# A Device for Respiratory Monitoring during Nutritive Sucking: Response to Neonatal Breathing Patterns

Authors: Andrea Rosi; Emiliano Schena; Carlo Massaroni; Eleonora Tamilia; Domenico Formica; Fabrizio Taffoni
Journal: Journal of Sensors
 (2016)

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## Abstract

The quantitative monitoring of breathing, sucking, and swallowing is required to predict newborns’ neurodevelopmental outcomes. In particular, the coordination of breathing timing with respect to sucking cycle is crucial. In this work, we present the characterization of a low-cost flowmeter designed for noninvasive recording of breathing pattern during bottle feeding. The transducer is designed to be integrated on a commercial feeding bottle also instrumented with a system for sucking monitoring. The flowmeter consists of two transistors (hot bodies) supplied at constant current, which are placed in a duct used to convey the inspiratory and expiratory flow coming from the newborn’s nostrils. The transducer design, its static calibration, and its response time are discussed. Moreover, a custom-made active lung simulator was used to perform a feasibility assessment of the proposed flowmeter for respiratory monitoring of neonatal respiratory patterns. The flowmeter has a discrimination threshold <0.5 L·min−1 and a response time of 347±12 ms. The breathing period estimated by the proposed transducer was compared with the one measured by a high performance flowmeter, used as reference: the mean absolute error was <11%. Results highlighted the ability of the device to track respiratory patterns at frequencies typical of neonatal breathing.


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## Body

## 1. Introduction

Coordination of sucking, swallowing, and breathing represents a key competency necessary to develop an efficient and effective nutritive sucking (NS). Its lack may cause aspiration and apnea with short-term clinical problems (as pulmonary diseases) and long-term consequences, as delays in neonatal growing and neurodevelopment [1]. Indeed, a modified neural control of feeding and swallowing may significantly alter the structure and function of the developing brain, delay the attainment of oral-motor skills such as nutritive sucking (NS), and negatively impact the transition to oral feeds [2, 3]. This is particularly true in preterm and low-birth-weight newborns, who often present problems with autonomous feeding that may be related to the immaturity of their Central Nervous System (CNS) [1–6].The assessment of feeding performance is widely recognized as very important for discharge timing and as a prospective indicator of medical and developmental progress (or problems) in the weeks after discharge and in later infancy. Yet, in common practice, neonatal feeding assessment is most often highly subjective, with substantial variability of practices across neonatal nurseries.Several studies have discussed the problem of the objective study of NS from both technological [7] and clinical point of view [8] and highlighted the importance of the concurrent assessment of sucking, breathing, and swallowing to analyze the relation among them.Breathing during NS has been analyzed using different commercial devices as Fleisch and screen pneumotachographs, ultrasonic flowmeters, variable orifice meters, and hot wire or hot film anemometers [9, 10]. One of the most common methods used to evaluate nasal airflow and breathing employs a thermistor or a thermocouple placed in a duct below or just inside the nostrils [11, 12].Many authors have proposed monitoring breathing through the assessment of thoracic movements using mercury-in-rubber and piezo-resistive strain gauges (respiratory bands) placed over the chest and the abdomen [13–15]. More recently, smart textiles based on optical fiber sensors have been proposed to enable respiratory monitoring during Magnetic Resonance Imaging procedures [16]. Our team recently proposed a novel sensor for neonatal breathing monitoring during bottle feeding [17]. Our main goal is to assess the coordination of breathing and sucking during feeding. Feeding is an aerobic activity characterized by a typical alternation of sucking and breathing cycles, which may be modified in preterm and low birth weight infants. This temporal alteration impairs the sucking efficiency and reduces the time spent by the newborn attempting to feed since she/he tires faster.In this work, after an overview of the working principle, the design, and the fabrication of the sensor (Section2), we focused on its experimental characterization (Section 3). In particular, we assessed its response time and its ability to estimate the respiratory period simulating typical neonatal breathing patterns. Future testing will evaluate the potential to integrate the investigated transducer with a portable system previously developed to assess sucking pressures in newborns [18, 19].


## 2. Theoretical Background and Sensor Design

The proposed transducer is based on the heat exchange between the surfaces of two hot elements (i.e., two transistors) and the gas exhaled and inhaled by the infant (see Figure1). Thermal sensors have previously been used to estimate breathing flow from heat exchange (see [20]), but this method has been studied further in recent works [21, 22]. In this paper we propose a specific application of this measuring principle to neonatal breathing monitoring. In particular, the proposed sensor detects the gas flow during the breathing phases, thanks to the dependence of the base-emitter voltage (Vbe) on the base-emitter temperature (Tbe) [23, 24] which depends in turn on the velocity of the hitting gas. In steady-state conditions, the transistors, placed in a constant fluid stream at temperature Tf, reach a superficial equilibrium temperature Tbe depending on the heat flow (Q) exchanged with the fluid [17]. Thus, Vbe can be expressed as a function of the fluid mean velocity (v):(1)Vbev=a+bQSA+Bρv+Tf.The coefficients a and b are constant and b is the thermal sensitivity of Vbe (≈-2 mV/K). A and B are two calibration parameters, ρ is the fluid density, and S is the exchange surface. Two NPN transistors have been placed in the midline of a cylindrical duct, as shown in Figure 1(a). When the gas directly hits the transistor Tr1, its PCB shields the transistor Tr2. In this case, the Tr1 reaches an equilibrium temperature lower than the one of Tr2. The difference between their Vbe values can be expressed as(2)ΔVbev1,v2=bQ1SA+Bρv1-Q2SA+Bρv2,where v1 and v2 are the velocities of the gas hitting Tr1 and Tr2, respectively.Figure 1
(a) Schematic representation of the hot bodies (two transistors, Tr1 and Tr2) inside the duct; (b) assembly of mechanical components: (A) duct inserted into the air conveying system with PCBs support and (B) duct support.
(a)
(b)Under laminar flow conditions (Re<2000), v1 is similar to vmax (maximum gas velocity in the duct), where it is about equal to 2v in a cylindrical duct. This hypothesis is justified by the geometry of the duct and the delivered flows described in detail in Section 3. Assuming v2 negligible, Q1=Q2=Q, and expressing the difference ΔVbe in terms of volumetric flow rate, (2) becomes(3)ΔVbeF=bQSA+Bρ2F/O-QSA,where O is the duct cross section and F=Ov.This configuration guarantees that one transistor is always directly hit by the gas during all breathing phases and so it allows an effective estimation of the breathing period.The transducer is composed of two nominally identical NPN bipolar junction transistors (PBSS2515M, Philips), in a SOT883 package (0.50 mm × 1.02 mm × 0.62 mm) with a default base-emitter temperature junction of 150°C and a maximum current collector of 500 mA [24]. The transistors, used as hot bodies, are supplied by a constant current in common emitter configuration. The two Vbe are preprocessed by a low distortion operational amplifier in a differential configuration with unit gain (TL074CN, Texas Instrument); then ΔVbe is amplified (G=51) by an instrumentation amplifier (INA101HP, Texas Instrument); see Figure 2. The amplification gain is set to work in the linearity region of the amplifier (Vs=±12 V).Figure 2
Schematic representation of the electric circuit (R1, R2, R3, R4≈22 kΩ, Vout=GΔVbe) to condition signals coming from the BD.The two transistors are soldered on two identical PCBs positioned inside a duct at a distance of 1 mm (Figure1(a)); this configuration enables (i) reducing cross-talk due to heat conduction between the transistors and (ii) shielding the transistor which is not directly hit by the air flow during breathing. This geometry is designed to be easily integrated into a commercial feeding bottle (angle Well-Being Chicco, Artsana S.p.A.), thus enabling the ecological monitoring of breathing during NS. The end of the duct is connected to a mask designed to match the profile of the feeding bottle and to convey the air during breathing (Figure 1(b)). These mechanical components were designed in SolidWorks and built using a rapid prototyping printer (Project 3000 by 3d Printer Inc.) to test the system in laboratory. Air conveying made by soft rubber disposable material will be used with infants in the final application.


## 3. Characterization of the Device

To verify that the theoretical model presented in (3) correctly predicts the actual output of the BD sensor, preliminary experiments have been carried out. BD sensor was supplied at constant operating current (500 mA) and connected to a mass flow controller (F-201C-FBC-22-V, Bronkhorst High-Tech) by a plastic duct (30 mm of diameter), which avoids any flow leakage. We delivered the following values of flow rates: 0 L/min, 0.1 L/min, 0.2 L/min, 0.5 L/min, 1 L/min, 1.5 L/min, 2 L/min, and 2.5 L/min. The output of the BD sensor was used to fit the model of (3); see Figure 3. This preliminary analysis confirms the model (R2=0.9913) and provides a calibration curve for the sensor.Figure 3
B
D
o
u
t as a function of flow rate and theoretical model fitting the simulation data.The sensing elements, presented in the previous section, and the mechanical arrangement, properly designed to enable breathing monitoring during oral feeding (as shown in Figure1(b)), were tested in order to assess the following features of the system: (i) the discrimination threshold, (ii) the step response, and (iii) the capacity to estimate the breathing period of different respiratory patterns.The sensing elements were embedded in the air conveying system in order to develop an integrated module to be used during bottle feeding. This breathing device (BD) was interfaced with a nostril simulator made by two pipes of 5 mm diameter and 15 mm length; the distance between their centers was 8.5 mm according to anatomical data [25–27]. The pipes were inserted in a plastic support (Figure 4(b)(C)), which can be used to interface the BD with different testing setups as shown in Figure 4(a). The transducer output (Vout) was acquired using a data acquisition board (DAQ NI USB-6009, National Instruments) at 1 kHz and sent to a remote laptop for data processing.Figure 4
(a) Schematic representation of the setups used to characterize the BD features. (b) Experimental setup with nostril simulator: (A) wood framework (34.5 cm × 13 cm × 14.5 cm), (B) device with air conveying system, (C) simulated infant’s nostrils, and (D) flow meter (4121 TSI).
(a)
(b)In the following subsections, we present the different testing setups used to assess the BD features.


### 3.1. Estimation of Discrimination Threshold

A mass flow controller (F-201C-FBC-22-V, Bronkhorst High-Tech) was used to deliver constant flow rates (Figure4(a)(A)) ranging from 0.1 L·min−1 to 7 L·min−1 [28]. Since during bottle feeding the relative position of the nostrils with respect to the BD may change, the discrimination threshold has been investigated placing transducer at three distances (10 mm, 20 mm, and 30 mm) and at three tilt angles (10°, 20°, and 30°) with respect to the simulated nostrils. Distances and tilt angles are illustrated in Figure 5. A micropositioners system (PT1A-1′′ Translation Stage, Thorlabs; tilt angle regulator M-481-A series, Newport) was used to adjust the experimental setup in the different configurations.Figure 5
Schematic representation of tilt angles and distances investigated:d is controlled by a translational micropositioner; tilt angles are set using an angular micropositioner, where O is the rotation center.The distance range investigated allows covering all the working conditions: the minimum distance corresponds to the average distance between the nose and the upper lip of infant as reported in [25–27]; the maximum distance is suggested by the geometry of the considered teat. Angles bigger than 30° were not investigated as the considered feeding bottle already has its own 30° tilt. Therefore, these ranges allow covering all the angles and distances, which can occur during bottle feeding [17].


### 3.2. Step Response Analysis

To assess the step response of the BD, we used an on/off valve (Series 821-2/2 NC, Matrix) coupled with a driving circuit, described in detail in [29] (see Figure 4(a)(B)). A flow rate step was delivered by connecting the valve to a pressurized source and quickly opening or closing the valve’s orifice. Thanks to the reduced valve switching time (<0.45 ms), nominally ideal steps were generated. The electromechanical valve was driven by square waves (frequency 0.2 Hz, amplitude 3 V) supplied by a function generator (FG120, YOKOGAWA).A PVC tube 160 mm in length and 16.7 mm in diameter, embedding the transistors, was connected to the valve.


### 3.3. Estimation of the Breathing Period during Simulated Neonatal Respiratory Patterns

We assessed the capability of the transducer to estimate the breathing period by delivering different respiratory patterns using a custom-made active lung simulator (ALS) [30]; see Figure 4(a)(C). The ALS is able to deliver flows similar to neonatal respiratory patterns in a wide range of frequencies and tidal volumes. In this work we simulated 30 breaths per minute (bpm), 39 bpm, 45 bpm, and 60 bpm [25] at two inspiratory : expiratory ratios (I : E) (i.e., 1 : 1 and 1 : 2) and a fixed tidal volume of 24 mL (i.e., 8 mL/kg for neonatal application) [1]. The results of the BD have been compared with the ones of a fast monodirectional commercial flowmeter (4121 TSI, accuracy of 2% of measured value, range of measurement up to 20 L/min, and response time of 4 ms), used as reference (Figure 6).Figure 6
Experimental setup to evaluate respiratory patterns: (A) ALS, (B) flow meter 4121 TSI, (C) simulated infant’s nostrils, (D) BD, and (E) electronic board for BD signal conditioning.In each trial, ten respiratory acts have been recorded to analyze the repeatability of the system. The flowmeter and BD outputs were recorded using a sampling frequency of 1 kHz. Moreover, data have been postprocessed using a virtual low-pass filter (cut-off frequency of 25 Hz).We estimated the breathing period of the two systems (TSI and BD), defined as the time between two consecutive local maxima in the corresponding output signal. The peaks were identified by a specific Matlab® function (findpeaks); see Figure 7.Figure 7
On (a), a block diagram for breathing period detection and comparison; on (b), an experimental trial of ten acts performed at 0.5 Hz (I : E = 1 : 1) (TBD, TTSI are the periods estimated from BD and flowmeter, resp.).
(a)
(b)While the temporal pattern of the signal is preserved, the BD sensor underestimates the flowrate. Actually, this underestimation cannot be considered a measurement error of the BD, but it is the result of two main causes: (i) air leakage between the nostrils and the air conveying system; (ii) attenuation due to the dynamic response of the BD sensor.


## 3.1. Estimation of Discrimination Threshold

A mass flow controller (F-201C-FBC-22-V, Bronkhorst High-Tech) was used to deliver constant flow rates (Figure4(a)(A)) ranging from 0.1 L·min−1 to 7 L·min−1 [28]. Since during bottle feeding the relative position of the nostrils with respect to the BD may change, the discrimination threshold has been investigated placing transducer at three distances (10 mm, 20 mm, and 30 mm) and at three tilt angles (10°, 20°, and 30°) with respect to the simulated nostrils. Distances and tilt angles are illustrated in Figure 5. A micropositioners system (PT1A-1′′ Translation Stage, Thorlabs; tilt angle regulator M-481-A series, Newport) was used to adjust the experimental setup in the different configurations.Figure 5
Schematic representation of tilt angles and distances investigated:d is controlled by a translational micropositioner; tilt angles are set using an angular micropositioner, where O is the rotation center.The distance range investigated allows covering all the working conditions: the minimum distance corresponds to the average distance between the nose and the upper lip of infant as reported in [25–27]; the maximum distance is suggested by the geometry of the considered teat. Angles bigger than 30° were not investigated as the considered feeding bottle already has its own 30° tilt. Therefore, these ranges allow covering all the angles and distances, which can occur during bottle feeding [17].


## 3.2. Step Response Analysis

To assess the step response of the BD, we used an on/off valve (Series 821-2/2 NC, Matrix) coupled with a driving circuit, described in detail in [29] (see Figure 4(a)(B)). A flow rate step was delivered by connecting the valve to a pressurized source and quickly opening or closing the valve’s orifice. Thanks to the reduced valve switching time (<0.45 ms), nominally ideal steps were generated. The electromechanical valve was driven by square waves (frequency 0.2 Hz, amplitude 3 V) supplied by a function generator (FG120, YOKOGAWA).A PVC tube 160 mm in length and 16.7 mm in diameter, embedding the transistors, was connected to the valve.


## 3.3. Estimation of the Breathing Period during Simulated Neonatal Respiratory Patterns

We assessed the capability of the transducer to estimate the breathing period by delivering different respiratory patterns using a custom-made active lung simulator (ALS) [30]; see Figure 4(a)(C). The ALS is able to deliver flows similar to neonatal respiratory patterns in a wide range of frequencies and tidal volumes. In this work we simulated 30 breaths per minute (bpm), 39 bpm, 45 bpm, and 60 bpm [25] at two inspiratory : expiratory ratios (I : E) (i.e., 1 : 1 and 1 : 2) and a fixed tidal volume of 24 mL (i.e., 8 mL/kg for neonatal application) [1]. The results of the BD have been compared with the ones of a fast monodirectional commercial flowmeter (4121 TSI, accuracy of 2% of measured value, range of measurement up to 20 L/min, and response time of 4 ms), used as reference (Figure 6).Figure 6
Experimental setup to evaluate respiratory patterns: (A) ALS, (B) flow meter 4121 TSI, (C) simulated infant’s nostrils, (D) BD, and (E) electronic board for BD signal conditioning.In each trial, ten respiratory acts have been recorded to analyze the repeatability of the system. The flowmeter and BD outputs were recorded using a sampling frequency of 1 kHz. Moreover, data have been postprocessed using a virtual low-pass filter (cut-off frequency of 25 Hz).We estimated the breathing period of the two systems (TSI and BD), defined as the time between two consecutive local maxima in the corresponding output signal. The peaks were identified by a specific Matlab® function (findpeaks); see Figure 7.Figure 7
On (a), a block diagram for breathing period detection and comparison; on (b), an experimental trial of ten acts performed at 0.5 Hz (I : E = 1 : 1) (TBD, TTSI are the periods estimated from BD and flowmeter, resp.).
(a)
(b)While the temporal pattern of the signal is preserved, the BD sensor underestimates the flowrate. Actually, this underestimation cannot be considered a measurement error of the BD, but it is the result of two main causes: (i) air leakage between the nostrils and the air conveying system; (ii) attenuation due to the dynamic response of the BD sensor.


## 4. Results

### 4.1. Discrimination Threshold

Measurements have been performed for each air flowrate and for no-flow conditions. For each measurement, lasting 5 s, the averageVout was estimated. Data acquired in no-flow conditions were compared with the ones acquired in case of flow using a t-test (sample = 8). The discrimination threshold was considered as the lowest flowrate for which the t-test identifies a significant difference (p<0.05).Results show that the discrimination threshold mainly depends on the tilt angle. In particular in optimal conditions (10° < tilt < 20°), the BD has a discrimination threshold < 0.5 L·min−1, lower than the infant’s minimum expiratory peak (i.e., 1 L·min−1) [31]. A relevant decrease of performances happens at 30° (see Table 1); however, this value represents a borderline case of employment in this kind of application.Table 1
Estimated threshold [L·min−1] for the three tilt angles and distances investigated.
Distance [mm]
Tilt angles [°]
10°
20°
30°
10
0.2
0.3
2
20
0.2
0.3
6
30
0.2
0.3
7


### 4.2. Step Response

Experiments were repeated five times to assess the step response of the BD. The BD output was exponential (see Figure8(a)); hence we modeled the BD as afirst order system and we estimated the response time (τ) using the function error Γ:(4)Γt=BDoutt-BDout∞BDout0-BDout∞=e-t/τ,where V(t) is the output at time t, V0 is the output at t=0, and V∞ is the steady-state output. We evaluated the error function in 8 time instants (starting from t=0, with steps of 250 ms). According to our hypothesis, the natural logarithm of Γ results linearly related to time: Figure 8(b) shows both experimental data (blue asterisks) and linear fitting (red line) obtained in one of the five experiments. τ was calculated as the reciprocal of the angular coefficient of the red line. By averaging the values from all the experiments, τ became equal to 347±12 ms. The uncertainty was calculated using a Student reference distribution with four degrees of freedom and a 95% level of confidence, as recommended in [32].Figure 8
(a) Step response of the BD sensor; (b) error function assessed in 8 different time instants. Blue asterisks represent the experimental measures while the red line represents the liner fitting (r=0.9947).
(a)
(b)


### 4.3. Breathing Period Estimation

We did not consider the configuration at 30° of tilt since the discrimination threshold measured for this inclination does not allow an effective monitoring of breathing during sucking (see Section4.1). Among the other possible configurations, we decided to investigate the one with the worst discrimination performance, that is, the 20° tilt angle configuration at the three distances (10 mm, 20 mm, and 30 mm).We estimated the error in measuring the breathing period evaluating the mean absolute error (MAE) between the breathing period measured by BD (TBD) and the one measured by TSI (TTSI) as reported in [33]:(5)MAE=1n∑i=1nTBD-TTSI,where n is the number of acts (i.e., 10). This error has been reported in percentage as (6)MAE%MAEmeanTTSI∗100.The maximum MAE [%] was 10.7% and it was measured at 30 bpm, with I : E = 1 : 2. The overall results are reported in Table 2. Figures 9 and 10 show the two different breathing patterns assessed by BD and TSI, respectively.Table 2
Estimated MAE [%] for all frequencies and distances investigated.
Frequencies [bpm]/[Hz]
MAE [%]30 mm
MAE [%]20 mm
MAE [%]10 mm
I : E = 1 : 1
30/0.50
9.1%
4.1%
3.4%
39/0.65
5.4%
3.8%
5%
45/0.75
4.2%
5%
3.7%
60/1.00
5.1%
4.6%
4.3%
I : E = 1 : 2
30/0.50
9.3%
10.7%
6.2%
39/0.65
4.4%
7.4%
2.5%
45/0.75
2.7%
6%
3.3%
60/1.00
4.1%
3.1%
4.2%Figure 9
Ten acts set at 0.5 Hz (30 bpm) with two different I : E ratios (the red line is the BD output and the blue one is the TSI output, resp.).Figure 10
Ten acts set at 1 Hz (60 bpm) with two different I : E ratios (the red line is the BD output and the blue one is the TSI output, resp.).


## 4.1. Discrimination Threshold

Measurements have been performed for each air flowrate and for no-flow conditions. For each measurement, lasting 5 s, the averageVout was estimated. Data acquired in no-flow conditions were compared with the ones acquired in case of flow using a t-test (sample = 8). The discrimination threshold was considered as the lowest flowrate for which the t-test identifies a significant difference (p<0.05).Results show that the discrimination threshold mainly depends on the tilt angle. In particular in optimal conditions (10° < tilt < 20°), the BD has a discrimination threshold < 0.5 L·min−1, lower than the infant’s minimum expiratory peak (i.e., 1 L·min−1) [31]. A relevant decrease of performances happens at 30° (see Table 1); however, this value represents a borderline case of employment in this kind of application.Table 1
Estimated threshold [L·min−1] for the three tilt angles and distances investigated.
Distance [mm]
Tilt angles [°]
10°
20°
30°
10
0.2
0.3
2
20
0.2
0.3
6
30
0.2
0.3
7


## 4.2. Step Response

Experiments were repeated five times to assess the step response of the BD. The BD output was exponential (see Figure8(a)); hence we modeled the BD as afirst order system and we estimated the response time (τ) using the function error Γ:(4)Γt=BDoutt-BDout∞BDout0-BDout∞=e-t/τ,where V(t) is the output at time t, V0 is the output at t=0, and V∞ is the steady-state output. We evaluated the error function in 8 time instants (starting from t=0, with steps of 250 ms). According to our hypothesis, the natural logarithm of Γ results linearly related to time: Figure 8(b) shows both experimental data (blue asterisks) and linear fitting (red line) obtained in one of the five experiments. τ was calculated as the reciprocal of the angular coefficient of the red line. By averaging the values from all the experiments, τ became equal to 347±12 ms. The uncertainty was calculated using a Student reference distribution with four degrees of freedom and a 95% level of confidence, as recommended in [32].Figure 8
(a) Step response of the BD sensor; (b) error function assessed in 8 different time instants. Blue asterisks represent the experimental measures while the red line represents the liner fitting (r=0.9947).
(a)
(b)


## 4.3. Breathing Period Estimation

We did not consider the configuration at 30° of tilt since the discrimination threshold measured for this inclination does not allow an effective monitoring of breathing during sucking (see Section4.1). Among the other possible configurations, we decided to investigate the one with the worst discrimination performance, that is, the 20° tilt angle configuration at the three distances (10 mm, 20 mm, and 30 mm).We estimated the error in measuring the breathing period evaluating the mean absolute error (MAE) between the breathing period measured by BD (TBD) and the one measured by TSI (TTSI) as reported in [33]:(5)MAE=1n∑i=1nTBD-TTSI,where n is the number of acts (i.e., 10). This error has been reported in percentage as (6)MAE%MAEmeanTTSI∗100.The maximum MAE [%] was 10.7% and it was measured at 30 bpm, with I : E = 1 : 2. The overall results are reported in Table 2. Figures 9 and 10 show the two different breathing patterns assessed by BD and TSI, respectively.Table 2
Estimated MAE [%] for all frequencies and distances investigated.
Frequencies [bpm]/[Hz]
MAE [%]30 mm
MAE [%]20 mm
MAE [%]10 mm
I : E = 1 : 1
30/0.50
9.1%
4.1%
3.4%
39/0.65
5.4%
3.8%
5%
45/0.75
4.2%
5%
3.7%
60/1.00
5.1%
4.6%
4.3%
I : E = 1 : 2
30/0.50
9.3%
10.7%
6.2%
39/0.65
4.4%
7.4%
2.5%
45/0.75
2.7%
6%
3.3%
60/1.00
4.1%
3.1%
4.2%Figure 9
Ten acts set at 0.5 Hz (30 bpm) with two different I : E ratios (the red line is the BD output and the blue one is the TSI output, resp.).Figure 10
Ten acts set at 1 Hz (60 bpm) with two different I : E ratios (the red line is the BD output and the blue one is the TSI output, resp.).


## 5. Discussion and Conclusion

In common practice, the infant feeding assessment is most often highly subjective, with substantial variability of practices across neonatal nurseries. To avoid these issues, a tool for the objective assessment of breathing during feeding may be useful: it may provide indices to estimate feeding performances in terms of coordination between sucking and breathing [34].In this work, we investigated the application of a noninvasive module to record breathing patterns in newborns during bottle feeding. The transducer is based on the convective heat exchange between the air breathed by the newborn and two transistors. The experimental validation demonstrated that the BD (i) is able to distinguish flow rate under 0.5 L·min−1 (with a dependence on the tilt angle between the nostrils and the bottle); (ii) has a response time of about 347 ms; and (iii) allows the estimation of the respiratory period (with a MAE < 10.7%) during the monitoring of neonatal respiratory patterns. Moreover, the proposed BD has been designed to be embedded in a commercial feeding bottle (angle Well-Being Chicco, Artsana S.p.A.), so that such device might enable noninvasively assessing developmental problems or progress in the weeks after discharge [35].Several methods have been already proposed to monitor sucking, swallowing, and in particular breathing activities [36–38]. Wang et al. proposed an interesting wireless system to monitor NS and to detect sucking and swallowing events [39]. However, the module for breathing assessment was complex (based on the electromyography) and it did not enable estimating the breathing period.On the other hand, although other commercial devices (e.g., nasal thermistors or thermocouple, miniaturized pneumotachographs, and hot wire/film anemometers) exhibit high dynamic performances [11, 12, 14, 35, 40, 41], their use often requires invasive procedures which are not suitable for at-home applications and which can affect the development of the neural circuits in charge to control the development of sucking and the related sensory integration.The BD presented in this work allows estimating the breathing period using a noninvasive low-cost approach. Although the BD time response is too high to distinguish between inspiration and expiration phase, this sensor can be integrated with a module for sucking assessment, enabling monitoring of typical coordination measurements like the sucking-breathing ratio, and the breathing frequency during nutritive sucking. For this reason we designed the BD to be easily integrated on a commercial feeding bottle to enable large-scale screening of breathing coordination during NS. To this end, the low cost of the components allows the production of disposable devices also reducing the sterilization issues. A redesign of the sensing elements, considering transistors with a smaller package, will allow further improvement of the system performance minimizing the heat inertia and enabling the discrimination between inspiration and expiration.In conclusion, the experiments we carried out in this work demonstrate the effective applicability of the proposed flowmeter for breathing monitoring during nutritive sucking. The results pave the way to a set of future solutions to improve the system performances: in particular, the use of different packages and materials for the case of the sensing elements can improve the dynamic response of the system. Moreover, a real time monitoring of the bottle orientation is also suggested to compensate the negative effect of tilting on the discrimination threshold. These solutions will allow extending the use of the module for breathing monitoring of preterm and low birth weight infants.



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*Source: 7450859-2016-03-15.xml*