium ions) and m/z 37 (first monohydrate cluster). Further details on subsequent
quantification are given in (Schwarz et al., 2009a). Based on our knowledge of isoprene and acetone
behaviour, representative time instants for drawing the GC-MS samples were defined as follows: one
sample was extracted during resting conditions as soon as the test subject had accustomed to the
experimental situation and cardiac output as well as alveolar ventilation had stabilized sufficiently,
i.e., about 2 minutes after the start of our protocol. Subsequent samples were drawn after 0.5, 1, 3, 5,
10 and 15 minutes had passed since the onset of exercise. Additionally, for the purpose of background
correction, a room air sample was taken just before the experiment.
3. Results and discussion
On the basis of the underlying SPME-GCMS analysis method discussed before, five compounds were
found to substantially increase/decrease in response to the workload sequence: isoprene, butane,
methyl acetate, DMS and 2-pentanone. Quantitative effects for these compounds are summarized in
figure 2 as well as in table 2.
Figure 2
For comparative reasons, only relative changes are presented, i.e., all individual profiles have been
normalized to the respective initial steady state value. The measured ventilation-perfusion ratio reflects
the applied workload sequence starting at time zero.
Table 2
Major hemodynamic and respiratory variables generally exhibit a very consistent behaviour among all
test subjects (King et al., 2009). At the onset of exercise, cardiac output rapidly increases from a mean
resting value of approx. 5 l/min at rest to a constant plateau of about 12 l/min during constant
workload of 75 W. Simultaneously, alveolar ventilation shows a monotonic rest-to-work transition
7
from 5-10 l/min to a steady state level of approx. 25-30 l/min, thereby increasing the average
ventilation-perfusion-ratio by a factor of ~ 2.5, see figure 2.
Representative PTR-MS/GC-MS results for one single study subject are given in figure 3, displaying
continuous end-tidal concentration profiles of isoprene, acetone and methyl acetate as determined by
PTR-MS in comparison with discrete measurements obtained from our GC-MS analysis. Error bars
result from taking two times the associated RSD value as given in table 1. In particular, the good
agreement between both methods for isoprene and acetone can be seen as a cross-validation of
phenomenological results related to both compounds which have been published previously (Karl et
al., 2001; King et al., 2009).
Figure 3
For all test subjects, individual isoprene levels in breath obtained prior to the workload sequence
varied within a range of 58 to 163 ppb, the median concentration being 107 ppb (cf., also Ref. (Kushch
et al., 2008)). In accordance with earlier findings, end-tidal isoprene concentration abruptly increases
by a factor of ~ 3 to 4 within the first minute of the applied workload scenario, followed by a gradual
decline back to initial (resting) levels within approximately 15 minutes of exercise. Excellent
agreement between isoprene concentrations acquired by PTR-MS and GC-MS throughout all
measurements reconfirms the extraction quality of our manually obtained samples. On the basis of this
observation it is deduced that the quantities of additional compounds in these samples are indeed
representative for the corresponding end-tidal levels. In this sense, isoprene acts as a practicable
control value that can potentially be used for detecting possible error sources and losses in the manual
sampling regime.
The marked rise of isoprene at the onset of exercise has mainly been attributed to its low affinity for
blood (dimensionless Ostwald blood:gas partition coefficient at body temperature: 0.75 (Filser et al.,
1996)). The classical alveolar gas exchange theory due to Farhi predicts a significant influence of
ventilation and perfusion on the observed exhaled breath concentration for compounds with small
solubility (Farhi, 1967; Farhi and Yokoyama, 1967), see also (King et al., 2009) for a derivation. In
view of the previously described isoprene exhalation kinetics, natural candidates for preliminary
studies of VOC behaviour under workload conditions hence are substances with similar physicochemical behaviour, e.g., the family of hydrocarbons. Within the ensemble of volunteers investigated,
our main focus was on butane, as the respective alveolar gradients (i.e., the difference between endtidal levels and background values) were generally high enough to allow for a reliable quantification.
Butane appeared in the breath of five volunteers with resting levels ranging from 0.6 to 6.5 ppb
(median: 2.4 ppb). Blood-borne butane is considered to originate from protein oxidation and/or
bacteria production in the colon (Kharitonov and Barnes, 2002; Miekisch et al., 2004) and is
particularly interesting due its functional comparability with isoprene. Indeed, the major factors
8
anticipated to affect pulmonary gas exchange show substantial similarity, see table 3 as well as Ref.
(Meulenberg and Vijverberg, 2000).
Table 3
According to these values, by Graham's law, diffusivity (governing the passage through the tissue
interfaces separating the respiratory microvasculature from the alveolar space) is expected to be
roughly similar for both compounds (West, 2005). Moreover, the presented affinities for blood
indicate that supply and removal via the pulmonary circulation will be of comparable order.
Despite this agreement, breath concentrations of butane and isoprene exhibit an entirely different
qualitative response among the ensemble of volunteers investigated: the behaviour of butane at the
onset of exercise resembles the trend as predicted by the classical Farhi equation (i.e., a decrease with
higher ventilation-perfusion ratios, see figure 2), whereas the behaviour of isoprene does not.
Consequently, from the viewpoint of endogenous MIGET, isoprene (in contrast to butane) appears to
be of limited suitability as a potential test gas. The above-mentioned visual discrepancy might be
assessed in a more formal manner by employing a Wilcoxon signed rank test (Wilcoxon, 1945) at each
discrete time instant greater than zero. It tests the null hypothesis that the differences between the
respective normalized butane and isoprene levels are drawn from a continuous, symmetric distribution
with zero median. Using a 10% confidence level, this null hypothesis might be rejected at all time
instants greater than zero with a maximum p-value of 0.0625.
In a series of separate experiments we exclusively focused on the simultaneous dynamics of breath
isoprene and butane in response to changes in ventilation and perfusion. Typical results referring to
one single test subject are given in figure 4. Here, in addition to the exercise protocol discussed before,
the ventilation-perfusion ratio is altered by a sudden change in body posture from semi-supine to
supine position (corresponding to the time interval between 10 and 20 min).
Figure 4
As has already been shown in Ref. (King et al., 2009), such a manoeuvre will result in only minor
changes of alveolar ventilation, while the associated rise in cardiac output (mainly due to an increase
in stroke volume) can be utilized for assessing the individual contribution of pulmonary blood flow on
the alveolar gas exchange process. Both isoprene and butane concentrations in end-tidal breath
approach an apparently stable steady state in supine position that is about a factor of 1.5 higher
compared to the resting level. This is the qualitative behaviour expected from the Farhi equation.
Particularly, a markedly peak shaped response of isoprene as in the case of ergometer scenarios could
not be observed.
9
Combining the above-mentioned findings it might thus be inferred that some isoprene-specific
(release) mechanism has to be taken into account for capturing the exhalation kinetics of this
important compound at the onset of physical exercise. The isoprene sources and exact stimuli for such
a workload-induced process, however, remain an object of speculation. Potential candidates for
instance include the working muscle compartment, which receives disproportionately high fractions of
cardiac output during an ergometer challenge and moreover undergoes a rapid change in metabolic
activity from which isoprene might be derived. Another alternative, which might be compared to the
flow-induced release of NO in the cardiovascular system, is an increased diffusion from potential
storage sites of lipophilic compounds such as the endothelial lining or muscle cells (Miekisch et al.,
2001).
A notable rise in concentration was also detected for methyl acetate. The possible endogenous origins
of this ester have not yet been explored. However, it has recently been demonstrated that methyl
acetate is released by human bronchial epithelial primary cells in vitro (Filipiak et al., 2010).
Exogenous uptake can result from its widespread use as a solvent as well as from different types of
food (e.g., coffee (Lindinger et al., 1998b)). This compound was detected in the breath of all
volunteers at concentrations of 0.04 to 3.2 ppb prior to the workload (median: 0.5 ppb). In case of all
individuals we observed an abrupt increase in concentration, usually by a factor of about 2 to 5 within
approximately one minute of pedalling (see also figure 3). Subsequently, either a new plateau was
reached or concentrations slightly decreased with the duration of exercise.
Dimethyl sulfide (DMS) appeared in the breath of all volunteers at concentrations ranging from 0.8 to
3.6 ppb during rest (median: 2.7 ppb) and was found to increase during exercise in four cases. This
rise in concentration, however, was not so pronounced like in the case of isoprene or methyl acetate
and amounted to 20 – 60 %. Despite the relatively small response to exercise, DMS remains a very
interesting compound in our study. DMS is a relatively stable volatile sulphur compound (VSC)
present in human breath. Endogenous production has been ascribed to an incomplete metabolism of
sulphur-containing amino acids, methionine and cysteine, in the transamination pathway (Miekisch et
al., 2004). DMS is formed by the enzyme thiol S-methyltransferase via the methylation of H2S and
methyl mercaptane (Tangerman, 2009). This process can be considered as a detoxification mechanism,
removing toxic sulphur species from the tissues. DMS is the main cause of extra-oral halitosis
(Tangerman, 2009; Tangerman and Winkel, 2007) and elevated breath levels were observed in patients
with cirrhosis, hepatitis and hypermethioninemia.
Breath concentrations of 2-pentanone during rest were spread around a median value of 0.23 ppb and
tended to approach a new steady state level during constant load exercise that was 10 – 60 % higher
than the initial value prior to workload, see figure 2. This behaviour closely resembles the profile of
acetone (King et al., 2009) (see also figure 3), which is not unexpected due to the functional
similarities of these two ketones. The endogenous source of 2-pentanone is still disputed. Similarly
like methyl acetate, 2-pentanone could be shown to be produced by human bronchial epithelial
10
primary cells in vitro (Filipiak et al., 2010). Elevated breath levels have been associated with fasting
(Statheropoulos et al., 2006) and liver diseases (Van den Velde et al., 2008).
The concentration profiles of compounds identified by GC-MS analysis might be reconfirmed by
monitoring their expected PTR-MS signal (i.e., count rate at a mass-to-charge ratio equal to the
respective molecular weight + 1). Such an approach is limited to species that are protonated in PTRMS, i.e., which have higher proton affinities than water (166.5 kcal/mol). Representative results for
methyl acetate (MW 74) are shown in figure 3. Here, PTR-MS count rates were converted to pseudo
concentrations (Schwarz et al., 2009a) and scaled to match the initial GC-MS results at the start of
measurement. For correction purposes, room air levels were subtracted from the corresponding signals
before conversion. Apart from methyl acetate, propionic acid and butanol appear at m/z 75 in PTR-MS
measurements. The agreement between PTR-MS and GC-MS supports the view that in the framework
of breath gas analysis of normal volunteers a major part of PTR-MS signal variability at m/z 75 can be
attributed to the dynamics of methyl acetate.
4. Conclusion
In general, we believe that several valuable pieces of information can be distilled from the
phenomenological study of breath VOC behaviour during distinct physiological states.
As has been indicated in the introduction, rather specific but yet very promising fields of application
are pulmonary function tests based on the joint exhalation kinetics of an ensemble of pre-selected
blood-borne inert gases. Within this context, a major focus lies on developing a less invasive extension
of standard MIGET methodology, which aims at avoiding the exogenous infusion of test gases and
replacing them with endogenous compounds originating from normal metabolic activity. The success
of such an approach will primarily depend on the extent to which possible test compounds proposed
for this purpose can be considered to follow the underlying Farhi description. For instance, it has
recently been pointed out that highly water soluble VOCs (including the standard MIGET test gas
acetone) will not represent an adequate choice within this framework since the associated end-tidal
concentrations can be expected to differ drastically from the respective alveolar levels (Anderson and
Hlastala, 2010). This is due to substantial interactions of such compounds with the water-like mucus
layer lining the conducting airways, commonly referred to as wash-in/wash-out effect (Anderson et
al., 2003; Anderson et al., 2006). As a phenomenological consequence of this fact, it has been
demonstrated that end-tidal exhalation dynamics of highly water soluble compounds in response to
distinct experimental conditions (e.g., exercise, hyperventilation or isothermal rebreathing) will
substantially depart from the trend predicted by the Farhi equation (King et al., 2009; O'Hara et al.,
2008). For instance, acetone concentrations in end-tidal breath tend to increase in response to
increased ventilation (see, e.g., figure 3), rather than showing a roughly stable behaviour as anticipated
from the classical theory by Farhi.
11
Analogous tests for low (blood) soluble compounds are straightforward and can be used for directly
revealing deviations from the assumptions underlying MIGET methodology (see also the comparison
between isoprene and butane presented above). In this sense, profiles of VOCs acquired in the course
of dynamic experiments offer the possibility to actively scan for breath constituents that qualify as
(endogenous) MIGET gases as well as to assess the adequacy of potential test compounds.
In the same spirit, we stress the fact that investigations covering dynamic VOC behaviour are a
general and necessary tool for gaining novel quantitative perspectives on the inherent variability of
VOC concentrations stemming from (short-term) physiological changes. This knowledge is of utmost
importance for everyday measurement practice in exhaled breath analysis, as slightly changing
experimental conditions (regarding, e.g., body posture, breathing patterns, etc.) or even premeasurement history (stress, physical exhaustion) can have a substantial impact on the observed breath
concentration (Cope et al., 2004). It moreover will be helpful for devising appropriate sampling
regimes as well as for comparing results obtained under different experimental protocols (Cope et al.,
2004; Miekisch et al., 2008; O'Hara et al., 2008).
Even though instruments for real-time breath analysis can be seen as canonical choice for the parallel
assessment of physiological (e.g., hemodynamic and respiratory) factors and VOC time response,
explorative measurements within this framework necessarily require a combination with GC-MS,
ensuring an unambiguous identification of the detected compounds. Here, we presented a
methodology for direct manual breath sampling and subsequent SPME/GC-MS analysis during free
tidal breathing under dynamic conditions. Moreover, we investigated a limited list of compounds
revealing interesting rest-to-work transitions in response to moderate exercise. Continuous PTR-MS
isoprene profiles were used as reliable control for confirming the quality of the manually extracted
samples. Further efforts will need to take into account a larger variety of trace gases as well as
experimental conditions (e.g., isothermal rebreathing (Ohlsson et al., 1990)). In this sense, we
recognize that our data only reflect very preliminary results that hopefully will guide future
investigations in this framework.
Acknowledgements
Julian King is a recipient of a DOC fellowship at the Breath Research Institute of the Austrian
Academy of Sciences. The research leading to these results has received funding from the European
Community’s Seventh Framework Programme (FP7/2007-13) under grant agreement No. 217967
(www.sgl-eu.org). We greatly appreciate funding from the Austrian Federal Ministry for Transport,
Innovation and Technology (BMVIT/BMWA, project 818803, KIRAS). We greatly appreciate the
generous support of the government of Vorarlberg and its governor Landeshauptmann Dr. Herbert
Sausgruber.
12
FIGURES
Figure 1: Sketch of the flow transducer mouthpiece from which end-tidal samples are manually
extracted for subsequent SPME/GC-MS analysis
Figure 2: Average relative changes of several VOC concentrations (determined by SPME/GC-MS)
during constant load exercise of 75 W as compared to their resting levels (t = 0). The graphs presented
here correspond to the median values among all seven volunteers investigated. In particular, the
concentration profiles were all normalized to the initial resting values Crest prior to averaging.
13
Figure 3: Simultaneous extraction of end-tidal VOC profiles by PTR-MS (continuous signal) and
discrete SPME/GC-MS measurements. Error bars for the latter result from taking two times the
associated relative standard deviation as given in table 1. Data refer to one single volunteer during a
constant workload protocol of 75 W after an initial resting phase of 5 minutes.
14
Figure 4: SPME/GC-MS profile of butane (λb:a = 0.41; 1 nmol/l approximately equals 25 ppb at
ambient conditions) compared with the synchronized and scaled PTR-MS response for isoprene (λb:a =
0.75). The experimental protocol is as follows: 0-10 min rest; 10-20 min supine position; 20-30 min
rest; 30-45 min exercise at 75 W; 45-49 min rest. The dotted light grey line represents an eye guide for
the expected alveolar concentration of butane as predicted by the Farhi equation (postulating a
constant mixed venous blood concentration of 0.7 nmol/l).
15
TABLES
Compound
CAS No.
Retention time
[min]
m/z (SIM)
Dwell time
[ms]
RSD
[%]
LOD
[ppb]
Isoprene
78-79-5
13.39
-
-
2.1
1.4
Acetone
67-64-1
10.89
-
-
2.6
2.5
DMS
75-18-3
11.54
47, 61, 62
60
5.5
0.05
Methyl acetate
79-20-9
12.28
43, 74
60
4.8
0.04
Butane
106-97-8
8.68
43
180
5.8
0.2
2-pentanone
107-87-9
22.72
86
60
3.8
0.04
Table 1: Major study compounds together with relevant methodological data. Retention times used for
confirming substance identifications based on spectral data are obtained by means of calibration
mixtures. Dwell times refer to the SIM mode.
MW
Blood:gas partition
coefficient λb:a
Octanol:water partition
coefficient log(Kow)
Isoprene
68
0.75 (Filser et al.,
1996; Karl et al.,
2001)
2.42 (Howard and Meylan,
1997)
Butane
58
0.41* (Liu
1994)
2.89 (Sangster, 1997)
et
al.,
Table 3: Functional similarities between isoprene and butane with respect to alveolar gas exchange.
*(refers to rat blood)
16
Butane [ppb]
0.5
1
3
Vol. No. / time
1
2
3
4
5
6
7
0
n.d.
5.94
n.d.
6.47
0.6
1.24
2.43
Vol. No. / time
1
2
3
4
5
6
7
Dime thyl sulfide
0
0.5
1
2.69 3.55 3.48
0.79 0.69 0.82
1.52 1.78 1.92
3.56 5.44 6.05
1.38 1.52 1.5
2.79 4.59 4.52
3.28 3.38 2.93
Vol. No. / time
1
2
3
4
5
6
7
0
163
82
138
107
78
58
154
3.93 3.61
3.43 3.45
3.42
3.7
8.57 7.83
0.45 0.4
0.98 0.76
2.73 1.43
2.45 1.68
0.13 0.23
0.42 0.43
0.52 0.6
2.02
0.29
0.5
0.79
1.74
0.36
0.45
0.71
Vol. No. / time
1
2
3
4
5
6
7
[ppb]
3
2.83
0.81
1.73
4.73
1.25
3.78
2.54
5
2.75
0.71
1.74
3.54
1.2
3.26
2.26
10
2.37
0.76
1.54
3.18
1.18
2.77
1.94
15
2.18
0.77
1.46
3.02
1.13
2.69
2.08
Vol. No. / time
1
2
3
4
5
6
7
5
240
79
176
88
79
71
148
10
148
59
130
79
63
47
102
15
124
52
81
67
50
42
79
Isopre ne [ppb]
0.5
1
3
532 669 324
122 129
98
260 342 200
317 441 159
192 243 119
209 212 104
359 467 229
5
10
15
Me thyl ace tate [ppb]
0
0.5
1
3
1.66 8.02 9.27 7.7
0.53 1.13 1.61 1.31
3.23 6.5 8.1 6.99
0.22 0.76 1.03 1.02
0.04 0.48 0.62 0.59
0.81 3.47 3.54 2.86
0.36 1.25 1.65 1.63
5
6.59
1.28
6.88
0.82
0.49
2.3
1.29
10
4.57
1.09
5.56
0.93
0.44
1.44
0.92
15
3.31
0.9
3.86
0.96
0.37
1.05
0.65
2-pe ntanone [ppb]
0
0.5
1
3
0.26 0.33 0.35 0.32
0.19 0.18 0.21 0.18
0.23 0.2 0.21 0.22
0.21 0.25 0.28 0.3
0.11 0.15 0.16 0.16
0.25 0.34 0.34 0.33
0.28 0.34 0.39 0.42
5
0.31
0.19
0.23
0.26
0.15
0.31
0.41
10
0.3
0.18
0.23
0.29
0.15
0.33
0.42
15
0.27
0.19
0.22
0.31
0.15
0.34
0.44
Table 2: GC-MS quantification results for the seven volunteers investigated. Time instants correspond to exercise duration in minutes (with time zero referring
to resting levels in end-tidal breath).
17
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