Device for measuring oral and nasal respirations, and control device for an interface comprising such a measuring device

Abstract

A device (1) for measuring the mouth and nose breathing of a user, comprising a probe (2) internally delimiting a first air passage channel (Ca) comprising a first opening (22a) suitable for being positioned under a first nostril of the user, a second air passage channel (Cb) comprising a second opening (22b) suitable for being positioned under a second nostril of the user, and a third air passage channel (Cc) comprising a third opening (23) suitable for being positioned opposite the mouth of the user, each air passage channel (Ca, Cb, Cc) housing an airflow measurement sensor (4a, 4b, 4c), each air passage channel (Ca, Cb, Cc) being associated with a microphone (5a, 5b, 5c) configured to detect a variation in air pressure in the associated air passage channel (Ca, Cb, Cc). Figure for the abridged version: Fig. 3

Description

Title of the invention: Apparatus for measuring oral and nasal respirations, and control device for an interface comprising such a measuring apparatus technical field

[0001] The present invention relates to the general field of devices for measuring a user's oral and nasal respirations. The invention thus applies to a device for measuring a user's oral and nasal respirations, as well as to a control device for an interface comprising such a measuring device. PRIOR TECHNOLOGY

[0002] In speech therapy, the assessment of breathing patterns, whether oral or nasal, plays a crucial role in identifying and treating orofacial dysfunctions, such as airway disorders or velopharyngeal insufficiency. Oral and nasal breathing measurement devices quantify airflow by analyzing, for example, the frequency, duration, and quality of a user's breathing. They provide invaluable assistance in diagnosing abnormal breathing patterns, often linked to conditions such as sleep apnea, nasal obstructions, or orofacial malformations, and thus facilitate the implementation of targeted rehabilitation interventions. Their use allows speech therapists to monitor the evolution of a patient's breathing and adapt therapies accordingly, thereby improving the quality of life of affected individuals.

[0003] While invasive diagnostic methods such as nasoendoscopy exist, non-invasive devices such as the rhinomanometer, spirometer, or acoustic pharyngometer have also been developed, each enabling specific diagnoses. For example, the rhinomanometer allows for the assessment of nasal respiratory efficiency and the detection of potential obstructions by measuring the resistance to airflow in the nasal passages, while the spirometer allows for the assessment of respiratory capacity by measuring the volumes of air inhaled and exhaled by the lungs.

[0004] More recently, document WO 2016 / 128627 Al proposed a device that allows both oral and nasal breathing of a patient to be measured simultaneously, in order to be able to assess the functional capacities of the soft palate and detect respiratory abnormalities, and to analyze the effects of speech therapy or improvements following maxillary expansion for example.

[0005] However, such a device does not simply allow differentiation between inhalation and exhalation during user respiration measurements. This distinction is essential for comparing exhaled and inhaled air volumes and identifying anomalies or asymmetries that may indicate a respiratory pathology. Description of the invention

[0006] One object of the present invention is to provide a measuring device that allows observation of a user's nasal and oral breathing by simply differentiating inspirations from expirations.

[0007] To this end, the invention proposes, according to a first aspect, a device for measuring a user's oral and nasal respirations, comprising a probe internally delimiting

[0008] a first air passage channel comprising a first opening, the first opening being suitable for positioning under a first nostril of the user,

[0009] a second air passage channel comprising a second opening, the second opening being suitable for positioning under a second nostril of the user, and

[0010] a third air passage channel comprising a third opening, the third opening being suitable for positioning opposite the user's mouth,

[0011] the probe comprising an airflow measurement sensor arranged in each air passage channel, each airflow measurement sensor being configured to measure a quantity representative of an airflow flowing in the air passage channel in which it is arranged,

[0012] the measuring device being remarkable in that the probe further comprises a microphone associated with each air passage channel, each microphone being configured to detect a pressure variation in the associated air passage channel during a flow of air from the first opening, the second opening or the third opening, respectively.

[0013] Thus, the measuring device comprises three airflow sensors that measure a representative quantity of the airflow from each of the user's nasal passages and oral airway. The presence of a microphone associated with each airflow simply allows for the identification of the expiratory phases. Indeed, when the user breathes into the device, overpressure is created inside the probe when air is exhaled, that is, when it enters one of the air passage channels through the opening specific to that air passage channel. Conversely, during inspiration, the microphone does not detect overpressure in the air passage channel, as the air passage channel is open. It is therefore easy for the practitioner to separate the inhalation and exhalation phases in the airflow measurements from the sensors.

[0014] The measuring device according to the invention is advantageously complemented by the following features, taken individually or in any of their technically possible combinations:

[0015] - the first air passage channel, the second air passage channel and the third The air passage channels are fluidically separated. This allows for measurements of airflow without interference between the user's different nasal and oral airways, and therefore enables relevant measurement of oral and nasal breathing;

[0016] - the associated microphone is arranged in a cavity in fluid communication with the air passage channel. This ensures that the microphone does not obstruct the air passage channel and therefore does not interfere with the measurement by the airflow sensor located in the same air passage channel. In addition, an overpressure is created in the cavity during exhalation, which allows for easy identification of exhalation;

[0017] - at least one air passage channel comprises a primary portion extending from the first, second, or third opening, respectively, depending on the direction of exhalation flow, and the cavity is located in an extension of the primary portion of the air passage channel along the direction of exhalation flow, so that the microphone faces the first, second, or third opening, respectively. This allows for a greater amplitude signal measurement, and therefore the detection of weaker exhalations;

[0018] - at least one microphone has a signal-to-noise ratio greater than 60 dB, preferably greater than 70 dB. This allows for a better quality measurement;

[0019] - at least one microphone is a MEMS microphone. Such a microphone has It offers structural advantages such as compactness, and can be easily integrated into the electronic circuit of the measuring device. It presents a good cost-to-quality ratio for measurement;

[0020] - the probe further comprises an electronic board electrically connected to the microphones and including a microprocessor configured for:

[0021] receive a noisy measurement signal from at least one primary microphone,

[0022] receive a noise signal from at least one secondary microphone distinct from at least one primary microphone, and

[0023] obtain a filtered measurement signal by subtracting the noise signal from the noisy measurement signal. Such a denoising process makes it possible to identify the exhalation phases by limiting the impact of external noises irrelevant to the measurement of respirations. This makes it possible to eliminate false positives in the identification of the user's breathing phases;

[0024] - the measuring device includes a reference microphone configured to measure ambient noise, and at least one secondary microphone is the reference microphone. The presence of an additional microphone allows the microprocessor to implement the noise reduction process, even when the user exhales simultaneously through the mouth and nose, i.e., when all other microphones are activated;

[0025] - the measuring device further comprises a handle assembled to the probe removable mechanism. This allows the measuring device to be easily adapted to the user's morphology, or to have different probes depending on the use of the measuring device.

[0026] According to a second aspect, the invention proposes a control device for an interface comprising a measuring device as described above, the interface being a mobile phone, a computer, a television or a video game console.

[0027] Typically, the previously described measuring device can be integrated into a video game control system. This makes establishing a respiratory diagnosis more engaging or facilitates the rehabilitation of a user, such as a patient with a respiratory abnormality. DESCRIPTION OF THE FIGURES

[0028] Other features, purposes and advantages of the invention will become apparent from the following description, which is purely illustrative and not limiting, and which should be read in conjunction with the accompanying drawings, given by way of non-limiting examples and on which:

[0029] Fig. 1 is a perspective view of a measuring device according to one embodiment.

[0030] Fig. 2 is a top view of the measuring device of Fig. 1.

[0031] Fig. 3 is a sectional view of the measuring device of Fig. 1 in a plane facial.

[0032] Fig. 4 is a perspective view of a cross-section in the face plane of the measuring device of Fig. 1.

[0033] Fig. 5 is a sectional view of the measuring device of Fig. 1 in a lateral plane.

[0034] Fig. 6 is a schematic representation of an airflow measurement sensor of the measuring device.

[0035] Fig. 7 is a schematic representation of a processing unit for analyzing respiration measurements from the measuring device.

[0036] Throughout the figures, similar elements bear identical references. DETAILED DESCRIPTION OF THE INVENTION

[0037] With reference to Figures 1 to 5, a measuring device 1 for the mouth and nasal breathing of a user is considered. The user may be a patient in the context of a medical diagnosis or the monitoring of rehabilitation, but the proposed measuring device may also be used in a non-medical context, for example for leisure or play.

[0038] Device structure

[0039] The respiration measuring device 1 as described includes a probe 2 adapted to be arranged in a measuring position opposite the user's face for measuring their respirations. The probe 2 forms a measuring unit comprising a plurality of respiration measurement sensors, as will be detailed later.

[0040] In this embodiment, the measuring device 1 includes a handle 3 for the user to grasp in order to position the probe 2 in the measuring position. Alternatively, the probe 2 may be integrated into a support for the user, for example a helmet, or may be held in the measuring position by a retention system, for example straps or elastic bands.

[0041] With reference to [Fig. 1], the handle 3 is formed by an external wall 31 for gripping by the user's hand, whose nostrils are positioned opposite at least one opening 22a, 22b arranged in the upper part of the probe 2, preferably a first opening 22a and a second opening 22b, and whose mouth is positioned opposite a third opening 23, which is arranged in the lower part of the probe 2. The handle 3 extends along a longitudinal direction Z. The shape of the handle 3 is chosen to allow ergonomic one-handed gripping of the measuring device 1.

[0042] Preferably, the probe 2 is removably mounted on the handle 3. In other words, the probe 2 is reversibly attached to the handle 3. The probe 2 is thus fixed to the handle 3 in a reversible locking position, meaning that it can be mounted on or removed from the handle 3 by the user or an operator. This allows for easy maintenance in the event of a malfunction or failure of one of the respiration measurement sensors in the probe 2.

[0043] Preferably, the measuring device 1 comprises several removable probes 2, each of which can be mounted interchangeably in the locking position on the handle 3. This allows the use of probes 2 of different sizes to adapt to the morphology or age of the user. It also allows the use of a different probe 2 depending on the intended use of the measuring device 1, for example, a probe 2 for orthodontic diagnosis, a probe 2 for speech therapy diagnosis, or a probe 2 for recreational use.

[0044] The probe 2 includes an outer casing formed by a shell 21. In the embodiment shown, the shell 21 includes a first shell forming a front wall of the probe 2 of the measuring device 1, and a second shell forming a rear wall of the probe 2.

[0045] The shell 21 comprises an upper wall having at least one opening, preferably a first opening 22a and a second opening 22b. The opening, preferably each of the first opening 22a and the second opening 22b, comprises at least one orifice allowing air to flow through the shell 21 during nasal breathing. The opening, or the first opening 22a and the second opening 22b, are thus intended to be positioned below the user's nostrils, at least when the nasal breathing measurement is performed.

[0046] In the illustrated embodiment, the measuring device 1 comprises a first opening 22a and a second opening 22b, referred to as the upper openings, each corresponding to one of the user's nostrils when the measuring device 1 is positioned for measurement, i.e., against the user's face. In other words, the first opening 22a is designed to be positioned under the user's first nostril (here, the left nostril), and the second opening 22b is designed to be positioned under the user's second nostril (here, the right nostril). "Under" means that the opening is located opposite or directly across from the associated nostril and is sufficiently close to it so that the air exhaled through the nostril enters the probe 2 through the corresponding opening, namely the first opening 22a or the second opening 22b.

[0047] The probe 2 also includes a third opening 23, referred to as the mouth opening or lower opening, designed to be positioned opposite the user's mouth. More specifically, the casing 21 includes a front wall having the third opening 23. The third opening 23 includes at least one orifice allowing air to flow through the casing 21 during mouth breathing. In the measurement position, the third opening 23 is thus positioned in front of the user's mouth, and close enough so that the air exhaled from the mouth enters the probe 2 through the third opening 23.

[0048] Thus, the first opening 22a and the second opening 22b correspond to nasal expiratory air inlets and nasal inspiratory air outlets, and the third opening 23 corresponds to a mouth expiratory air inlet and a mouth inspiratory air outlet.

[0049] To improve user comfort, the shell 21 may include a notch 210 extending along the upper wall of the shell 21 from the front wall, between the first opening 22a and the second opening 22b. The notch 210 is ergonomic and has a shape adapted to accommodate the lower edge of the nose of the user. In the measurement position, the user's nose is thus placed against the upper wall of the shell 21, each nostril coinciding with an associated opening 22a, 22b on either side of the notch 210.

[0050] Typically, the front wall of the shell 21 includes a forward-opening recess, allowing the user to comfortably position their mouth against the measuring device 1 in the measurement position. In the embodiment shown, the opening(s) of the third opening 23 are surrounded by a collar to allow for proper positioning of the upper and / or lower lip of the mouth at the level of the third opening 23. This also improves the reliability and quality of the measurement performed with the measuring device 1.

[0051] The probe 2 internally delimits a first air passage channel Ca comprising the first opening 22a, a second air passage channel Cb comprising the second opening 22b, and a third air passage channel Ce comprising the third opening 23. By "air passage", it is understood that a flow of breathing air can flow in each air passage channel Ca, Cb, Ce in a bidirectional manner.

[0052] The first air passage channel Ca and the second air passage channel Cb can be delimited by the shell 21, i.e., integral with the shell 21, or obtained by assembling an added part, for example, a flexible tube. Preferably, the first air passage channel Ca and the second air passage channel Cb do not communicate with each other, i.e., they are fluidically separated. This allows the measuring device 1 to measure the breathing of each nostril of the user independently, and thus makes it possible to detect an asymmetry in nasal breathing.

[0053] In the embodiment shown, the side wall of the hull 21 includes a first lateral opening 24a in fluid communication with the first opening 22a via the first air passage channel Ca, and a second lateral opening 24b in fluid communication with the second opening 22b via the second air passage channel Cb.

[0054] Each lateral opening 24a, 24b includes at least one orifice allowing air to flow through the shell 21, and in particular the air outlet when the user exhales through the nose through the opening 22a, 22b of the respective air passage channel Ca, Cb, and the air inlet when the user inhales through the nose through the opening 22a, 22b.

[0055] The shell 21 comprises a rear wall, opposite the front wall with respect to the probe 2, and having a rear opening 25 in fluid communication with the third opening 23 via the third air passage channel Ce. The rear opening 25 typically comprises a plurality of orifices opening onto The third air passage channel Ce. The third air passage channel Ce allows the circulation of oral airflow between the user's mouth and the outside of the probe 2. The X direction here corresponds to a direction of oral airflow. The third air passage channel Ce can be delimited by the shell 21, i.e., integral with the shell 21, or be obtained by assembling an added part.

[0056] Preferably, the third air passage channel Ce does not communicate with either the first air passage channel Ca or the second air passage channel Cb; that is, the third air passage channel Ce is fluidically separated from the first air passage channel Ca and the second air passage channel Cb. This allows the measuring device 1 to measure the user's mouth breathing independently of nasal breathing, and thus enables the detection of an asymmetry between nasal and mouth breathing.

[0057] The casing 21 delimits a compartment 26 in the probe 2 in which control elements of the measuring device 1, for example an electronic board 6, can be arranged. The casing 21 can form a sealed assembly. For example, the various sensors and electronic components contained in the probe 2 are arranged in the compartment 26, which is separated from the outside in a sealed manner.

[0058] The measuring device 1 is designed to be sterilizable by a UV (ultraviolet radiation) method or by the use of disinfectant wipes. Preferably, the measuring device 1 is compatible with standard sterilization protocols such as autoclaving, vacuum sterilization with ethylene gas (EtO₂), or a hydrogen peroxide vapor diffusion sterilization process as offered by Sterrad (registered trademark).

[0059] Preferably, the measuring device 1 includes a removable hygiene piece designed to be attached to the front wall of the shell 21. The hygiene piece is configured to filter oral or nasal airflow, thereby protecting the sensors of the probe 2 from moisture or solid particles from the user's respiration. In a medical setting, this also eliminates the need to sterilize the measuring device 1 between each user, thus saving the practitioner time while limiting the risk of transmitting respiratory diseases between successive patients. The removable hygiene piece, corresponding to a protective mask, can be attached to the shell 21 via the protrusions at the first lateral opening 24a and the second lateral opening 24b.

[0060] The probe 2 includes an airflow measurement sensor 4a, 4b, 4c arranged in each air passage channel Ca, Cb, Ce, each airflow measurement sensor 4a, 4b, 4c being configured to measure a quantity representative of an airflow flowing in the air passage channel Ca, Cb, Ce in which it is arranged. The operation of the airflow measurement sensors 4a, 4b, 4c will be detailed later.

[0061] The measuring device 1 is distinguished by the fact that the probe 2 further comprises a microphone 5a, 5b, 5c associated with each air passage channel Ca, Cb, Ce. Advantageously, each microphone 5a, 5b, 5c is configured to detect a pressure variation in the associated air passage channel Ca, Cb, Ce during the flow of air from the first opening 22a, the second opening 22b, or the third opening 23, respectively. Thus, each air passage channel Ca, Cb, Ce is associated with a microphone 5a, 5b, 5c configured to detect an air pressure variation in the associated air passage channel Ca, Cb, Ce.

[0062] The operation of the microphones will also be detailed later.

[0063] Respiration measurement sensors

[0064] The probe 2 is configured to provide a measurement of the user's oral and / or nasal breathing. Each airflow measurement sensor 4a, 4b, 4c is capable of providing at least one airflow presence measurement signal, i.e., is configured to provide a measurement signal enabling the estimation of a quantity representative of the airflow, for example the airflow velocity, its direction, or its flow rate.

[0065] With reference to the view in the facial plane (Y, Z) of [Fig.3], the probe 2 has an axis of symmetry parallel to the longitudinal direction Z passing through the notch 210. The longitudinal direction Z corresponds to a nasal flow direction.

[0066] The first air passage channel Ca comprises a first portion or primary portion extending from the first opening 22a towards the interior of the probe 2 in the Z direction, and a second portion extending from the lateral opening 24a towards the interior of the probe 2 in the Y direction. The two portions are separated by an elbow. Symmetrically, the second air passage channel Cb comprises two portions extending in two orthogonal directions and connected by an elbow.

[0067] The probe 2 comprises a first nasal airflow measurement sensor 4a and a second nasal airflow sensor 4b. Each airflow measurement sensor 4a, 4b is disposed in a respective air passage channel Ca, Cb.

[0068] More specifically, the first airflow sensor 4a is located at the bend connecting the primary and second portions of the first air passage channel Ca. This ensures that the first airflow sensor 4a is equally exposed to the airflow from the first opening 22a during nasal expiration, or from the lateral opening 24a during nasal inhalation. Similarly, the second airflow sensor 4b is symmetrically located in the bend of the second air passage channel Cb.

[0069] The probe 2 also includes an oral airflow measurement sensor 4c located in the third air passage channel Ce. The oral airflow measurement sensor 4c is configured to measure a quantity related to the oral airflow between the third opening 23 and the rear opening 25. The oral airflow measurement sensor 4c may be identical to the nasal airflow measurement sensors 4a, 4b. Their operation will be described in detail later.

[0070] Advantageously, the associated microphone 5a, 5b, 5c is arranged in a cavity in fluid communication with the air passage channel Ca, Cb, Ce.

[0071] Advantageously, at least one Ca, Cb, Ce air passage channel comprises a primary portion extending from the first opening 22a, the second opening 22b, or the third opening 23, respectively, along an expiration flow direction Z or X.

[0072] Preferably, the cavity is located in an extension of the primary portion of the air passage channel Ca, Cb, Ce along the direction of expiration flow Z or X, so that the associated microphone 5a, 5b, 5c faces the first opening 22a, the second opening 22b, or the third opening 23, respectively.

[0073] In the embodiment shown, the probe 2 comprises the first microphone 5a configured to detect an airflow from the first opening 22a. More specifically, the first microphone 5a is configured to detect an overpressure in the first air passage channel Ca during an airflow from the first opening 22a, i.e., during exhalation through the user's left nostril. Similarly, the second microphone 5b is configured to detect an airflow from the second opening 22b, and in particular an overpressure in the second air passage channel Cb during an airflow from the second opening 22b, i.e., during exhalation through the user's right nostril.

[0074] The probe 2 includes the third microphone 5c - or mouth microphone - configured to detect an airflow from the third opening 23. More specifically, the third microphone 5c is configured to detect an overpressure in the third air passage channel Ce during an airflow from the third opening 23, i.e. when the user exhales through the mouth.

[0075] Each of the first microphone 5a and the second microphone 5b is disposed in the dedicated cavity in fluid communication with the respective air passage channel Ca, Cb. Each of the first microphone 5a and the second microphone 5b is oriented opposite the associated opening 22a, 22b. More precisely, the dedicated cavity is disposed in the extension of the first portion of the air passage channel Ca, Cb, along the nasal expiration direction Z.

[0076] The third microphone 5c is arranged in a dedicated cavity in communication with the third air passage channel Ce, and typically oriented opposite, that is, so as to face, the third opening 23. The third microphone 5c may be identical to the first microphone 5a and the second microphone 5b. The operation of the microphones 5a, 5b, and 5c will be described in detail later.

[0077] Preferably, the probe 2 is further configured to be connected to a laryngeal vibration sensor. The laryngeal vibration sensor can be a generic external sensor or one embedded in another device, typically integrated into a smartwatch. The laryngeal vibration sensor can be of the vibration type (such as a piezoelectric sensor or an accelerometer), or, without limitation, a blood flow sensor. The housing 21 includes, for example, a connector, typically a jack port, connected to the electrical circuit 6 and intended to receive a jack cable connected to the laryngeal vibration sensor. Preferably, the laryngeal vibration sensor is configured to exchange information with the electronic board 6 wirelessly, for example via Bluetooth (registered trademark) or Wi-Fi (registered trademark). This increases user comfort and facilitates the use of the measuring device 1.

[0078] The laryngeal vibration sensor is intended to be applied to the user's throat, at the level of the larynx. It is held in position by a suitable fastening means, for example, an adhesive or an elastic band. The laryngeal vibration sensor is typically a piezoelectric sensor configured to transform a force caused by the vibrations of the user's larynx into an electrical voltage transmitted to the electronic board 6. Such an external analysis channel is very useful in speech therapy, as it allows the detection of additional sounds and low-level breathing at the lung level. The pronunciation of the sound "A," for example, does not produce an airflow and can be detected by the laryngeal vibration sensor.

[0079] Airflow measurement sensors

[0080] Hereafter, the term "airflow measurement sensor 4" will refer to any one of the airflow measurement sensors 4a, 4b nasal, and 4c oral. Thus, each of the airflow measurement sensors 4a, 4b nasal, and 4c oral can be implemented according to the airflow measurement sensor 4.

[0081] According to one embodiment, the airflow measurement sensor 4 is of the thermistor type. The airflow measurement sensor 4 is positioned in the respective air passage channel Ca, Cb, Ce to be exposed to the airflow coming from or going towards the associated opening 22a, 22b or 23. Thus, each air passage channel Ca, Cb, Ce houses an airflow measurement sensor 4a, 4b, 4c.

[0082] With reference to [Fig. 6], the airflow measurement sensor 4 comprises a bare electrical conductor 41 of a thermistor, held in position in the channel of respective air passage Ca, Cb, Ce through a support 42. The bare electrical conductor 41 has between its two ends an electrical resistance, which varies according to the temperature, and generates a power by Joule effect dependent on the airflow through it.

[0083] The bare electrical conductor 41 of the airflow measuring sensor 4 can be formed by a metal wire or a metal filament. For example, the airflow measuring sensor 4 shown corresponds to a standard incandescent light bulb marketed by JKL components corporation under reference 7373 from which the protective glass bulb has been removed, so that the filament is in direct contact with the airflow passing through the respective air passage channel Ca, Cb, Ce during the user's breathing.

[0084] The bare electrical conductor 41, or here the metal filament, can be made of a noble metal, for example gold, platinum, or a platinum-iridium alloy. The use of such a metal increases the resistance of the airflow measuring sensor 4 to corrosion and oxidation and extends the service life of the measuring device 1.

[0085] Alternatively, the bare electrical conductor 41 can be made of tungsten or steel. Such metals are commonly used in incandescent light bulb filaments and are inexpensive. This makes the measuring device 1 more accessible to practitioners. Preferably, the bare electrical conductor 41 is a pre-oxidized metal filament, for example, burned on a test support before assembly on the electronic board 6. This allows it to be partially corroded and thus resistant to oxidation.

[0086] The airflow measurement sensor 4 also includes a sensor body 44 having two contacts 43, each connecting one end of the bare electrical conductor 41 to a respective electrode (or leg) 45. The airflow measurement sensor 4 is intended to be connected to the electronic board 6 via the two electrodes 45, in order to pass an electric current through the bare electrical conductor 41.

[0087] Preferably, the airflow measurement sensor 4 is mounted on a modular printed circuit board attached to the electronic board 6. This allows easy assembly of the airflow measurement sensors 4 in the measuring device 1, but also easy replacement of the airflow measurement sensors 4 in case of failure.

[0088] The electrical resistance of the bare electrical conductor 41 varies, in particular, with its temperature. The heat transfer or power of the bare electrical conductor 41 depends on the flow velocity of the airflow passing through it, for example, according to King's law. The electronic board 6 is configured to measure the current flowing through the bare electrical conductor 41 and the voltage across its ends and to deduce from this a quantity representative of the airflow, typically the flow velocity.

[0089] Preferably, the electronic card 6 includes a microcontroller 61 configured to take into account the variation in electrical resistance of the bare electrical conductor 41 in the determination of the representative quantity.

[0090] Preferably, the electrical voltage applied to the bare electrical conductor 41 by the electrical circuit 6 is a low voltage, typically less than 220 V or even less than 50 V.

[0091] Preferably, the airflow measurement sensors 4 are configured to perform self-calibration, so that the measuring device 1 can perform user breathing measurements without prior calibration.

[0092] Each airflow measurement sensor 4 is configured to transmit a measurement signal to the microcontroller 61. The microcontroller 61 is configured to calculate or estimate the representative quantity of a nasal or oral airflow from the measurement signal.

[0093] Preferably, the airflow measurement sensors 4 have high sensitivity, so that the microcontroller 61 can estimate an airflow rate over an amplitude range greater than ±15 l / s, with an accuracy of less than ±5% error, preferably less than ±1% error. Advantageously, the flow rate range measurable by the airflow measurement sensors is ±250 sim (standard liters per minute). The resolution of the airflow measurement sensors 4a, 4b, 4c is preferably less than 0.1 sim, preferably even less than 0.01 sim.

[0094] The measurement signals from the airflow sensors 4 can enable the microcontroller 61 to calculate a plurality of representative quantities to assist the practitioner in their diagnosis. For example, the microcontroller 61 can be configured to calculate, from the measurement signals, a maximum ventilation per minute (MW), a peak expiratory flow rate (PEF), and an exhaled or inspired air volume.

[0095] At least one of the 4 airflow measurement sensors can be configured to implement TrueFlow spirometry technology (registered trademark). Another example of an 4 airflow measurement sensor is marketed by Sensirion (registered trademark) and is based on CMOSens® technology.

[0096] Microphones

[0097] Hereafter, "microphone 5" will be designated as any one of the microphones of the nasal air passage channels Ca, Cb, namely the first microphone 5a and the second microphone 5b, and the third microphone 5c of the third air passage channel Ce. Thus, the first microphone 5a, the second microphone 5b and the third microphone 5c can be made in accordance with microphone 5.

[0098] As explained previously, the presence of a microphone 5 configured to detect a pressure variation caused by an airflow from the first opening 22a, the second opening 22b and the third opening 23 makes it possible to simply identify the successive expirations of the user when the measuring device 1 is in the measuring position.

[0099] With each air passage channel Ca, Cb, Ce open, the user's inhalation does not create a vacuum inside the probe 2. In addition, the clean cavity in which the microphone 5 is housed protects it from a flow from the lateral openings 24a, 24b and the rear opening 25.

[0100] The microphone 5 typically comprises a membrane or diaphragm that can vibrate under the action of mechanical pressure (due to breath or sound waves). The microphone 5 transmits a measurement signal in the form of a voltage representing the movement of the membrane. The membrane of the microphone 5 is positioned opposite a dedicated air-capture channel communicating with the air-capture channel Ca, Cb, Ce through which the airflow flows. The air-capture channel is oriented towards the associated opening 22a, 22b, 23 corresponding to the exhalation air inlet. Thus, when the user blows through one of the openings 22a, 22b, 23, the associated microphone 5 detects a pressure variation, and in particular an overpressure exerted by the air in the air-capture channel on the membrane.

[0101] The microphone 5 preferably has high sensitivity. The microphone 5 has a high signal-to-noise ratio (SNR), typically greater than 60 dB, preferably greater than 70 dB. This makes it easier to process the signals emitted by the microphone 5 and to easily identify the pressure variation in the air passage channel of interest without extraneous noise.

[0102] The microphone 5 preferably has a wide pickup bandwidth and is capable of detecting very low frequency (below 10 Hz) and very high frequency (above 10 kHz) signals. Typically, the microphone 5 has the widest possible frequency range, preferably from 10 Hz to 20 kHz.

[0103] The microphone 5 may be of the analog or digital type. It may include an analog-to-digital converter and / or its own amplifier. For example, the microphone 5 may be an electrostatic or mechanical microphone, or an electret condenser microphone (ECM).

[0104] Preferably, the microphone 5 is a MEMS microphone. In this embodiment, the microphone 5 comprises a pressure-sensitive diaphragm etched onto a silicon wafer using a microelectromechanical process. A MEMS microphone 5 has the advantage of being very stable. It is easily integrated into the electrical circuit 6, and is robust, thus presenting a low risk of damage, particularly during assembly or soldering. The microphone 5 MEMS is also very compact, which allows it to be placed in a small, clean cavity without increasing the size of the measuring device 1 and without risking disturbing the measurement of the airflow measurement sensors 4.

[0105] The microphone 5 can be configured to amplify and clean the measurement signal generated by the vibration of the diaphragm. Alternatively or in addition, the microcontroller 61 can be configured to perform denoising of the measurement signal from an active microphone 5.

[0106] Preferably, microprocessor 61 is configured to: • receive a noisy measurement signal from at least one primary microphone 5; • receive a noise signal from at least one separate secondary microphone 5 of at least one primary microphone 5; • obtain a filtered measurement signal by subtracting the noise signal from the noisy measurement signal.

[0107] By "primary microphone" is understood to mean an active microphone among the first microphone 5a, the second microphone 5b and the third microphone 5c, i.e. detecting a pressure variation in the associated Ca, Cb, Ce air passage channel and transmitting a measurement signal to the microprocessor 61. The "secondary microphone" corresponds to the other microphone(s) 5 which are inactive when they do not detect a sufficient pressure variation.

[0108] For example, when the user exhales through their mouth, i.e., during oral exhalation, air enters through the third opening 23 and exerts pressure on the diaphragm of the third microphone 5c, which emits a measurement signal. The microprocessor 61 receives a measurement signal that is noisy due to ambient noise or spurious signals. The noisy signal typically extends over the entire available spectrum, beyond the speech spectrum, for example, between 80 Hz and 12 kHz. The ambient noise can be distinguished from the user's speech frequencies, which are concentrated only in the lower frequencies (e.g., below 1 kHz).

[0109] The first microphone 5a and the second microphone 5b located in the respective nasal air passage channels Ca, Cb are inactive. They transmit a noise signal to the microprocessor 61. The microprocessor 61 can then receive the noise signal and use this noise signal to filter the noisy measurement signal.

[0110] Preferably, the measuring device 1 further comprises a reference microphone configured to measure ambient noise. The reference microphone may be located in one of the air passage channels Ca, Cb, Ce or in a cavity communicating with one of the air passage channels Ca, Cb, Ce, or in a dedicated compartment provided in the housing 21.

[0111] More specifically, the microphone 5a, 5b, 5c allows the measurement of white noise, that is to say, noise generalized over a wide frequency band, for example including between 10 Hz and 20 kHz. In white noise, all frequencies are present at the same intensity or power, evenly distributed. Thus, white noise is distinguishable from a measurement signal emitted when the user speaks, for example. In the latter case, the frequency of the emitted signal will be within a narrower frequency band, on the order of kilohertz. Ambient noise is distinct from white noise caused by the user's breath. Typically, in a measurement signal corresponding to white noise, a similar amplitude difference is measured across several frequencies, for example, a 10 dBA increase in the measurement signal across several frequencies, such as 25 Hz, 50 Hz, 100 Hz, 200 Hz, 400 Hz, or even higher frequencies.For detecting user breath, measuring device 1 is configured to search for an audible signal corresponding to white noise, by measuring the amplitude of the filtered measurement signal at different frequencies, including those outside the audible spectrum. Prior elimination of ambient noise unrelated to user breath, preferably using the reference microphone, allows for a more reliable measurement of pressure variations due to user breath.

[0112] In other words, after removing ambient noise from the measured sound signal, a sound signal corresponding to white noise is sought in the filtered measurement signal. When a similar variation in sound amplitude (white noise) is present at several frequencies, it is deduced that the user is blowing.

[0113] This is possible either by performing a spectral analysis or by calculating the sound level of the overall sound signal over a given period.

[0114] To identify white noise in the noisy measurement signal, or preferably in the filtered measurement signal, the measuring device 1 can implement spectral analysis. Spectral analysis allows for more precise detection of the user's breath, as it enables the search for corresponding white noise at frequencies outside the purely "audible" spectrum. However, spectral analysis is more computationally expensive and therefore requires a more powerful microprocessor 61.

[0115] Alternatively or complementarily, the measuring device 1 can determine the overall sound level of the signal over a given period. This method is particularly relevant when ambient noise is attenuated beforehand. The attenuation or suppression of ambient noise described above makes it possible to identify the hiss without requiring spectral analysis, as the analysis by measuring the sound signal is sufficient to precisely identify the hiss. Thus, with good attenuation—or good filtering—of the ambient noise, the analysis by measuring the sound signal may be sufficient to detect white noise, which is preferable for limiting the computing power used.

[0116] The secondary microphone used by the microcontroller 61 to filter the noisy measurement signal can be the reference microphone.

[0117] Preferably, the microphone 5a, 5b, 5c is pre-calibrated. This allows the frequency response of each active microphone 5a, 5b, 5c integrated into the measuring device 1 to be recorded. The frequency response is stored in the memory of the microprocessor 61. In this embodiment, the microprocessor 61 can compensate for the values ​​of the noisy measurement signal, or the filtered measurement signal, using the stored frequency response for the corresponding microphone.

[0118] Alternatively or complementarily, the microcontroller 61 can calculate an average noise from the set of noise signals from the secondary microphones, for example by averaging, and use the average noise to filter the noisy measurement signal.

[0119] Preferably, the measuring device 1 includes an accelerometer. The accelerometer can be located in the probe 2 or in the handle 3. It allows the microcontroller 61 to determine the orientation of the measuring device 1, and in particular whether it is in a vertical position, and whether it is stationary or moving. Thus, the microcontroller 61 can be configured to eliminate noise picked up due to handling of the measuring device 1, if, for example, an airflow enters the openings 22a, 22b, or 23 due to swinging of the measuring device 1.

[0120] Assembling the measuring device 1

[0121] The removable probe 2 can be assembled onto one end of the handle 3, for example by means of cooperating fastening means, typically a screw or clip system. The fastening means are reversible to allow the removable probe 2 to be removed from the handle 3.

[0122] In one embodiment, the measuring device 1 is electrically powered by a processing unit located outside the measuring device 1 via a power cable.

[0123] Preferably, the handle 3 includes a battery to power the airflow measurement sensors 4a, 4b, 4c, the microphones 5a, 5b, 5c, and the electronic board 6. Typically, the battery can be a lithium-ion battery. Preferably, the battery is rechargeable and can perform fast charging cycles. The battery can have a capacity greater than 1000 mAh to provide sufficient autonomy for the measuring device 1.

[0124] Thus, the probe 2 includes a first connector and the handle 3 includes a second connector configured to be electrically connected to the first connector, when the probe 2 is assembled on the handle 3. The first connector is for example of the male type, and the second connector of the female type.

[0125] The cooperation of the connectors with each other can contribute to locking the probe 2 on the handle 3 in the operating position of the measuring device 1.

[0126] Analysis of respiratory measurements from measuring device 1

[0127] The second connector or the first connector can be connected to the measurement signal processing unit 100. For example, the handle 3 includes, at its lower end, an interface for connection to the processing unit 100. The interface is, for example, a USB or USB-C port, so as to connect a USB or USB-C cable to the processing unit 100.

[0128] Preferably, the measuring device 1 includes wireless communication means for communicating with the processing unit 100. For example, the handle 3 includes a Bluetooth module (registered trademark) configured to exchange information via Bluetooth with the processing unit 100. Alternatively or in addition, the handle 3 and / or the probe 2 include a Wi-Fi module (registered trademark) configured to exchange information via Wi-Fi (registered trademark) with the processing unit 100.

[0129] With reference to [Fig. 7], the processing unit 100 advantageously includes a human-machine interface, for example a display 101. The display 101 may be touch-sensitive. The processing unit 100 may include buttons or sliders 102 for selecting the signals to be displayed or for changing the display on the display 101. This allows visualization of the time evolution of the measurement signals from the airflow measurement sensors 4a, 4b, 4c and the microphones 5a, 5b, 5c.

[0130] Typically, the processing unit 100 allows for the simultaneous display of the evolution of the respiratory measurement signals 104 resulting from the processing of the measurement signals from the airflow sensors 4a, 4b, 4c, and the measurement signals 105 from the microphones 5a, 5b, 5c. An alternation between inspiratory and expiratory phases is observed, which can be simply delimited by the reception of a higher amplitude signal 105 during exhalation. The amplitude of the measurement signal 105 also depends on the force of exhalation and therefore on the airflow rate.

[0131] The measuring device 1 thus allows the practitioner to perform a simultaneous and comparative study of nasal and / or oral airflow. In particular, it allows for a clinical assessment of upper air ventilation and the functional capacities of the soft palate. The analysis of the signals transmitted by the airflow measurement sensors 4a, 4b, 4c and the microphones 5a, 5b, 5c allows the practitioner to evaluate velar insufficiency and assess nasal air leakage, and to propose respiratory and phonation rehabilitation methods adapted to the user, such as a patient.

[0132] Observation by the practitioner (e.g., orthodontist or speech therapist) of the time curves of the measurement signals on the processing unit 100 allows to perform a diagnosis of the user's breathing. Measuring device 1 also allows for the analysis of the user's oral and / or nasal breathing when they speak. The detection by measuring device 1 of nasal airflow during the repetition of phonemes, words, or phrases spoken by the user objectively demonstrates the phenomenon of nasal air leakage and quantifies its severity.

[0133] Thanks to the sensitivity of the nasal airflow measurement sensors 4a, 4b, the opening and closing movements of the velopharyngeal sphincter are clearly visible on the curves displayed on the processing unit 100, objectifying the muscular potential of the sphincter and allowing verification of its rigidity, its possibilities of complete opening and closing, its speed of execution of opening and closing movements, or its stability.

[0134] Use of the measuring device 1 in a control device

[0135] The measuring device 1 can be advantageously used in a control device for an interface, in particular for a video game. The interface is, for example, a mobile phone, a computer, a television, or a video game console.

[0136] The measuring device 1 can be integrated into a primary remote control or be an accessory connected to a remote control. The control device can take the form of a handheld joystick incorporating the probe 2 described above or the measuring device 1.

[0137] The control device can also be a mask that can be placed on the user's face and incorporates the measuring device 1, so that the first opening 22a and the second opening 22b correspond respectively with the user's nostrils, and the third opening 23 corresponds with the user's mouth.

[0138] The measuring device 1 exhibits high responsiveness and low latency. Preferably, it can communicate with the interface via a wireless link, for example via Bluetooth (registered trademark) or Wi-Fi (registered trademark), so as to enable wireless control.

[0139] The control device may further include other means of controlling the interface, for example a button or a joystick.

[0140] The control device may include means of sensory interaction with the user, for example a light indicator or a vibrating motor.

[0141] The control device may include means for localizing the device in space, for example integrating a 6-axis inertial unit, preferably a 9-axis inertial unit including an accelerometer, a gyroscope and a compass.

[0142] The control device allows for the execution of control operations for a video game, for example. The video game can make rehabilitation more enjoyable, for example following jaw surgery.

[0143] The present invention is not limited to the embodiments shown. The embodiments and examples described may be combined with each other in any technically feasible combination or selected independently of each other.

Claims

Demands

1. A device (1) for measuring the mouth and nose breathing of a user, comprising a probe (2) internally delimiting a first air passage channel (Ca) comprising a first opening (22a), the first opening (22a) being suitable for positioning under a first nostril of the user, a second air passage channel (Cb) comprising a second opening (22b), the second opening (22b) being suitable for positioning under a second nostril of the user, and a third air passage channel (Ce) comprising a third opening (23), the third opening (23) being suitable for positioning opposite the user's mouth, the probe (2) comprising an airflow measurement sensor (4a, 4b, 4c) arranged in each air passage channel (Ca, Cb, Ce), each airflow measurement sensor (4a, 4b, 4c) being configured to measure a quantity representative of an airflow flowing in the air passage channel (Ca,Cb, Ce) in which it is arranged, the measuring device (1) being characterized in that the probe (2) further comprises a microphone (5a, 5b, 5c) associated with each air passage channel (Ca, Cb, Ce), each microphone (5a, 5b, 5c) being configured to detect a pressure variation in the associated air passage channel (Ca, Cb, Ce) during the flow of an air stream from the first opening (22a), the second opening (22b) or the third opening (23), respectively.,

2. Measuring apparatus (1) according to claim 1, wherein the first air passage channel (Ca), the second air passage channel (Cb) and the third air passage channel (Ce) are fluidly separated.

3. Measuring apparatus (1) according to any one of claims 1 and 2, wherein the associated microphone (5a, 5b, 5c) is arranged in a cavity in fluid communication with the air passage channel (Ca, Cb, Ce).

4. Measuring apparatus (1) according to claim 3, wherein at least one air passage channel (Ca, Cb, Ce) comprises a primary portion extending from the first opening (22a), the second opening (22b), or the third opening (23), respectively, along an expiratory flow direction (Z, X), and wherein the cavity is located in an extension of the primary portion of the air passage channel (Ca, Cb, Ce) along the direction of expiration flow (Z, X), so that the microphone (5a, 5b, 5c) faces the first opening (22a), the second opening (22b), or the third opening (23), respectively.

5. Measuring apparatus (1) according to any one of claims 1 to 4, wherein at least one microphone (5a, 5b, 5c) has a signal-to-noise ratio greater than 60 dB, preferably greater than 70 dB.

6. Measuring apparatus (1) according to any one of claims 1 to 5, wherein at least one microphone (5a, 5b, 5c) is a MEMS microphone.

7. Measuring apparatus (1) according to any one of claims 1 to 6, wherein the probe (2) further comprises an electronic board (6) electrically connected to the microphones (5a, 5b, 5c) and comprising a microprocessor (61) configured to: receive a noisy measurement signal from at least one primary microphone, receive a noise signal from at least one secondary microphone distinct from at least one primary microphone, and obtain a measurement signal filtered by subtracting the noise signal from the noisy measurement signal.

8. Measuring apparatus (1) according to claim 7, further comprising a reference microphone configured to measure ambient noise, and wherein at least one secondary microphone is the reference microphone.

9. Measuring apparatus (1) according to any one of claims 1 to 8, further comprising a handle (3) removably assembled to the probe (2).

10. Control device for an interface comprising a measuring device (1) according to any one of claims 1 to 9, the interface being a mobile phone, a computer, a television or a video game console.

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