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1 Dept of Pneumology, Allergology and Sleep Medicine, University Witten/Herdecke, and 2 Medizintechnik für Arzt und Patient (MAP), Martinsried, Germany
CORRESPONDENCE: W.J. Randerath, Klinik Ambrock, Dept of Pneumology, Allergology and Sleep Medicine, Ambrocker Weg 60, 58091, Hagen, Germany. Fax: 49 2331974209. E-mail: winfried.randerath@dland.de
Keywords: apnoea, breath tests, humidity, positive pressure ventilation, respiratory system
Received: August 1, 2001
Accepted February 18, 2002
This study was supported by the MAP, Martinsried, Germany.
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Abstract |
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Humidity and temperature were determined separately for the respiratory phases, without humidification, with cold passover and heated humidifiers in 10 healthy subjects. Humidity was measured with a capacitive hygrometer, temperature with a "Type K" thermosensor, and impedance of the total respiratory system with impulse oscillometry.
The relative humidity (rH) of the inspired air (mean±sd) increased significantly from 24.0±9.1% rH (34.8±1.0°C, no humidifier) to 34.5±10.1% rH (34.6±1.0°C) under cold humidification, and to 53.9±13.2% rH (35.0±1.1°C) under heated humidification. With heated humidification, water loss was reduced by 38% compared to cold humidification. The impedance increased from 5.7±1.8 cmH2O·L·s–1 (no humidifier) to 6.7±1.8 cmH2O·L·s–1 (heated humidifier).
The authors conclude that the use of a heated humidifier during continuous positive airway pressure appreciably increases the relative humidity of the inspired air and reduces the water loss during respiration.
The use of humidifiers is recommended for the treatment of local side-effects associated with nasal continuous positive airway pressure (nCPAP) therapy to increase the humidity and temperature of the respired air 1–4. To date, however, only humidity data averaged over a lengthy period of time have been reported 5, 6. Humidifiers are thought to exert an effect by changing the inspired air. Separate measurement of humidity during inspiration and expiration appears to be particularly useful as, owing to the high expiratory humidity, averaging of humidity figures over lengthy periods cannot completely reveal the effect of humidification on inspired air. Therefore, the present authors studied the influence of humidification under continuous positive airway pressure (CPAP) using sensors with a small dead time, making it possible to determine the rapid changes in humidity in the alternation of inspiration and expiration. The authors aimed to compare the relative humidity (Hrel) of the inspired air between cold passover and heated humidifiers, and to measure the water loss of respiration under CPAP treatment. A secondary aim was to evaluate the impedance (Z) of the total respiratory system under the various humidification systems.
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Methods |
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Design
The subjects were examined in randomised order in the supine position, at a CPAP pressure of 10 cmH2O and in the wake state over three phases (without humidification (no H, 32.8±10.8 min), with cold passover humidification (cold H, 36.4±7.5 min), and with heated humidification (heated H, 54.3±12.5 min)) of 
20 min of stable breathing each. The ambient temperature was 22.0±0.2°C and Hrel 29.6±2.3%.
Materials
The subjects were connected via a nose mask (Special®, Gold Seal®, Respironics Inc., Pittsburgh, USA) to a CPAP device (fig. 1
). This device incorporates a surface contact humidifier, which was used for cold H (water temperature
ambient temperature) or heated H (>35°C) (CPAP with integrated humidifier: Max II®, Medizintechnik für Arzt und Patient, Martinsried, Germany). The humidity of the air was measured with a capacitive hygrometer (custom-made, University of Göttingen, Germany, range for 5–99% rH 8) between the mask and Y-adapter. This system incorporates a layer of plastic polymer, between two electrodes which, depending on the humidity, can adsorb water molecules. These bring about a change in the capacity, which is correlated with the humidity. The sensor is heated to prevent water condensation. The capacitive hygrometer has only a very low dead time, enabling changes in the humidity between inspired and expired air to be measured (time constant 0.23 s at 40°C, 0.18 s at 50°C and 0.14 s at 60°C). The nonlinearity of the sensor was ±0.1 mg·L–1. The device was calibrated using a mirror-type dew point hygrometer (maximal error after calibration ±0.6 mg·L–1) 8. Temperature was measured with a "Type K" thermosensor (range –200–1,300°C, tolerance 0.3%) in the mask and a second thermosensor in the capacitive hygrometer. The authors applied the following data sets, recorded for 
1 min preceding each measurement of Z of the total respiratory system, for the evaluation of humidity and temperature. Expiration: 632 data sets under no H, 430 under cold H, 672 under heated H; inspiration: 633, 434, 660, data sets respectively. Z was determined every 5 min using impulse oscillometry (50 measurements under no H, 37 with cold H, and 60 with heated H (IOS, Jaeger, Höchberg, Germany); oscillating frequency 0–100 Hz). Impulse oscillometry was employed for the lower and upper airways 7, 9 and the forced oscillation technique proved to be useful in the diagnosis and automatic treatment of obstructive sleep apnoea syndrome (OSAS) 10–13. Flow was measured with a laminar flow element LFE-Typ PT (SI, Nördlingen, Germany; 0–150 L·min–1, tolerance <0.1%). The ambient conditions were determined with the hygrometer HP 100A (Rontronic, Bassersdorf, Switzerland; temperature –20–60°C, tolerance 0.3°C, humidity 0–99% rH, tolerance 1.5% rH).
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) 8.
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4: 2.06448x10–6 mg·L–6 °C–1; 3: 1.83498x10–4 mg·L–4 °C–1; 2: 9.92897x10–3 mg·L–3 °C–1; 1: 3.3282x10–1 mg·L–1 °C–1; 0: 4.8681 mg·L–1; 
: temperature (°C), Habs: absolute humidity (mg·L–1), Hrel (% rH): relative humidity.
The water loss during respiration (Wloss) can be calculated from the difference in Habs between inspired and expired air.
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Statistics
All data are presented as mean±sd. The computations for significant differences at p<0.05 were performed using a repeated-measure one-way analysis of variance (ANOVA) with post hoc comparisons (Bonferroni post hoc test).
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Results |
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). In the expired air, Hrel showed only mild, but significant, increases with both humidification modes. With no H, the difference in absolute humidity between inspired and expired air was 21.5±4.7 mg·L–1. This was reduced under cold H to 18.8±4.6 mg·L–1 (p<0.01) and under heated H to 12.3±5.1 mg·L–1 (p<0.001 as compared with cold H and no H). Thus, the loss of water under no H was only slightly reduced under cold H, but was halved under heated H (38% decrease of the water loss under heated H compared to cold H) (table 1). The Z of the total respiratory system increased under heated H (table 1).
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Discussion |
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Nasal obstruction is one of the major side-effects of continuous positive airway pressure treatment. Therefore, the possibility that the upper airways' impedance might be influenced differently by the various modes of humidification was investigated. The forced oscillation technique has proven useful in measuring the total airway system impedance under continuous positive airway pressure 10, 11. In the present study, it was measured with an impulse oscillometry device, selected because it does not require patient cooperation or, in contrast to posterior rhinomanometry, the introduction of a tube into the throat. Using posterior rhinomanometry, Richards et al. 3 obtained appreciably lower baseline measurements, which might have been due to differences in methodology. The present data showed no clinically relevant changes in impedance under the various humidification systems, and all measurements were carried out with the patient breathing quietly with the mouth closed. The small elevation in impedance under heated humidification compared to no humidification may have been due to the longer period of heated humidification (54.3±12.5 versus 32.8±10.8 min) and/or the kind of humidification system used. The present study provides no data on the long-term use of humidification systems and therefore, the conclusions presented cannot be related to long-term overnight use of humidification. Moreover, because the study was specifically designed to compare relative humidity of the inspired air under cold and heated humidification and to measure water loss in healthy subjects in the wake state and at a continuous positive airway pressure of 10 cmH2O, the results cannot be translated to other specific situations (e.g. mouth leaks, different pressure levels and ambient conditions).
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This article has been cited by other articles:
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  G. Nilius, U. Domanski, K-J. Franke, and K-H. Ruhle Impact of a controlled heated breathing tube humidifier on sleep quality during CPAP therapy in a cool sleeping environment Eur. Respir. J., April 1, 2008; 31(4): 830 - 836. [Abstract] [Full Text] [PDF]
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 S. Willing, M. S. Pedro, H. S. Driver, P. Munt, and M. F. Fitzpatrick The acute impact of continuous positive airway pressure on nasal resistance: a randomized controlled comparison J Appl Physiol, March 1, 2007; 102(3): 1214 - 1219. [Abstract] [Full Text] [PDF]
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| HOME | HELP | FEEDBACK | SUBSCRIPTIONS | ARCHIVE | SEARCH | TABLE OF CONTENTS |
hygr) is located between mask and breathing tube. A valve serves to eliminate the expired carbon dioxide (3). In the impulse oscillometry unit (impulse oscillometry (IOS) device), an oscillating flow is generated and conducted, via a tube (4) and Y-adapter (5), to the airways. The IOS device also picks up the pressure (pIOS) and flow (vIOS) signals recorded by the pneumotachograph (6) and filters out the signals produced by the oscillating flow. These signals are used to calculate the impedance. The transducer picks up all the measuring signals in the tube system and from the surroundings, and passes them, via an analogue-to-digital converter (A/D converter), to the computer (PC). pCPAP: pressure measured in the breathing tube; V': flow measured in the breathing tube; 
