Inaccurate calculation of drug output from nebulisers

Effect of Disinfection Method and Testing Methodology on the Performance of a Breath-Enhanced Jet Nebulizer

National guidelines for cystic fibrosis recommend cleaning and disinfecting nebulizers after each use. We tested two groups of five reusable breath-enhanced nebulizers after 0, 5, 10, 15, 20, 30, 60, 90, 120, 150, and 180 sterilization (baby bottle sterilizer) or cleaning cycles. The nebulizers were operated for 7 min (6 L/min) after loading albuterol (2.5 mg/3 mL), and they were evaluated with and without breathing simulation after cleaning/sterilization (0-180 and 0-60 cycles, respectively). Over the course of 180 cleaning/sterilization cycles, the mean (SD) solution output was 1.33 mL (0.12 mL)/1.29 mL (0.08 mL); the nebulizer mass remaining in the nebulizer was 61.5% (5.2%)/63% (4%); sputtering time was 4.7 min (0.8 min)/4.8 s (0.6 min); inspiratory filter was 19% (3%)/18.5% (2.4%); expiratory filter was 6.7% (1.1%)/6.7% (0.8%); and difference in drug output calculated using the solution output and nebulizer mass was 6.8% (4%)/5.2% (2.9%). Thermal disinfection with a baby-bottle sterilizer did not alter the performance of a reusable breath-enhanced nebulizer. The nebulizer test performed without breathing simulation underestimated its performance. The calculation of the drug output based on the solution output resulted in its overestimation.

The function and performance of aqueous aerosol devices for inhalation therapy

OBJECTIVES

In this review paper, we explore the interaction between the functioning mechanism of different nebulizers and the physicochemical properties of the formulations for several types of devices, namely jet, ultrasonic and vibrating-mesh nebulizers; colliding and extruded jets; electrohydrodynamic mechanism; surface acoustic wave microfluidic atomization; and capillary aerosol generation.

KEY FINDINGS

Nebulization is the transformation of bulk liquids into droplets. For inhalation therapy, nebulizers are widely used to aerosolize aqueous systems, such as solutions and suspensions. The interaction between the functioning mechanism of different nebulizers and the physicochemical properties of the formulations plays a significant role in the performance of aerosol generation appropriate for pulmonary delivery. Certain types of nebulizers have consistently presented temperature increase during the nebulization event. Therefore, careful consideration should be given when evaluating thermo-labile drugs, such as protein therapeutics. We also present the general approaches for characterization of nebulizer formulations.

SUMMARY

In conclusion, the interplay between the dosage form (i.e. aqueous systems) and the specific type of device for aerosol generation determines the effectiveness of drug delivery in nebulization therapies, thus requiring extensive understanding and characterization.

Modeling breath-enhanced jet nebulizers to estimate pulmonary drug deposition

BACKGROUND

Predictable delivery of aerosol medication for a given patient and drug-device combination is crucial, both for therapeutic effect and to avoid toxicity. The gold standard for measuring pulmonary drug deposition (PDD) is gamma scintigraphy. However, these techniques expose patients to radiation, are complicated, and are relevant for only one patient and drug-device combination, making them less available. Alternatively, in vitro experiments have been used as a surrogate to estimate in vivo performance, but this is time-consuming and has few "in vitro to in vivo" correlations for therapeutics delivered by inhalation. An alternative method for determining inhaled mass and PDD is proposed by deriving and validating a mathematical model, for the individual breathing patterns of normal subjects and drug-device operating parameters. This model was evaluated for patients with cystic fibrosis (CF).

METHODS

This study is comprised of three stages: mathematical model derivation, in vitro testing, and in vivo validation. The model was derived from an idealized patient's respiration cycle and the steady-state operating characteristics of a drug-device combination. The model was tested under in vitro dynamic conditions that varied tidal volume, inspiration-to-expiration time, and breaths per minute. This approach was then extended to incorporate additional physiological parameters (dead space, aerodynamic particle size distribution) and validated against in vivo nuclear medicine data in predicting PDD in both normal subjects and those with CF.

RESULTS

The model shows strong agreement with in vitro testing. In vivo testing with normal subjects yielded good agreement, but less agreement for patients with chronic obstructive lung disease and bronchiectasis from CF.

CONCLUSIONS

The mathematical model was successful in accommodating a wide range of breathing patterns and drug-device combinations. Furthermore, the model has demonstrated its effectiveness in predicting the amount of aerosol delivered to "normal" subjects. However, challenges remain in predicting deposition in obstructive lung disease.

Higher tobramycin concentration and vibrating mesh technology can shorten antibiotic treatment time in cystic fibrosis

Poor adherence to recommended therapy in cystic fibrosis (CF) is often because of the time demands of therapy. Tobramycin (TOBI®, 300 mg at 60 mg/ml) inhaled from the PARI LC PLUS® nebulizer requires about 20 min. This study determined if equivalent levels of pulmonary deposition could be achieved in shorter time using 1.5 ml of 100 mg/ml tobramycin solution delivered by an investigational eFlow® nebulizer. Sixteen males with stable CF, 8 children and 8 adults, and an FEV(1)  > 45% predicted inhaled both preparations on two occasions with (99m) Tc-DTPA added to the tobramycin. Blood samples were taken for quantification of tobramycin in the serum. The PARI LC PLUS® delivered 45.4 (39.3-51.6), mean and 95% CI, mg to the lungs in 17.0 ± 2.5 min (mean ± SD) with serum levels of 1,089 ± 388 µg/L. The investigational eFlow® delivered 46.3(40.3-51.7) mg in 4.0 ± 1.0 min with blood levels of 909 ± 458 µg/L. Only the time of delivery was significantly different with P < 0.0001 (paired t-test). Tolerability of the treatment was comparable for both inhalation regimes, but the shorter treatment was preferred by all patients. These results demonstrate the possibility of delivering equivalent levels of tobramycin much faster into the lungs of CF patients when using eFlow®, a very efficient electronic nebulizer.

A comparison of amount and speed of deposition between the PARI LC STAR® jet nebulizer and an investigational eFlow® nebulizer

BACKGROUND

The potency and physical properties of many of the drugs used in the treatment of cystic fibrosis necessitates the use of nebulization, a relatively time-consuming pulmonary delivery method. Newer, faster, and more efficient delivery systems are being proposed. The purposes of this study was to compare the length of time it took to deliver the equivalent of normal saline nebulized for 10 min in a PARI LC STAR(®) nebulizer to that of an investigational PARI eFlow(®).

METHODS

Six normal adults inhaled a 4-mL (36-mg) charge volume of saline from the LC STAR(®) or a 2.5-mL (22.5-mg) charge volume from the investigational eFlow(®). The saline was mixed with (99m)Tc-DTPA to allow two-dimensional imaging. The inhalation was preceded by a xenon equilibration scan to allow more accurate separation of deposition into central and peripheral lung regions.

RESULTS

The investigational eFlow(®) delivered 8.6 ± 1.0 mg, approximately 90% of the lung dose compared to the LC STAR(®), 9.6 ± 1.0 mg, but did in less than half the time (p < 0.02 for both). There were no differences in central versus peripheral distribution for either device.

CONCLUSIONS

In conclusion the investigational eFlow(®) was both faster and more efficient than the LC STAR(®).

Rapid pulmonary delivery of inhaled tobramycin for Pseudomonas infection in cystic fibrosis: a pilot project

BACKGROUND

Patients with cystic fibrosis spend as much 30 min a day inhaling tobramycin. Could a new rapid system deposit the equivalent amount of tobramycin faster?

METHODS

Six healthy adult males inhaled 5 ml (300 mg) of tobramycin from a breath enhanced nebulizer and either 125 mg (n = 3) or 150 mg (n = 3) from a vibrating membrane system with a large or small aerosol mixing chamber respectively. A radiolabel was added to the solution and shown to "track" with the tobramycin. Imaging was done with a dual headed gamma camera. Because the radiolabel will be cleared by mucociliary action during administration, algorithms were developed to allow the comparison of a slower system to a faster one.

RESULTS

Both formulations were well tolerated. The lung deposition was 16.6 +/- 3.2% (mean +/- SD) of the charge dose delivered in 10.9 +/- 1.0 min for the breath enhanced nebulizer versus 32.0 +/- 5.1% delivered in 2.5 +/- 0.4 min from the vibrating membrane system. The absolute pulmonary delivery of tobramycin was 49.9 +/- 9.6 versus 43.9 +/- 4.8 mg for the two systems respectively, differences that were statistically significant (pair t-test) but unlikely to be clinically significant. There was a similar deposition of tobramycin for the 125 and 150 mg dose.

CONCLUSIONS

It is possible to deliver an equivalent amount of tobramycin in a shorter period of time with the new vibrating membrane system and a more concentrated formulation. These data will allow the design of a comparison in patients with CF.

Nebulized therapies for childhood pulmonary hypertension: an in vitro model

OBJECTIVES

Sildenafil, tezosentan, and prostacyclin reduce pulmonary vascular pressures in pulmonary hypertension, but have potential to vasodilate the systemic circulation. Nebulized vasodilators allow targeted drug delivery, high local drug concentrations, less systemic hypotension, and better matching of the lung's ventilation and perfusion. We aimed to estimate pulmonary deposition of these drugs from commonly employed nebulizers using in vitro techniques and to create a mathematical model to predict inspired mass of aerosol.

DESIGN

Lung deposition was estimated by characterization of drug output and particle size distribution (PSD) of nebulizers using helium-neon laser diffraction techniques. A mathematical model for each device was created to estimate pulmonary deposition using patients' breathing patterns and was verified with a mechanical-breathing model.

RESULTS

Total output and PSD were similar for the Hudson Updraft II and Whisperjet nebulizers, consisting of half the nebulizer's charge, with (1/4) of particles < or = 5 microm, in the respirable fraction (RF). Drug output increased with inspiratory flow for the Pari LC Star. Differences were noted in device performance, depending on the drug tested. Estimated pulmonary deposition (mean, 95% CI) was 8.1 (7.2, 9.0)% of the initial drug charge for the Hudson Updraft II, 6.4 (5.8, 7.0)% for the Whisperjet, and 33.0 (28.3, 37.9)% for the Pari LC Star. A mechanical model was consistent with our mathematical model.

CONCLUSIONS

All drugs could be nebulized, but expected pulmonary deposition varied depending on the nebulizer and drug.

Accounting for radioactivity before and after nebulization of tobramycin to insure accuracy of quantification of lung deposition

The ability to predict drug deposition of inhaled drugs used in cystic fibrosis (CF) is important if there is a need to target specific doses of drug to the lungs of individual patients. The gold standard of measuring pulmonary deposition is the quantification of an aerosolized radiolabel either mixed with the drug solution or tagged directly to the compound of interest. Accuracy of the quantification could be assured if there is agreement between the amount of radioactivity before and after administration. Before administration, the radiolabel is concentrated in the well of the nebulizer, whereas after administration, it is distributed throughout the nebulizer, the expiratory filter and connectors, and the upper airway, stomach, trachea, and lung. Not only is the geometry of the distribution that is presented to the gamma camera different, but there are different attenuation factors for the various body tissues. The primary aim of this study was to evaluate the accuracy of the quantification of deposition. Secondary goals were to compare in vitro nebulizer performance with that measured in vivo during the deposition study. Eighty milligrams of tobramycin and technetium bound to human serum albumin was administered to 10 normal adults using a Pari LC Jet Plus (Pari Respiratory Equipment, Inc., Richmond, VA) breath-enhanced nebulizer. Techniques were developed that allowed for the accounting of 99 +/- 2% of the initial radioactivity. The fraction of the rate of lung deposition to total body deposition was the in vivo respirable fraction (0.62 +/- 0.07), which closely agreed with in vitro measurements of respirable fraction (0.62 +/- 0.04). Drug output measured from the change in weight and concentration in the nebulizer systematically overestimated drug output measured by the deposition study. The results indicate that 11.8 of the initial 80 mg would be deposited in the lungs. This technique could be adapted to accurately quantify the amount of deposition on any inhaled therapeutic agent, but caution must be used when extrapolating performance of a nebulizer on the bench to expected deposition in patients.

Nebulizer choice for inhaled colistin treatment in cystic fibrosis

STUDY OBJECTIVES

To develop practical ways of nebulizing colistin by determining the rate of drug output, total drug output, and particle-size distribution of two commercially available jet nebulizers, the disposable Hudson 1730 Updraft II (Hudson Respiratory Care; Temecula, CA) and the reusable Pari LC Star breath-enhanced nebulizer (Pari Respiratory Equipment; Midlothian, VA).

METHODS

The nebulizers contained colistin, 75 mg, in 4 mL of isotonic solution. Particle-size distribution was measured by helium-neon laser diffraction, allowing calculation of the respirable fraction (RF), the mass of aerosol comprised of droplets < 5 microm.

RESULTS

The mean (95% confidence interval [CI]) total rate of output of the Updraft II was 2.6 mg/min (2.0, 3.1; n = 4) with 1.3 mg/min (1.0, 1.5) mg/min within the RF. The rate of output of the LC Star increased in a quadratic relationship to the inspiratory flow, delivering 1.8 mg/min (0.7, 2.0; n = 4) with 1.4 mg/min (1.3, 1.6) within the RF, and 6.2 mg/min (5.6, 6.8) with 5.3 mg/min (4.8, 5.7) within the RF, at 0 L/min and 20 L/min inspiratory flows, respectively. Efficiency, as the rate of expected pulmonary deposition divided by rate of total output, was then calculated. The LC Star estimated 56% (51, 61) efficiency, with pulmonary delivery of 29% (26, 32) of the charge of the nebulizer, compared to the Updraft II at 22% (22, 23) efficiency and expected pulmonary deposition of 10% (10, 10) of the dose.

CONCLUSIONS

Colistin can be successfully nebulized with both nebulizers tested. This study provides an estimate of in vivo efficiency and expected pulmonary deposition that may be used in future trials.

The choice of jet nebulizer, nebulizing flow, and addition of albuterol affects the output of tobramycin aerosols

The use of inhaled antibiotics in the treatment of cystic fibrosis has become widespread despite controversy in the literature as to the appropriate dosing regimen and its effectiveness. This study compared two tobramycin (T) preparations (one with and one without the addition of albuterol) using two different jet nebulizers in order to determine if drug output would be affected. Using calibrated flows from a dry compressed gas source of 6 and 8 L/min as well as a specific compressor (Pulmo-Aide), the Hudson 1720 nebulizer was compared with the newer disposable Hudson 1730. The albuterol preparation used in this study was the Ventolin (albuterol) Respirator Solution (VRS). The nebulizers were charged with (1) 2 mL T (80 mg/2 mL) with 0.5 mL VRS (5 mg/mL) and normal saline solution to make the total nebulizer charge of 3 or 4 mL, or (2) 2 mL T and either 1 or 2 mL normal saline solution. A laser diffraction analyzer (Malvern 2600) was used to determine the aerosol particle size distribution. From the distribution, the respirable fraction, which is the fraction of aerosol that could enter and remain in the lungs, was calculated. For all solutions and each particular flow, the Hudson 1730 had a larger respirable fraction of T. The addition of VRS lowered the surface tension of the solution in the nebulizer and resulted in a greater output of T. This effect was most apparent for the 3-mL volume fills of the Hudson 1720. The greatest differences were between the 3-mL nebulizer charges of T using the Hudson 1720 driven by a flow of 6 L/min, which produced 8 mg of T in the respirable fraction, compared with 35 mg produced by the Hudson 1730 driven by a flow of 8 L/min. These results suggest that different nebulizers, different nebulizer solutions, and different techniques of nebulization may result in very different amounts of T aerosol output in the respirable fraction.

Measuring nebulizer output. Aerosol production vs gravimetric analysis

STUDY OBJECTIVES

The function of jet nebulizers has been measured traditionally by gravimetric methods, i.e., by weighing nebulizers before and after nebulization. Newer techniques measure aerosol output directly by analyzing aerosolized drug or tracer, i.e., radioactive 99mTc. Because of evaporation, the equivalence of these methods is uncertain. The aim of this study was to determine if the gravimetric method is an accurate measure of aerosol production under different conditions of aerosol generation (i.e., nebulizer type, flow rate, pressure, volume fill, and concentration of solution used to nebulize a drug).

METHODS

In the first phase of the study, we measured the aerosol output of nine commercially available jet nebulizers (AvaNeb; Up-Draft-Hudson RCI; Cirrus-Intersurgical Inc; DeVilbiss 646-DeVilbiss; Powermist-Hospitak, Inc; Respirgard II-Marquest Medical Products; Seamless-Seamless/Dart Respiratory; Salter; Salter Labs; Airlife-Baxter Health Care) run under commonly used conditions (2.5 mL volume fill, 2.0 mL normal saline solvent, 0.5 mL albuterol, flow of 6 L/min, and pressures averaging 15.0 +/- 2.3 [mean +/- SD] pounds per square inch [on the] gauge [psig] provided by a DeVilbiss PulmoAide compressor) with simultaneously measured gravimetrics and filtered radioactivity. Each nebulizer was run to dryness with data acquired every 2 min. The change in the weight of the nebulizer and radioactivity captured on the filter were expressed as percentages of the total in the nebulizer solution. In the second phase of the study, the experiments were repeated using the same nebulizers with a volume fill of 5 mL (diluted to half normal saline solution plus albuterol), flow of 10 L/min, and pressures of 35.6 +/- 8.8 psig.

RESULTS

The cumulative (sum of all 2-min runs) weight loss for each individual nebulizer ranged from 25.00 to 64.55% and cumulative aerosol captured varied from 12.63 to 38.76%. While different, the weight loss and aerosol captured were closely correlated (y = -0.62 + 0.62x; r = 0.961, p < 0.0001). Changing volume fill and concentration of solvent did not affect this correlation (p = 0.921 and 0.373, respectively). However, changing flow from 6 L/min to 10 L/min significantly (p = 0.02) affected the relationship (y = -3.80 + 0.83x; r = 0.969, p < 0.001).

CONCLUSIONS

When compared with direct methods such as filtering generated particles, the gravimetric method of assessing nebulizer function overestimates aerosol output by 1.8 +/- 0.18 times, presumably because of the loss of solvent during nebulization. However, the relationship between methods is predictable and appears unaffected by changing the type of nebulizer, volume fill, and concentration of solvent. Changes in nebulizer flow and pressure significantly affected the correlation. Gravimetric methods can be used as simple and convenient screening techniques for comparing jet nebulizers under a wide range of experimental conditions.

A comparison of pulmonary availability between Ventolin (albuterol) nebules and Ventolin (albuterol) Respirator Solution

The two most common albuterol preparations used for nebulization are: (1) Ventolin (albuterol) respirator solution (Glaxo Canada Inc; Montreal, Canada) of which 2.5 mg (0.5 mL) is diluted with 2 mL of normal saline solution, and (2) the preservative-free, prediluted Ventolin (albuterol) Nebules PF (Glaxo) (2.5 mg/2.5 mL). The two preparations were compared using both a Hudson 1720 "T" up-draft Neb-U-Mist jet nebulizer and a Hudson 1730 "T" up-draft Neb-U-Mist II jet nebulizer (Hudson; Temecula, Calif), which were driven by a compressor (Pulmo-Aide; Devilbiss; Somerset, Pa) and by dry compressed air at 6 and 8 L/min. Particle size distribution was measured with a particle sizer (Malvern 2600; Malvern Instruments; Malvern, UK) and drug output for the nebulizer was calculated from the differences in predrug and postdrug volume and concentration. Drug availability was defined as the amount of drug carried in particles less than 5 microns in diameter. Drug availability was greater with the albuterol respiratory solution, due to the surface activity of the preservative benzalkonium chloride, for both nebulizers but particularly for the 1720. Differences in drug availability between nebulizers exceeded fourfold depending on the preparation, the nebulizer, and the nebulizing flow. These differences could not have been predicted from the manufacturer's specifications. The results suggest that prediction of drug availability must be based on measurements with the specific preparation and the specific nebulizer used.

Medication nebulizer performance. Effects of diluent volume, nebulizer flow, and nebulizer brand

BACKGROUND

Medication nebulizers are commonly used to delivery aerosolized medications to patients with respiratory disease. We evaluated output and respirable aerosol available to the patient (inhaled mass) for 17 medication nebulizers using a spontaneous breathing lung model.

METHODS

Three nebulizer fill volumes (3, 4, and 5 mL containing 2.5 mg of albuterol) and 3 oxygen flows (6, 8, and 10 L/min) were evaluated using the 17 nebulizers. A cotton plug at the nebulizer mouthpiece was used to trap aerosol during simulated spontaneous breathing. Following each trial, the amount of albuterol remaining in the nebulizer and the amount deposited in the cotton plug were determined spectrophotometrically. Aerosol particle size was determined using an 11-stage cascade impactor.

RESULTS

Increasing fill volume decreased the amount of albuterol trapped in the dead volume (p < 0.001) and increased the amount delivered to the patient (p < 0.001). Increasing flow increased the mass output of particles in the respirable range of 1 to 5 microns (p = 0.004), but the respirable mass delivered to the patient was affected to a greater extent by nebulizer brand (p < 0.001) than flow. Although 2.5 mg of albuterol was placed into the nebulizers, less than 0.5 mg in the respirable range of 1 to 5 microns was delivered to the mouthpiece.

CONCLUSIONS

The performance of medication nebulizers is affected by fill volume, flow, and nebulizer brand. When they are used for research applications, the nebulizer characteristics must be evaluated and reported for the conditions used in the investigation.

Aerosol deposition in infants with cystic fibrosis

Twenty asymptomatic infants with cystic fibrosis (CF) were studied to determine the amount of radiolabeled aerosol [99m technetium diethylenetriamine penta acetic acid (Tc99m DTPA)] deposited in the respiratory system and its distribution. Aerosols were generated by jet nebulization systems that were used in the wards and the laboratory. Subjects were studied in three groups: group A (n = 10) was sedated with chloral hydrate; children inhaled an aerosol of 7.7 microns mass median diameter (MMD); group B (n = 5) was not sedated, using the same nebulization system (same aerosol particle size as group A); and group C (n = 5) was not sedated; these children inhaled an aerosol with an MMD of 3.6 microns. Normal saline plus 4 mCi of Tc99m bound to DTPA was added to each nebulizer. A closed system was used to collect the expired aerosol. Radioactivity in each infant and in the equipment was measured with a gamma camera on completion of nebulization. In groups A and B, the percentages of the total dose deposited in the lung were 0.97 +/- 0.35% and 0.76 +/- 0.36%, respectively. In group C, 2.0 +/- 0.71% was deposited in the lung (P < 0.01). Deposition in the nose, mouth, and pharynx was least in group C (P < 0.01). In groups A and B, the intrathoracic deposition occurred predominantly in the trachea and main bronchi, whereas in group C, significantly more aerosol was deposited in the lung region. There was marked inter-subject variability in the percentage of aerosol deposition within the three groups. There was no correlation between percentage of aerosol deposited in the respiratory system and age, height, or weight. Sedation did not have a significant effect on deposition of aerosol in infants. This study indicates that only a small proportion of nebulized solution is deposited in the lungs of infants and that this proportion is influenced by the particle size of the aerosol. The smaller particle size (3.6 microns MMD) was deposited in the lung better than large particles.

Prediction and experimental determination of solute output from a Collison nebulizer

The total output from a nebulizer is made up of aqueous droplets containing solute and a significant component of water vapor. The solvent loss is reflected in an increase in the nebulizer solution concentration over time and this has been described mathematically. This theory, originally described by Mercer et al., was modified to describe the solute output from a three-jet Collison nebulizer. The influence of concentration, air flow (air pressure), volume, and temperature on the output parameters were then studied. Inlet air pressures were 10 (4.1), 20 (6.4), and 40 (10.0) psig (L/min), starting concentrations were 0.1, 2, and 5% (w/w) and initial solution volumes were 10 and 20 mL. To study temperature effects, solutions were nebulized at fixed temperatures ranging from 4 to 50 degrees C. This was achieved by water-jacketing the nebulizer flask. Test solutions consisted of mannitol and a fixed concentration of 11.1 micrograms/mL carboxyfluorescein. Nebulization was carried out for up to 30 min using dry, filtered air at ambient temperature. Total output was determined gravimetrically while solute output was determined by fluorimetry (495-nm excitation, 515-nm emission). Solution concentration changes were also monitored over time by fluorimetry. The results show that the solution and solvent output parameters are independent of concentration, volume, and air flow within the ranges studied but that solvent output, in particular, is highly dependent upon temperature.

Salbutamol output from two jet nebulizers

Nebulized bronchodilators are commonly used in the management of patients with airflow obstruction, although there is little information available on the bronchodilator output from the nebulizer unit. We have examined the fluid and salbutamol outputs of a single jet nebulizer from two commercial manufacturers at 1 min intervals up to 12 min. The drug and fluid output continued throughout the study period, with a greater fluid output leading to an increase in the concentration of salbutamol remaining within the nebulizer unit. This suggests that weight change is not a good indicator of drug output. Furthermore, there was a marked difference in peak salbutamol output between the two nebulizer units, being 2.9 mg (55%) with the Micro-Neb unit and 1.98 mg (38.7%) with the System 22 unit.

Design characteristics for drug nebulizers

Drug nebulizers should be designed to produce an aerosol which efficiently targets drug to the respiratory tract. In this article we review the basic principles of aerosol generation from both jet and ultrasonic nebulizers, and the factors governing respiratory tract penetration and deposition. We review methods for accurate measurement of aerosol dose and size, with emphasis on evaporative effects and the implications to drug nebulizer design. We identify three forms of drug aerosol waste attributable to: generation of non-respirable aerosol, losses to the environment, and dead volume solution; and we consider how each may be minimized through good nebulizer design. Finally, we compare the relative merits of jet and ultrasonic nebulizers, and conclude by predicting a new trend in future drug nebulizer therapy.

Nebulization of liposomes. II. The effects of size and modeling of solute release profiles

A series of carboxyfluorescein (CF)-containing multilamellar vesicle (MLV) dispersions was prepared and extruded through polycarbonate membranes ranging in size from 0.2 to 5 microns. Vesicle dispersions were nebulized for 80 min using a Collison nebulizer, and the release of CF was monitored during nebulization. Solute retention was dependent upon the size of the vesicles and leakage ranged from 7.9 +/- 0.4% (N = 3) for vesicles extruded through 0.2-microns filters to 76.8 +/- 5.9% (N = 3) for liposomes that were not filtered. Solute release profiles obtained over greater than or equal to 420-min nebulization periods conformed to a two-compartment kinetic model and exhibited a "fast" initial phase (k1 = 0.052 +/- 0.0043) followed by a "slow" terminal phase (k2 = 0.0034 +/- 0.00018). The results show that CF retention can be increased by nebulizing small vesicles and modeling suggests that the rate of CF leakage from the bilayers is faster than from the core of the liposomes.

Jet and ultrasonic nebuliser output: use of a new method for direct measurement of aerosol output

Output from jet nebulisers is calibrated traditionally by weighing them before and after nebulisation, but the assumption that the weight difference is a close measure of aerosol generation could be invalidated by the concomitant process of evaporation. A method has been developed for measuring aerosol output directly by using a solute (fluoride) tracer and aerosol impaction, and this has been compared with the traditional weight loss method for two Wright, six Turbo, and four Micro-Cirrus jet nebulisers and two Microinhaler ultrasonic nebulisers. The weight loss method overestimated true aerosol output for all jet nebulisers. The mean aerosol content, expressed as a percentage of the total weight loss, varied from as little as 15% for the Wright jet nebulisers to 54% (range 45-61%) for the Turbo and Micro-Cirrus jet nebulisers under the operating conditions used. In contrast, there was no discrepancy between weight loss and aerosol output for the ultrasonic nebulisers. These findings, along with evidence of both concentrating and cooling effects from jet nebulisation, confirm that total output from jet nebulisers contains two distinct fractions, vapour and aerosol. The vapour fraction, but not the aerosol fraction, was greatly influenced by reservoir temperature within the nebuliser; so the ratio of aerosol output to total weight loss varied considerably with temperature. It is concluded that weight loss is an inappropriate method of calibrating jet nebuliser aerosol output, and that this should be measured directly.