Obstructive sleep apnea (OSA) is characterized by the intermittent and repetitive collapse of the upper airway during sleep with simultaneous respiratory effort. Symptoms such as headache, sleepiness, fatigue, depression and difficulties in keeping concentration are frequent in patients with OSA.1 Even more, OSA has been related to an increased risk of cardiovascular and cerebrovascular diseases, such as systemic hypertension, atrial fibrillation, and cerebral stroke,2–5 as well as to increased mortality.6,7 The key factors involved are the repetitive intermittent hypoxia, the increased sympathetic activity, the sleep fragmentation, and the periodic cerebral hemodynamic changes but further understanding is desirable.8,9
Previously, the apnea-induced changes of cerebral hemodynamics have been studied and characterized by several groups through the measurement of the cerebral blood flow velocity (CBFV) in the middle cerebral artery by transcranial Doppler (TCD).10–14 In Bålfors and Franklin10 study, both CBFV and the mean arterial blood pressure showed a biphasic pattern, where during the apnea a gradual increase of both CBFV and mean arterial blood pressure was observed followed by a sudden drop after the end of the apneic event. These hemodynamic changes are rapid and, therefore, many modalities for CBF measurement are not applicable, limiting the literature to studies, where the macrovascular CBFV was measured by TCD. Few studies have also used microvascular cerebral blood oxygenation measured by near-infrared diffuse optical spectroscopy (NIRS-DOS) as a surrogate.15–18
However, neither TCD nor NIRS-DOS can measure the actual microvascular cerebral blood flow (CBF) in the brain, which is a desirable parameter since it provides direct information about the health of the brain,19 acts as biomarker of cerebral autoregulation,20 and is a key parameter to measure the oxygen metabolism.21–23 This is what led us to adopt an emerging technology, diffuse correlation spectroscopy (DCS), to measure local, microvascular CBF on the brain cortex noninvasively at the bed-side.24,25 DCS utilizes near-infrared light like NIRS-DOS but relies on the speckle statistics of the laser light to characterize red blood cell motion. To the best of our knowledge, only one study attempted to measure night sleep changes by DCS in OSA patients26 but could not characterize individual apneic events, presumably due to technical limitations.
In this study, we have used a DCS device to evaluate and characterize the individual apnea-induced hemodynamic changes of CBF measured continuously in patients with severe OSA simultaneously by using DCS and polysomnography (PSG).
This study was conducted at a referral Sleep Unit (Department of Respiratory Medicine, Hospital de la Santa Creu i Sant Pau) in Barcelona, Spain. The study protocol was approved by the local ethical committee (EC/11/001/1166). All participants gave their informed written consent. It was part of a larger study involving other modalities.
Patients were referred to a sleep study at the unit because of being at a high risk of severe OSA according to the Epworth sleeping scale27 results, other clinical symptoms, and the results of a previous home-use nocturnal pulse oximetry session.28
Those who were older than 80 years, had previous or current continuous positive air pressure (CPAP) treatment,29 had chronic obstructive pulmonary or neuromuscular diseases, a previous ischemic stroke, or who refused to participate in the study were excluded. Demographic and clinical characteristics were obtained for all participants. A pre-established questionnaire was used to collect demographic variables including their medical history, cardiovascular risk factors, and current medications. Diagnosis of arterial hypertension was defined as having systolic blood pressure and/or diastolic blood pressure.30
All patients were asked to arrive at the Sleep Unit at 19:00 on the study date. They were instructed to avoid caffeinated or alcoholic beverages 24 h previously to the measurement. PSG monitors and optical probes were placed as explained below. Concurrent optical and PSG data were acquired during the night sleep.
If the obstructive apnea or hypopnea index (AHI; number of apneas and hypopneas per hour of sleep) was greater than 30 after about 4 h of sleep, the clinical technician fixed a CPAP mouth-nose mask to find the correct air pressure for preventing apneas (called split-night PSG). For those patients with split-night PSG, only the data recording of the first 4 h of night sleep without CPAP were then used for further analysis since there are practically no apneas during CPAP use.
PSG (Siesta Compumedics, Melbourne, Australia) sensors were wirelessly connected to the monitoring room. Among other variables, PSG included the recording of the oronasal flow (by a thermistor and a nasal cannula), the thoracic and abdominal movements (by a respiratory inductance plethysmography band), the heart rate (HR; by electrography chest leads and calculated from the electrocardiogram as described in Ref. 31), and the arterial oxygen saturation (; by pulse oximetry).
PSG data were postprocessed and manually scored by the sleep technicians according to the Spanish Sleep group recommendations,29 which, among other things, describe the rules for scoring respiratory events. Sleep technicians determined the start and end time points of each apneic event, identified the apnea types (i.e., obstructive apnea, hypopnea, mixed apnea, and central apnea) and calculated, among other parameters, the percentage of total sleep time with lower than 90% (CT90), the 4% oxygen desaturation index (ODI4), and the AHI. From these variables, the diagnosis of OSA and the high degree of severity of these patients were confirmed or rejected after our recruitment. Due to the different pathophysiology of each type of apneic event, and for simplicity, only obstructive apneas were used for the analysis of this study.
Determination of the Cerebral Blood Flow by Diffuse Correlation Spectroscopy
Microvascular CBF during the whole night sleep was continuously assessed by a custom-built DCS system that was previously described.25,32,33 Briefly, the DCS consisted of a mode-hope free, long-coherence-length, continuous-wave laser at 785 nm and eight single photon avalanche photodiode detectors, whose outputs were fed to a custom-built hardware autocorrelator. DCS uses the intensity autocorrelation of the diffuse light to evaluate the motion of the scatterers, i.e., the red blood cells.24 The intensity autocorrelation data are then fitted by a physical model of the photon diffusion in tissues to determine a blood flow index (BFI), which is recorded as a continuous variable. The BFI () is not a measure of absolute blood flow in traditional units. Even though under controlled situations, the absolute values are proportional to the absolute blood flow,34 the relative changes are more reliable and have been shown to be quantitative.25,35 Therefore, we report relative changes in this work.
The averaging time of the DCS measurement in each patient was adjusted from 1 to 3 s during the first minutes of the measurement in order to maximize the signal-to-noise ratio for the rest of the sleep measurement. In order to coregister the DCS data with the PSG variables, a transistor–transistor logic signal was generated through a digital output channel, which was fed into the PSG device and was used as a marker to synchronize DCS and all PSG variables.
The optical probe was made of custom built, 90-deg bent fibers of 2 mm of external diameter and consisted of a source fiber of a core of and a detector fiber bundle of four single-mode fibers of a core of . The source–detector separation was 2.5 cm. We have assumed that the hemodynamic changes in the brain are homogeneous bilaterally and, for patient comfort, we opted to fix a single DCS probe on the right forehead of the patient. The probe was placed over the patient’s forehead, properly fixed to avoid the movement of the patient, and allowed the placement and removal of the CPAP mask when necessary with the minimum impact possible on the optical measurement. A black elastic band was attached to the standard CPAP head frame to fix the optical probe and the CPAP mask on the head.
Group and Individual Analysis of Apnea Induced Cerebral Blood Flow, Heart Rate, and Arterial Oxygen Saturation Changes
Individual apneic events were characterized by the percent relative CBF change (), defined as , where is the average of the cerebral BFI from 30 s before the apnea start up to 30 s after the apnea end. This choice for was used to account for the possible changes in the absolute CBF at different stages of sleep and to correct for slight changes in the probe position during the whole night of sleep. We note that we have taken a similar approach to systemic variables too, i.e., was defined as , and was defined as .
In order to discard the CBF, HR, and responses to obstructive apneic events with a low signal quality or with movement artifacts during the measurement, all responses were studied by previously developed methods for outlier detection.36,37 These allowed us to find the responses that exhibited a different time behavior or that presented higher or lower magnitude values than the majority. Also, the outlier detection method36,37 allowed us to reduce the effect of outliers that exist not only due to measurement issues but also because of uncontrolled physiological outliers (e.g., mixture of two events, other physiological alterations). Each variable (CBF, HR, or ) was analyzed independently. For instance, if the response for one apnea was classified as an outlier, it did not imply that and/or response for the same apnea were also classified as outliers. We do not expect this to cause any errors in the data analysis due to the large number of events that were analyzed. The outlier detection procedure was implemented in Ref. 38 using the “fda.usc”37 package and the R function “Outliergram.”36
After removing the outliers from our database, all the remaining apneic events for each variable (, , or ) of all patients were averaged in order to visualize representative cerebral and systemic dynamics of obstructive apneas. The averaging was performed by (1) selecting the start and the end of each apnea based on PSG measurements using the established criteria (see above), (2) calculating the , , or traces for each apnea, as explained previously, (3) aligning the data considering as the pivot point the start of each individual apnea, as shown in Fig. 1(a), and (4) grouping and averaging all apneas within a given range of apnea duration. Four groups were used based on their duration; apneas shorter than or equal to 15 s, apneas longer than 15 and up-to 30 s, apneas longer than 30 and up-to 45 s, and apneas longer than 45 and up-to 60 s. There were apneas of varying lengths in each group and, if an apnea was shorter than the full duration, it did not contribute to the remaining average. This grouping before averaging was done since the apnea lengths vary from 10 s up to around a minute and, even though it is not perfect, grouping by duration allowed us to see more details of the dynamics.
This heterogeneity of the duration of apneas did not allow us to analyze the full duration of the single apnea induced , , or changes. Instead, we have considered the apnea end as a pivot point to calculate each parameter. The parameters associated to each obstructive apneic event were considered as a function dependent on time [ (time), (time), and (time)], and then, the relative extrema of these functions along a specific time interval relative to the apnea end were calculated. The positive extrema are referenced as “peak” values, and the negative as “drop” values. The time windows to find these extrema were from to 15 s for the first extremum on [see Fig. 1(b) as an example], from 0 to 15 s for the , and from 5 to 35 s for the . In order to visualize the possible link between the hypoxemia present in these patients and the CBF, also the second extremum that was outside this window was considered for . These time windows were selected from the literature10,39 and also by visual observation of all the apneas plotted together from to 60 s in order to include the majority of the peak/drop values. This analysis was performed with MATLAB 2012a (Mathworks, Massachusetts).
The association between the calculated , , and extrema to the apnea duration (from the PSG) was analyzed by adjusting a linear mixed-effect model.40 The patient identifier was used as a random factor, the parameter apnea duration was the fixed effect, and the positive and negative extrema (previously defined as “peaks” and “drops”) of the apnea time response on variables , , and were the predictors. The linear mixed-effect analysis was carried out in the R programming language and environment40 using the “nlme” package. The associations between the mean of the previously calculated , , and extrema responses for each patient with gender, age, and body mass index (BMI) (one by one) were analyzed by performing simple linear models. The demographic parameters were the fixed effects and the mean calculated extrema were the predictors. The residuals of the models were checked for linearity by plotting the standard residuals versus the predicted means. Residuals were inspected for deviations from homoscedasticity. Also, residuals were inspected for deviations from normality by means of histograms and also by means of Q–Q plots. The presence of influential data points was also inspected.
The Wilcoxon signed-rank test was used to check if , , and peaks and drops for each grouping of apneas by duration were different from zero.
A was considered to be statistically significant.
We have included 16 patients with high risk of severe OSA. Fourteen patients were studied with a split-night PSG and two patients with overnight PSG. All sixteen patients were diagnosed with severe OSA according to the criteria described above.
The microvascular CBF during the whole night of sleep was continuously assessed by DCS with a range of 0.9 to 3.1 (, ) second time-resolution in order to maximize the signal-to-noise ratio. The time-resolution was decided during a baseline test, as mentioned in Sec. 2. The typical count rate for these patients was from 50 to 150 kHz.
A total of 3817 apneic events were identified including 1365 (36%) obstructive apneic events. The DCS recording in two patients was discarded (14% of total obstructive apneic events) due to synchronization failure between the PSG and the DCS. A part of the HR of different patients was discarded due to low electrocardiogram data quality recording (15% of total obstructive apneic events). The recording in one patient was discarded (9% of total obstructive apneic events) due to the detachment of the pulse oximeter during the main part of the recording. After removing the outliers, 87% obstructive apneic events were considered for the CBF, 90% events for the HR, and 88% events for the . Further clarification of the total of number of apneas considered for the analysis is given in Sec. 5.
Table 1 shows the demographic, clinical, and polysomnographic characteristics of the subjects. The table shows that this is a relatively homogeneous group of patients with a very severe OSA syndrome, commonly associated with a high percentage of cardiovascular and metabolic comorbidity. The severity of OSA syndrome in our cohort is shown by an AHI higher than 30, and high values of CT90 and ODI4. The prevalence of hypertension in our sample was 62.3%, which is consistent with the results of other studies.41 Four patients received beta blockers, which may cause alterations in the HR.42 There was no other relevant use of medications.
Demographic, clinical, and polysomnographic characteristics of the patient population. Values are reported in median (interquartile range) or frequency (%).
|OSA patients (n=16)|
|Age (years)||57 (52–64.5)|
|Males (%)||12 (75)|
|BMI ()||34 (32–37.5)|
|AHT (%)||10 (62.5)|
|Smokers (%)||13 (81)|
|Diabetes (%)||5 (31.25)|
|Dyslipidemia (%)||3 (18.75)|
|AHI (n./h)||85 (76–94)|
|Mean (%)||92 (90.5–93.5)|
|CT90 (%)||23 (12–33)|
|ODI4 (%)||74 (65–85)|
|Total number of apneas detected by PSG||3817|
|Obstructive apneas (%)||1365 (36)|
|Hypopneas (%)||1918 (50)|
|Mixed apneas (%)||358 (9)|
|Central apneas (%)||176 (5)|
As an example of the apnea effect on systemic variables and CBF, Fig. 2 shows 3 min of continuous BFI measurement together with nasal airflow, HR, and changes for one representative patient. BFI has been plotted here instead of , since this is calculated from a specific baseline of each individual apnea, where the baseline corresponds to a preapnea period of 30 s from the start up-to a postapnea period up-to 30 s from the end. From the PSG recording, we can see that shows a drop with a delay relative to the apneic event. In this time period with frequent apneas, characteristic of patients with severe OSA, the drop of the previous apnea is in the apnea period of the next event. It can also be observed that the HR starts to rise when the breathing restarts after a period of cessation. BFI also shows a similar behavior as the HR.
To better understand the general response of CBF to obstructive apneic events, measurements during obstructive apneas were grouped depending on their duration (as explained in Sec. 2) and averaged, as shown in Fig. 3. It can be observed that the mean of the different apnea-duration groups follows a similar pattern: a increase toward the apnea end followed by a drop (in ).
Apnea duration range from 15 up-to 30 s has been chosen for further visualization of the data since it has the highest number of events. The peak observed in CBF in Fig. 3 is also observed in the HR in Fig. 4, whereas the shows a drop. We can also observe in Fig. 2 that cerebral and systemic variables are not constant during preapnea periods. This effect is clearly evident in the peaks/drops right before or at the start of the apnea in Figs. 3 and 4. This is attributed to the presence of a previous apneic event equal or less than 30 s prior to the start of the evaluated event, which was the case for 80% () of all the events detected by PSG, i.e., the subject’s physiology did not yet stabilize. According to this, and following the literature, in order to characterize the response to a given apnea, we have considered only the CBF peaks/drops, HR peaks, and drops near the end of the apnea or in the postapnea period (as explained in Sec. 2).
Figure 5 and Table 2 show the individual data points and average amounts of peaks/drops for cerebral and systemic variables (, , and ) grouped by apnea duration. All , , and peaks and drops for each grouping of apneas by duration were statistically different from zero. Microvascular CBF increased by a mean of at the end of the event followed by a drop of . HR, as expected, increased by . Also, , as expected, decreased by .
Mean±standard deviation values for the amount of the peak or drop close to the apnea end for the different apneas grouped by their duration and for all apneas.
|Apnea duration (s)||ΔrCBF||ΔrHR||ΔSpO2|
|n (%)||Peak (%)||Drop (%)||n (%)||Peak (%)||n (%)||Drop (%)|
|130 (13)||116 (11)||126 (11)|
|to||618 (62)||681 (65)||697 (64)|
|to||238 (24)||236 (23)||258 (24)|
|to||16 (1)||7 (1)||7 (1)|
|All,||1002 (100)||1040 (100)||1088 (100)|
When fitting a linear model with the peak or the peak as the dependent parameter and the apnea duration as the predictor parameter, positive statistically significant associations ( and , respectively) were found () for both dependent parameters. When the dependent parameter was the drop or the drop, negative statistically significant associations ( and , respectively) were found () for both dependent parameters. Females, in comparison to males, showed a larger CBF response (, ). Older age was associated to smaller a response (, ). No statistically significant associations were found with the BMI ().
In this work, we have demonstrated the successful assessment of microvascular CBF during individual obstructive apneic events by noninvasive, continuous DCS measurements. All subjects tolerated the study during the whole-night sleep showing the suitability of the technique for bed-side continuous CBF monitoring over long time periods and its compatibility with standard PSG monitoring.
Our first finding was that DCS results had the sufficient contrast-to-noise ratio in order to enable us to measure the dynamics of microvascular CBF during obstructive apneic events in a synchronized manner with systemic variables, as illustrated in Fig. 2. HR and followed the expected dynamics according to the literature.15,16,39,43 CBF showed a similar behavior as HR. There is only one study that has also measured microvascular CBF in OSA patients continuously with DCS26 during night sleep. However, apnea cerebral hemodynamics were not characterized, instead, only 2-min time periods with apneas and 2-min time periods with no apneas were compared in order to see altered variability of the microvascular hemodynamics with or without apneas.
Our second finding revealed a steep rise and a peak of microvascular toward or after the end of an apnea, followed by a drop. Figure 4 indicates that the and traces are similar and are in-phase. This could suggest that we are primarily measuring the extracerebral contributions instead of the cerebral contribution, since, in principle, cerebral signals are not directly driven by heart-rate changes, i.e., the cerebral signals are autoregulated. However, the literature supports this type of correlation between HR changes and the cerebral signals during an apnea. For example, the reported microvascular CBF changes measured by DCS follow the same patterns of those of middle cerebral artery CBFV measured by TCD10,13,14 showing a peak close to the end of the apnea. In addition to the similarity of their temporal profile, these and CBFV peaks are in agreement within variability of the both methods. The peak change in CBFV right after the apnea end by Bålfors and Franklin10 is similar to our microvascular values of for obstructive apnea, as can be seen in Table 2. Also, Alex et al.13 found similar peaks in CBFV of 22% to 42%. However, other authors have reported larger CBFV peaks. Klingelhöfer et al.11 found changes of CBFV of 19% to 219% and Siebler and Nachtmann14 found a mean CBFV peak during apnea of 142% compared with the baseline CBFV. The differences of these last studies with our results may be related to the longer apnea durations and to different normalization of the data. The drops after the apnea end are also in agreement with the CBFV drops found in the bibliography.10,11 These results tell us that there is a decrease in cerebral perfusion due to an apneic event. If these intermittent decreases lead to ischemia, they can cause hypoxic/ischemic brain injury, especially if cerebrovascular reactivity and regulation are impaired.44
Another point about the extracerebral contamination is that DCS in adult brain with this source–detector separation has been validated against other measures of CBF in different studies, where it was demonstrated that the relative changes in different challenges follow the intracerebral signals closely.25,45–47
However, despite these arguments, we cannot rule out the possibility that microvascular and macrovascular changes diverge and that extracerebral signals have strongly impressed themselves on the DCS signals. Future studies are needed to study this point.
We have observed (Figs. 2 and 3) that cerebral hemodynamics in the pre- and during-apnea periods are not stable as it has been previously observed due to the influence of the previous apnea.15,16,39,43 80% () of the total events (i.e., obstructive apneas, mixed apneas, hypopneas and central apneas) are followed by the next episode within 30 s or less, hence, we expect that the effects of the previous events overlap with the next apnea. This is because the rapid succession of events does not allow ample time for the physiology to recover as observed by Bålfors and Franklin,10 where they have reported that it took up to 60 s for CBFV to return to baseline after the apnea termination.
We have attempted to resolve this by isolating apneas by forcing different lengths of minimum gaps between the events, however, in this group of patients with a severe condition, due to the high frequency of repetitive events, only a small group of apneas could be isolated, as shown in Fig. 6, and no final conclusions could be drawn about what would have happened if there had been no overlapping apneas.
The CBF peak and drop amplitudes that are characteristic of each apneic event were associated with the apnea duration. The association of the peak with the apnea duration has also been observed previously for CBFV in the middle cerebral artery.13 About the systemic variables, a correlation of desaturation depth with apnea duration has been observed previously by several authors.48,49 Also, the abrupt HR increase immediately after obstructive apnoeas has been documented,50 and recently, in a preliminary work, we have already observed a correlation between HR excursion and the duration of apneas.31 These results tell us that the longer the apnea duration, the bigger is its effect on systemic variables, but also, on the microvascular cerebral hemodynamics.
About the gender effect that was observed, where females showed larger CBF responses, this is in contrast to Edlow et al.,51 who has reported a smaller CBF response to HOB manipulation for females in the healthy population. It is difficult to know whether this is due to a smaller head circumference and a smaller scalp-to-brain-distance, hence a smaller extracerebral effect or not. We also note that we did not observe a BMI effect. However, Peppard et al.52 observed an association between BMI and decreases. The BMI was quite homogeneous for our group (32 to 37.5), which may have hidden this relationship. About the age effect that was observed, older age has already been associated to smaller apnea responses, as predicted in the literature.53
Finally, we have discarded several apneas (13% for CBF, 10% for HR, and 12% for ; see Sec. 5) as outliers. Similar percentages of apneas were removed between CBF and the PSG variables (HR and ) and, therefore, these support the idea that the DCS signal has the quality needed in the clinics.
Our study has some potential limitations that should be taken in consideration. First, the contribution from the extracerebral tissues could not be assessed independently since our probe lacked a short source–detector separation. A multidistance source–detector separation probe and pressure modulation algorithms54 should be considered in future studies. We do note that a source–detector separation of 2.5 cm has been found to be a good compromise and was validated in numerous studies.25,47,46 Second, the absorption and reduced scattering coefficients have been considered as constant along the study. While significant changes in the reduced scattering coefficient can affect the DCS results, they are not expected during an apnea. The changes in the absorption coefficient due to an apnea have a minimal effect on the DCS signal.24,47 Third, there are additional factors to consider to go deeper into the physiology of the relationship between the systemic physiology and microvascular CBF changes, such as the effects of different sleep states, arousals, leg movement, and others sleep events. The detailed analysis is beyond the scope of this paper and will be a point of future studies. Finally, our findings correspond to a group of patients with very severe OSA, which implies that these results are not necessarily extrapolated to the different OSA severities. However, at the same time, it strengthens the validity of our results for patients with severe OSA.
In summary, we have demonstrated that DCS is a suitable technology for bedside and continuous monitoring of the microvascular during sleep. We were able to obtain sufficient signal-to-noise ratio to reveal the dynamics and the canonical shape of the microvascular CBF changes. We were then also able to characterize each CBF peak and the following drop in each obstructive sleep apneic event, as well as to visualize the apnea-induced cerebral and systemic hemodynamics simultaneously in patients with severe OSA. This work, to our best knowledge, is the first characterization of the microvascular CBF during an OSA.
Not all the apneic events detected by the PSG technique have been used for the data plotting and analysis. Table 3 shows the different steps from the initial number of apneas detected by the PSG to the final number of apneas considered.
Total number of apneas considered from the PSG detection and the apneas considered for the analysis for different steps. The total number of events remaining after each step and its percentage (%) are reported. Step 1, total events detected by PSG. Step 2, obstructive apneic events detected by PSG. Step 3, obstructive apneic events detected by PSG and recorded by each technique. Step 4, obstructive apneic events detected by PSG and recorded with each technique after removing the outliers.
|1||Total apneas detected by PSG, (%)||3817 (100)||3817 (100)||3817 (100)|
|2||Obstructive apneas detected by PSG, (%) of step 1||1365 (36)||1365 (36)||1365 (36)|
|3||Obstructive apneas, (%) of step 2||1150 (84)||1161 (85)||1239 (91)|
|4||Obstructive apneas after outlier removal, (%) of step 3||1002 (87)||1040 (90)||1088 (88)|
Herewith, the following current or potential financial relationships are disclosed. ICFO has equity ownership in the spin-off company HemoPhotonics S.L., that has pushed the commercialization of this technology. Potential financial conflicts of interest and objectivity of research have been monitored by ICFO Knowledge & Technology Transfer Department. No financial conflicts of interest were identified.
The authors thank Dr. Raquel Delgado Mederos, Dr. Joan Martí Fàbregas, Ivan García Domínguez, Ignasi Jorba, Nuray Aysan, and Rosa Maria Miralda for their discussions and contributions to some of the software used for analysis. This work was funded by Fundació CELLEX Barcelona, Institució CERCA/Generalitat de Catalunya, Ministerio de Economía y Competitividad/FEDER (Grant Nos. PHOTODEMENTIA, DPI2015-64358-C2-1-R, DPI2015-68820-R, and FIS2015-71851-P), Instituto de Salud Carlos III/FEDER (Grant Nos. MEDPHOTAGE and DTS16/00087), the “Severo Ochoa” Programme for Centres of Excellence in R&D (Grant No. SEV-2015-0522), the Obra Social “la Caixa” Foundation (Grant Nos. LlumMedBcn, Programa de Matemàtica Col·laborativa), AGAUR-Generalitat (Grant Nos. 2017SGR-1380, 2014SGR-1307, GRC-2014 SGR-1569), LASERLAB-EUROPE IV (Grant No. EU-H2020 654148), Marie Curie initial training network (Grant No. OILTEBIA 317526), Societat Catalana de Pneumologia (SOCAP), and Sociedad Española de Neumología y Cirugía Torácica (SEPAR).
Peyman Zirak obtained his PhD degree in the Laboratory of Professor Alfons Penzkofer at University of Regensburg, Germany. As postdoctoral researcher in the laboratories of Professor Turgut Durduran at ICFO-The Institute of Photonic Sciences, Spain, he worked on (pre-) clinical application of diffuse optical modalities. Currently, as a research fellow of Professor Andreas Zumbusch at University of Konstanz, Germany, he works on nonlinear optical microendoscopy and waveform shaping to access deeper tissue while imaging.
Clara Gregori-Pla is a doctoral student in the group Medical Optics at ICFO-The Institute of Photonic Sciences, Spain. She received her master’s degree in engineering physics in Biomedical Physics at the Royal Institute of Technology, Sweden. Her research is focused on developing diffuse optical instrumentation, algorithms and protocols and applying them for clinical studies.
Igor Blanco received his PhD degree from ICFO-The Institute of Photonic Sciences, Spain, researching within the medical optics group, the cerebral hemodynamics in experimental and clinical neurology, under the supervision of Professor Durduran. He is currently leading a data science team in the private consulting sector.
Ana Fortuna obtained her PhD degree in medicine in the Universitat Autònoma de Barcelona in 2006. She is a specialist in respiratory medicine (PhD since 2014). She works in the Sleep-Disordered Breathing Unit and the Pulmonary Function Unit (Hospital de la Santa Creu i Sant Pau, Barcelona), in which she has professional experience as a clinician and as a researcher. She conducts basic and clinical research in sleep disorders as a member of the Spanish Sleep Network.
Gianluca Cotta is a medical doctor, who obtained his training in pneumology at Hospital de la Santa Creu i Sant Pau, Barcelona, in 2014. He studied a master in scientific research methodology at Universitat Autònoma de Barcelona. He is currently working in a hospital as a pneumologist.
Pau Bramon received his master’s degree in telecommunications engineering at UAB—Universitat Autònoma de Barcelona, Spain, and worked for three years as a development and startup engineer in the industrial automation sector. He is currently studying a master’s degree in artificial intelligence at UPC—Universitat Politècnica de Catalunya.
Isabel Serra received her PhD degree from UAB—Universitat Autònoma de Barcelona, Spain, researching within the development statistical techniques in analysis of rare events. She leads the knowledge transfer unit at Centre de Recerca Matemàtica (CRM), she is collaborator researcher in complex system group at CRM and senior researcher at Computer Architecture/Operating System group at BSC-Barcelona Supercomputing Center.
Anna Mola is a medical clinician, who completed her respiratory specialty in Hospital de la Santa Creu i Sant Pau, Spain. Her research was focused in sleep respiratory disorders and its relationship with stroke and with cerebral hemodynamics. She is currently working as a respiratory doctor.
Jordi Solà-Soler is a collaborator professor of automatic control at Technical University of Catalonia, and a senior researcher at Biomedical Signal Processing and Interpretation group from the Institute for Bioengineering of Catalonia. His research interests include statistical signal analysis of breath sounds, polysomnographic and cardiovascular signals from subjects with sleep disorders and cardiac pathologies.
Beatriz F. Giraldo-Giraldo is an associate professor of automatic control and statistical analysis of biomedical signal processing at Technical University of Catalonia. She is a senior researcher at Biomedical Signal Processing and Interpretation, Institute for Bioengineering of Catalonia, and of the Spanish Research Center CIBER-BBN. Her main research interests include biomedical signal processing and statistical analysis, especially in cardiovascular and cardiorespiratory systems, applying linear and nonlinear techniques to characterize and analyze their behavior and dynamics.
Turgut Durduran was trained at the University of Pennsylvania. In 2009, he moved to ICFO-The Institute of Photonic Sciences, Spain, where he leads the medical optics group. His research interests revolve around the use of diffuse light to noninvasively probe tissue function. The group develops new technologies and algorithms and routinely translates them to preclinical, clinical, and industrial applications.
Mercedes Mayos obtained her PhD degree in medicine at the Universitat Autònoma de Barcelona, Spain, where she is now an associate professor. She is a specialist in pneumology. She coordinates the Sleep Disorders Unit and leads the Pulmonary Function Unit in the Hospital de la Santa Creu i Sant Pau, Spain. Her research and work interests are related to respiratory sleep disorders and new study methods and clinical impact of obstructive sleep apnea-hypopnea syndrome.