- Open Access
High-resolution mucociliary transport measurement in live excised large animal trachea using synchrotron X-ray imaging
© The Author(s). 2017
- Received: 27 February 2017
- Accepted: 3 May 2017
- Published: 16 May 2017
The Australian Synchrotron Imaging and Medical Beamline (IMBL) was designed as the world’s widest synchrotron X-ray beam, enabling both clinical imaging and therapeutic applications for humans as well as the imaging of large animal models. Our group is developing methods for imaging the airways of newly developed CF animal models that display human-like lung disease, such as the CF pig, and we expect that the IMBL can be utilised to image airways in animals of this size.
This study utilised samples of excised tracheal tissue to assess the feasibility, logistics and protocols required for airway imaging in large animal models such as pigs and sheep at the IMBL. We designed an image processing algorithm to automatically track and quantify the tracheal mucociliary transport (MCT) behaviour of 103 μm diameter high refractive index (HRI) glass bead marker particles deposited onto the surface of freshly-excised normal sheep and pig tracheae, and assessed the effects of airway rehydrating aerosols.
We successfully accessed and used scavenged tracheal tissue, identified the minimum bead size that is visible using our chosen imaging setup, verified that MCT could be visualised, and that our automated tracking algorithm could quantify particle motion. The imaging sequences show particles propelled by cilia, against gravity, up the airway surface, within a well-defined range of clearance speeds and with examples of ‘clumping’ behaviour that is consistent with the in vivo capture and mucus-driven transport of particles.
This study demonstrated that the wide beam at the IMBL is suitable for imaging MCT in ex vivo tissue samples. We are now transitioning to in vivo imaging of MCT in live pigs, utilising higher X-ray energies and shorter exposures to minimise motion blur.
- Mucociliary transport
- Particle tracking
- Cystic fibrosis
- Phase contrast
- X-ray imaging
Cystic fibrosis (CF) lung disease is caused by an improperly functioning ion channel in the airway epithelium and results in a reduction in the depth of the airway surface liquid (ASL) layer and impaired mucociliary transport (MCT). MCT is the mechanism by which tiny hair-like structures called cilia move inhaled particles along the airway surfaces and out of the lungs. In CF, the airway dehydration and production of thick sticky mucus result in a cycle of inflammation and infection that ultimately leads to progressive lung disease and early death from lung failure .
We have developed an airway gene transfer technique that inserts the corrective gene (CFTR) into defective airway cells of CFTR-null mice, with the resulting CFTR ion-channel correction lasting for at least 12 months . Although we can electrically measure the ionic changes produced by our gene therapy using the established transepithelial potential difference measurement technique, there are currently no methods to rapidly and accurately quantify small corrections in the dysfunctional mucociliary activity or any improvements in airway health in a live animal, after a potential treatment is performed. The ability to detect beneficial effects produced by novel therapies in live CF airways soon after treatment would substantially advance research into new genetic and pharmaceutical CF treatments.
MCT has typically been quantified by measuring the bulk clearance of radioactive or fluorescent particles deposited in the airways . To rapidly determine the efficacy of genetic and pharmaceutical therapies for CF we have developed MCT monitoring methods in live anaesthetised normal and CFTR-null mice to measure the transport rate and behaviour of individual deposited 10-30 μm diameter high refractive index (HRI) glass bead marker particles using propagation-based synchrotron phase contrast X-ray imaging (PCXI) . Compared to conventional sources, a synchrotron can produce X-rays that are much brighter, more spatially coherent and closer to monochromatic, enabling PCXI setups able to utilise X-ray refraction (in addition to absorption) to achieve high spatial and temporal resolution, and excellent airway and lung soft tissue contrast. Nuclear imaging techniques, fluoroscopy and CT imaging systems are not able to resolve particles of this size. These synchrotron X-ray MCT imaging methods have been developed in mice over more than 8 years at the SPring-8 synchrotron in Japan, and we have recently begun to transition them to the Imaging and Medical Beamline (IMBL) at the Australian Synchrotron .
However, CFTR-null mice are a limited model because they do not exhibit human-like lung pathophysiology , and although the nasal airways of these mice do exhibit the CF pathophysiology, there is evidence that nasal MCT is not altered in CFTR-null mice [4, 7]. Furthermore, since it is designed for large animal imaging, the IMBL beam characteristics are not well suited to resolving the 10–30 μm particles normally used for MCT measurement in a ~1 mm diameter mouse airway.
Our group is interested in using newly developed large-animal CF animal models, such as the CF pig, which display human-like lung disease and have human-sized lungs . In future imaging experiments we plan to test the effectiveness of our gene therapy treatment in live CF animals at the IMBL, to rapidly and non-invasively determine the effectiveness of our gene therapy protocols via assessment of MCT-rate changes. The IMBL is primarily designed for performing propagation-based PCXI due to its high x-ray flux and high coherence, partly brought about by a large source-to-sample distance (greater than 137 m in the satellite building hutch). The beamline setup produces an X-ray beam of up to 400 mm × 40 mm (W × H) at the sample position, making the imaging of larger animals such as sheep, pigs, and potentially humans, possible in the future.
A recent article has detailed the importance and feasibility of MCT analyses for CF, and revealed the differences between CF and normal airways, both at baseline and under pharmaceutical manipulation . That study used a standard human clinical CT setup combined with large (350 μm diameter x 25 μm thickness) tantalum discs as MCT markers that were insufflated into the airways using a puff of air. CT scans were acquired every 15 s for 10 minutes to track micro-disc motion, and used a minimum detection velocity of 1 mm/min. They showed that a similar proportion of micro-discs cleared the CF and non-CF airways over the 10-minute period, and that in both groups the discs migrated toward the ventral tracheal surface. Impaired clearance in the CF group was only apparent when a methacholine challenge was applied to both. Importantly, they noted that MCT assays could be used to report therapeutic efficacy.
The aim of the present study was to report the feasibility of using PCXI at the IMBL to quantify MCT in excised normal large animal airways using HRI glass marker particles. We used freshly excised normal tracheal tissue from sheep and pigs to remove the imaging complexity that would be produced by surrounding body tissues. We aimed to use our ex vivo imaging system to determine the range of MCT rates, whether there are preferential patterns of MCT flow within the trachea, and to demonstrate the effect of common clinical rehydrating therapies for CF airways that are known to alter MCT . Importantly, we aimed to obtain the baseline MCT data from normal large animal trachea as well as permit the establishment of the necessary logistics and IMBL needs and protocols for airway MCT imaging. This study was essential for our continued efforts to establish imaging and technical infrastructure required for the transition to in vivo trials in large animal models such as normal and CF pigs, in order to validate the effects of genetic and pharmaceutical therapies.
The Imaging and Medical Beamline at the Australian Synchrotron was used for all imaging experiments, and the data was collected over two beamtime allocations.
The storage ring operated at 3 GeV and a ring current of 200 mA for both experiments. The RMS electron beam size in the straight sections was 320 × 16 μm , and corresponded to a Gaussian FWHM of 754 × 38 μm in the horizontal and vertical directions, respectively. The IMBL X-ray beam was produced by a superconducting multi-pole wiggler functioning at a field strength of 3.0 T. The required energy of 30 keV was selected using a dual silicon Laue crystal monochromator, and the source-to-monochromator distance was 16.15 m.
All imaging was performed in the IMBL satellite building experimental hutch 3B at a distance of ~136 m from the storage ring , using the previously established setup shown in Murrie et al. . A sample to detector distance of 2.5 m was used, and images with an effective pixel size of 16 μm (field of view of ~ 16.6 mm × 14 mm) were captured using the Ruby detector . This was the smallest field of view of which the detector was capable, and was selected in order to visualise most of the width of the ~15–20 mm diameter tracheae at high magnification.
X-ray beam uniformity is to a certain extent governed by the power load on the monochromator. For the first experiment the power of the input spectrum was reduced using copper filters, resulting in a lower flux and uniform illumination. Exposure times of 1 s were required to use most of the dynamic range (16-bits) of the PCO.edge sensor (PCO imaging, Germany). In the second experiment the copper filters were removed, increasing the available flux and enabling an exposure length of 250 ms to be used, at the expense of a slight degradation in the quality of the beam shape.
MCT tracking particle testing
Prior to the excised tissue experiments, the visibility of a selection of differently-sized HRI glass beads (Corpuscular, NY, USA) was assessed using the chosen imaging parameters. Minute quantities of HRI beads with diameters of 52, 78 and 103 μm were placed on Kapton tape and imaged.
Excised tissue preparation
The first experiment utilised five freshly-excised normal adult sheep tracheae and the second utilised three freshly-excised normal adult pig tracheae (Camborough 29, ~250 kg female); all samples were recovered from animals off-site from the synchrotron. Animals were sedated and then humanely killed by sodium pentobarbital overdose, with the trachea rapidly excised immediately after death. Care was taken to minimise the amount of blood that entered the tracheae. After excision each trachea was washed in a solution of 20 mM Krebs-HEPES Buffer at pH 7.4, and stored for transport to the IMBL in a fresh container of the same buffer solution at ~4 °C.
At the IMBL each trachea was cut into ~20 mm long segments (typically resulting in 3–5 segments per trachea, containing ~3 cartilage rings each, with each segment slightly taller than the imaging field of view). Prior to imaging, the tracheal segment was pinned out vertically onto the base of a custom-made polycarbonate trachea chamber on well-moistened gauze, then slowly warmed to and maintained at physiological temperature (~37 °C). The segments were normally mounted with the cranial end at the top, so that the predominant direction of MCT was upwards, against gravity. In the sheep experiment two segments were mounted “upside down” to verify that MCT occurred in the expected direction (downwards in this “upside down” case). In the pig experiment four segments of conducting airway tissue from, at and below the carina were also examined.
Samples were typically imaged within 8 h of excision except for one during the sheep experiment that was deliberately imaged ~24 h after excision to assess whether residual MCT activity was present after a prolonged period in buffer at 4 °C.
Each tracheal segment was placed on the hutch X-Y stage with temperature maintained at ~37 °C, and oriented such that images were captured from the dorsal/ventral (anterior/posterior) direction. In the pig studies images of the trachea were captured prior to HRI particle delivery, to be used for background subtraction. A small quantity of 103 μm diameter HRI glass particles were then delivered to the caudal end of the tracheal segment using a mouse Dry Powder Insufflator™ (PennCentury, PA). For the sheep studies the particles were placed on the ventral tracheal surface (i.e. the side opposite the trachealis muscle and oesophagus where MCT was expected to be maximal ), and for the pig studies on the dorsal tracheal surface (to detect any dorsal to ventral particle motion).
Hoegger et al. showed that deposited particles preferentially migrated to the ventral tracheal surface [9, 15], so to test whether this effect was detectable in our samples some segments were rotated axially 90° after the first imaging run was completed. An additional sample of beads was deposited in the same manner, but this time onto the lateral tracheal wall. A second imaging run, including aerosol delivery, was then performed in a lateral direction to compare the MCT and spatial pattern of particle movement beginning on a ventral or a lateral wall of the trachea.
Custom image analysis software (written by MD and described in Appendix A) was used to measure and compare particle MCT rates by identifying particles and tracking their motion throughout the image sequences.
To validate the automated tracking algorithm the first frame of each imaging run was manually analysed to count the number of features incorrectly identified as particles (false positives) and the number of moving particles that were not correctly identified or tracked (false negatives). These values were used along with the number of detected particles (positives) to determine the sensitivity of the algorithm.
Where appropriate, statistical analyses were performed using GraphPad Prism 7. Data were tested for normality, statistical significance was set at p = 0.05 and power = 0.80, and a one-way ANOVA and Bonferroni post-hoc test were used for multiple comparisons. MCT rates are presented as mean plus standard deviation.
The number of imaging runs in which MCT tracking particles were successfully tracked in each group
Sheep (n = 5)
Pigs (n = 3)
At 24 h
Additional file 1: Video S1. Were assembled from the processed images to show the variability in particulate behaviour on the tracheal airway surfaces. The movie frame rate was set to 5x normal speed. Additional file Videos can be played using the free VLC Media Player (available at http://www.videolan.org/vlc/). shows MCT tracking particles in the segment of sheep trachea shown in Fig. 3a, during a baseline (no aerosol) run, taken from a dorsal/ventral view. The majority of particles are correctly tracked, but occasional un-detected particles are visible. (MP4 21840 kb)
Additional file 2: Video S2. Were assembled from the processed images to show the variability in particulate behaviour on the tracheal airway surfaces. The movie frame rate was set to 5x normal speed. Additional file Videos can be played using the free VLC Media Player (available at http://www.videolan.org/vlc/). shows tracked particles in a baseline run from a dorsal/ventral view in the segment of pig trachea shown in Fig. 3c. The direction of transport is clearly different to the sheep trachea. (MP4 10903 kb)
Additional file 3: Video S3. Were assembled from the processed images to show the variability in particulate behaviour on the tracheal airway surfaces. The movie frame rate was set to 5x normal speed. Additional file Videos can be played using the free VLC Media Player (available at http://www.videolan.org/vlc/). shows MCT particle motion at the segment of airway containing the pig carina, shown in Fig. 7. A number of false positives were present in this run, due to bubbles on the airway surface. (MP4 21962 kb)
When particles aggregated very closely the particle detection step (described in Appendix A) was unable to accurately separate them into individual particles (producing false negatives). Accordingly, when beads were isolated they were more accurately identified and tracked than when aggregated into groups. This happened more frequently in the pig tracheal segments, but again had little effect on the results because all particles in the aggregates normally moved at similar speed. Often particles were not tracked for the entire image sequence, with the algorithm occasionally losing a particle for a frame or two before detecting it again in subsequent frames. In the sheep experiment there were some beads that moved too fast to be accurately detected by the tracking code (described in Appendix A1.4). Since we used a 15 pixel maximum displacement to ensure tracking was successful, particles moving faster than 6 mm/min could not be tracked by this algorithm (see Additional file 1: Video S1). This may have reduced the measured mean MCT rate in the sheep experiment, and was one of the primary reasons we increased the frame rate for the second (pig trachea) experiment. For the pig tracheal segments the theoretical maximum MCT rate that could be measured by the tracking algorithm was 24 mm/min.
Particle MCT was visible in all tracheal segments examined, including the sheep segment that was deliberately stored in chilled buffer solution for ~24 h after excision. In the normally-prepared (caudal end upwards) samples beads moved in the direction of preferential MCT, primarily up the tracheal wall when oriented against gravity, although interestingly they rarely moved directly up the trachea at an angle of zero degrees. In the two sheep tracheal segments that were mounted “upside down” MCT also proceeded downwards, as expected. Beads tended to organise and aggregate into long strings, and appeared to move in favoured MCT tracts. In the pig samples the beads typically moved circumferentially towards the ventral tracheal surface.
The mean instantaneous baseline MCT rate was 1.62 ± 1.22 mm/min for the sheep, and 1.32 ± 1.19 mm/min for the pigs. Following treatment with aerosolised hypertonic saline the average MCT rate over the 10-min period rose to 2.50 ± 1.19 mm/min for the sheep, and 1.75 ± 1.59 mm/min for the pigs; clearly individual rates would have been higher at some time points. For the sheep tracheal segment imaged upside down the instantaneous MCT rate was 1.45 ± 0.81 mm/min, and for the segment imaged 24 h after excision the MCT rate was 0.34 ± .0.3 mm/min. In all cases the measured mean MCT rates were lower than those previously reported in humans; 5.7 ± 2.6 mm/min  and 4.1 mm/min [16, 17] as well as in sheep; 8.2 ± 1.9 mm/min  live pigs; 6.9 ± 0.7 mm/min  and excised pig trachea; 2.3 ± 0.3 mm/min . Although we did see many particles moving at similar rates to these, the presence of large numbers of very slow moving particles lowered the average rate. From our pilot SPring-8 studies in mice we suspect that the choice of MCT tracking particles (size and surface characteristics) may also play a role in the particle transport rate, and may also be responsible for some of the difference in our reported MCT rates.
The predominant direction of MCT appeared different between species, being along the length of the trachea in the sheep, and more circumferentially in the pigs (see Additional file 1: Video S1 and Additional file 2: Video S2). This may have been because in the sheep the particles were deposited on the ventral wall – the portion of the trachea that Hoegger et al. showed particles migrate towards [9, 15] – whereas in the pigs the particles were deposited on the dorsal wall, and therefore had a more axial motion to transport towards the ventral wall (See Additional file 1: Video S1 and Additional file 2: Video S2). Further studies must be performed to confirm this speculation.
At SPring-8, we have exploited synchrotron PCXI on a highly coherent source (BL20XU and BL20B2) for live small-animal imaging (mice and rats) where high flux is critical to obtain very short exposure times (<50 ms) to avoid motion blurring in animals with high respiratory rates. High spatial coherence is necessary for PCXI, however the experiments we describe here, with a larger field of view and strong absorption contrast from the beads, demonstrate that the reduced spatial coherence at the Australian Synchrotron’s IMBL is sufficient for our methods, making these experiments in large airways viable at the IMBL. We expect that when imaging a ~20 kg piglet (i.e. 8–9 weeks old) the additional neck tissue surrounding the trachea will require the use of a higher energy (e.g. 60 keV) with an exposure time of around 100 ms to maintain motion-free images during respiration. However, based on the results from this study, we predict that in vivo MCT measurements in a live pig trachea are feasible.
These clear pilot data has shown the exciting potential of the IMBL for performing live large animal imaging when relevant large normal and CF animal models are appropriate and available. These studies did have a number of limitations, including the rudimentary maintenance of humidification (closed imaging vessel held at 37 °C) and the variability in the time between excision and imaging for each segment. There was also an absence of reciprocating airflow within the tracheal segment that would mimic the normal lung airflow conditions during breathing; such airflow conditions are known to release airway nucleotides that can influence ASL depth and MCT rate . However, these experiments were designed as ex vivo studies using scavenged tracheal tissue, to trial expected imaging, biological, and logistical parameters with sufficient experimental flexibility to enable imaging optimisation without the complications of strict radiation dose control and live-animal handling restrictions. Provided physiological support is utilised to maintain adequate tissue hydration and temperature, it would be possible to use this ex vivo setup to image multiple particles in various locations within large animal airway segments over long time periods (e.g. multiple hours), and to examine the effects of mucus reducing agents or other pharmaceuticals on MCT function.
When extended to in vivo tracheal imaging using higher X-ray energies for improved penetrating power (and minimise the effects of overlying tissue and cartilage) we expect to be able to track multiple small particles, perform repeat imaging, and image for long periods; a protocol that will be useful for studying the effects of long-acting pharmaceuticals or genetic therapies on MCT. Although imaging of the deeper airway was possible in this study, we expect that in live imaging experiments the greater lung motion in the deeper lung regions would make accurate measurements in this region much more challenging. The primary benefits of using this type of two-dimensional imaging setup compared to CT (e.g. as used by Hoegger et al. [9, 15]) is that it can be used to track treatment effects for long periods with reduced radiation exposure, it can track multiple individual particles with high spatial and temporal resolution and thereby examine clearance heterogeneity and particulate grouping behaviour within the trachea. This may be particularly informative in CF models where some portions of the airway have dysfunctional clearance while other areas retain essentially normal clearance . Future in vivo studies will deal with essential aspects of in vivo experimental design, and with reductions in radiation dose we expect that repeated-measures studies that allow for the tracking of treatment effects will be possible and allow assessment of MCT over longer periods (as already successfully performed in mice at the SPring-8 Synchrotron in Japan ).
This experiment demonstrated that the IMBL X-ray beam is suitable for imaging MCT in ex vivo tissue samples from large animals. Our findings indicate that with increased flux and reductions in exposure length the measurement of MCT behaviour via PCXI imaging will be possible in future live-imaging studies of intact large animals such as sheep and pigs.
This research was undertaken on the Imaging and Medical Beamline at the Australian Synchrotron, under proposal numbers AS151/IMBL/8993 and AS153/IM/10057. We thank Dr Robert Acres, Dr Andrew Stevenson and Dr Daniel Hauserman for technical assistance on the beamline. We also thank Dr Anne Gibbon for assistance with tracheal tissue procurement, Dr Rob Bischof for providing excised sheep tissue, and Graham Shillito and Melissa Knight from the Monash Animal Research Platform for providing the excised pig tissue.
Studies supported by the Women’s and Children’s Hospital Foundation, and philanthropic donors via the Cure4CF Foundation (www.cure4cf.org). MD is supported by a MS McLeod Fellowship, and KM by an ARC DECRA, a Veski VPRF Fellowship and completed this work with the support of the Technische Universität München Institute for Advanced Study, funded by the German Excellence Initiative and the European Union Seventh Framework Programme under grant agreement n° 291763 and co-funded by the European Union. MD, MA, NF and DP were supported by the Australian Synchrotron Domestic Travel Funding Program.
Availability of data and materials
The data obtained and/or analysed during this study are available from the corresponding author on reasonable request.
MD, DP and KM designed the studies. All authors assisted with the experiments. MD wrote the manuscript, with assistance from KM and DP. All authors read and approved the final manuscript.
The authors declare that they have no competing interests.
Consent for publication
Ethics approval and consent to participate
Animal tissue was collected under a scavenged-tissue permit from the Women’s and Children’s Health Network Animal Ethics Committee.
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