Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/08—Measuring devices for evaluating the respiratory organs
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/0048—Detecting, measuring or recording by applying mechanical forces or stimuli
  • A61B5/0051—Detecting, measuring or recording by applying mechanical forces or stimuli by applying vibrations
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
  • A61B5/0077—Devices for viewing the surface of the body, e.g. camera, magnifying lens
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/48—Other medical applications
  • A61B5/4848—Monitoring or testing the effects of treatment, e.g. of medication
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
  • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
  • A61B2562/0204—Acoustic sensors
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B2576/00—Medical imaging apparatus involving image processing or analysis
  • A61B2576/02—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part

Definitions

• the invention relates to a method for characterizing the vibration of a surface, in particular a surface of the bust of an individual.
• Visual observation includes looking for an increase in respiratory rate or a change in the "ventilatory profile", i.e. the respective duration of inspiration and expiration, and looking for 'paradoxical abdominal breathing', i.e. abdominal deflation on inspiration when one should observe an expansion synchronous with that of the thorax.
• the examination of the transmission of vibrations and sounds at the level of the thorax corresponds to the examination of the "vocal fremitus" (tactile) which consists of palpating the chest wall to detect changes in the intensity of the vibrations generated by certain vocalizations or a constant voice, and thus identify a pathology affecting the underlying pulmonary system. For example, the influence of pleurisy on the inhomogeneity of vocal vibrations reaching the surface of the thorax has been observed.
• This examination can be carried out in two ways.
• the second possible examination is auscultation, using a stethoscope placed on the patient's chest, of the sound produced by the circulation of air in the patient's bronchi and lungs, and the search for noises abnormal.
• the examination of the thorax provides a first approach before a final diagnosis by observing hyperventilation and detecting pulmonary condensation using percussion or auscultation.
• this examination has certain limitations because it only highlights very flagrant anomalies.
• this examination is very dependent on the experience of the observer and does not allow any recording, transmission or a posteriori re-analysis of the data.
• the ventilatory profile of an individual is a fine and easily disturbed phenomenon. The simple touch of the doctor's hand or the stethoscope can impact the results of the examination.
• the doctor can resort to chest imaging by scanner.
• This examination makes it possible to complete the data of the clinical examination, and in particular to visualize images of "frosted glass” and "condensations" in patients suspected of having a COVID19 infection.
• the aim of the invention is in particular to overcome these drawbacks of the prior art.
• the aim of the invention is to provide a method for the fine detection and characterization of vibrations at the surface of the body of an individual without contact with said individual.
• the subject of the invention is a method for characterizing the vibration of a surface of the bust of an individual, in particular with the aim of establishing a diagnosis of a pathology affecting the respiratory system, said method comprising: a) the generation of an incident vibration of the respiratory system of the individual, said incident vibration being characterized by a signal Sp r having at least a frequency of 20 to 5000 Hz, for obtaining resulting vibrations at the level of a surface S of the individual's chest following the propagation of the incident vibration from the respiratory system to the surface S, said surface S having an area of at least 10 cm 2 and being characterized by a plurality of points Pi, b) measuring the oscillation of each point Pi using a measuring device and obtaining the signal Sp i of the resulting vibration at each of the points Pi, said measuring device being placed at a distance from the bust of said individual, and c) the characterization of each signal Sp i at the frequency or frequencies of the signal Sp r : - by the analysis over a given time of at
• the inventors discovered unexpectedly that it was possible to obtain precise and relevant data for establishing a diagnosis of a disease affecting the respiratory system of an individual, without contact with said individual and without exposing the patient/individual to radiation. This is made possible by the generation of an incident vibration at the level of his respiratory system and the study of the transformation of this vibration following its propagation to a surface of the bust of the individual.
• the method according to the invention allows a complete study of the bust of the individual by establishing two or three-dimensional (2D or 3D) vibratory maps on which can be represented one or more parameters p of the resulting vibrations or the dynamics of evolution of these parameters.
• mammals By “individual”, it is understood in the invention a mammal, in particular a human.
• bust it is understood in the invention the upper front, rear and side parts of the body of an individual starting from the waist, or above the lower limbs, and arriving up to the top of the neck, excluding upper limbs.
• the bust thus includes the abdominal part, the thoracic part and the neck of an individual.
• respiratory system any organ belonging to the respiratory system, in particular the larynx, the trachea, the main, segmental and lobar bronchi, the alveoli, the bronchioles, the right and left lungs and the diaphragm.
• Pulthology affecting the respiratory system means any pathology that alters the structure and/or functioning of the respiratory system. These pathologies include respiratory pathologies proper as well as cardiac and neuromuscular pathologies affecting the respiratory system.
• the first step of the method of the invention concerns the generation of an incident vibration at the level of the respiratory system.
• the vibration of the respiratory system is forced at one or more determined frequencies.
• the incident vibration is characterized by a signal Sp r having at least a frequency of 20 to 5000 Hz, in particular from 40 to 2500 Hz, in particular from 60 to 1000 Hz.
• a lower limit of 60 Hz and more is preferred. Indeed, such a low limit makes it possible to greatly reduce the parasitic vibrations due to the self-induced vibration of certain parts of the body, such as the heart, the blood network, the muscles, etc.
• the frequency profile of the incident vibration can be static or evolve over time.
• the signal Sp r can have a single frequency which is modified over time, in particular at regular intervals.
• the signal Sp r can have several frequencies which can each be modified over time, in particular at regular intervals.
• a multi-frequency incident vibration makes it possible to refine the analysis of the resulting vibrations and therefore to provide more relevant data with a view to establishing a diagnosis. Indeed, some pathologies are more sensitive to a particular range of frequencies, and generating more frequencies thus makes it possible to cover more pathologies.
• the frequency range of the incident vibration used in the invention corresponds to that of a human voice.
• the incident vibration can be generated either by a device or by the individual himself, for example by vocalizations.
• the incident vibration can be generated by: i) a device generating vibrations in an acoustic tube, in particular the tip of which is inserted into the oral cavity of said individual, or ii) a vibrating device placed against a surface S g of the body of the individual, in particular of the bust, the surfaces S g and S being opposite to each other with respect to the bust of the individual, or iii) a vibration of the vocal cords of said individual.
• said device used can be any means generating a vibration and in particular a loudspeaker or a compressor.
• the vibration generated is passed through an acoustic tube so that it is transported to the respiratory system.
• the tip of the acoustic tube is inserted into the oral cavity of the individual, or even into the trachea of the latter.
• This system is particularly advantageous in the case where the individual is not able to generate sounds, or else generates sounds of too low an amplitude for a precise study of the resulting vibrations at the level of the surface of the bust.
• this system has the advantage of generating a vibration at one or more determined frequencies, and distributing it directly to the respiratory system through the acoustic tube. The incident vibration thus generated by the device is very little transformed when it reaches the respiratory system and is almost identical to that of the respiratory system. The resulting vibrations are therefore little or not noisy and their analysis is directly relevant.
• said device used can also be any means generating a vibration, and in particular a loudspeaker, a vibrating pot or a pneumatic hammer.
• the incident vibration will start from the surface S g , propagate through the body, cross the respiratory system, until it reaches the surface S, possibly the opposite.
• This system is also well suited in the case where the individual is not able to generate sounds, or generates sounds of too low an amplitude for a precise study of the resulting vibrations at the level of the surface of the bust.
• This system has the advantage of generating a vibration at one or more determined frequencies.
• the resulting vibrations obtained are the product of a double transformation: the transformation of the vibration generated up to the respiratory system and the transformation of the incident vibration (that coming from the respiratory system) up to the surface of the bust resulting in the resulting vibrations.
• This system therefore involves interference due to the first transformation, and in particular possible processing of the resulting vibrations to remove this interference.
• the individual himself who will generate the vibration of the respiratory system, by the vibration of his vocal cords.
• This alternative has the advantage of not requiring any ancillary equipment, which reduces the costs of implementing the invention.
• the vibration of the individual's vocal cords can be simple or complex vocalization, singing or speech.
• this aspect of the invention has the advantage of generating a vibration directly distributed to the respiratory system.
• the vibrations generated and the incident vibration are almost identical, even identical, and the resulting vibrations are only the result of the transformation of the incident vibration from the respiratory system to the surface of the bust. The resulting vibrations are therefore little disturbed and their analysis is simplified and directly relevant.
• simple vocalization it is understood in the invention a monotonic sound pronounced by the individual, such as the continuous pronunciation of the phoneme "A”, of any other vowel.
• a simple vocalization therefore presents a narrow frequency band, of the order of 4 to 10 Hz, centered on the fundamental frequency.
• complex vocalization it is understood in the invention a nuanced sound, such as the pronunciation of the word “thirty-three”. A complex vocalization then presents a wider frequency band, greater than 10 Hz, centered on the fundamental frequency.
• Singing and speech correspond to a nuanced sound.
• the fundamental is generally around 100 Hz for a man and 150 Hz for a woman.
• the frequency band retained is that around the fundamental, as will be seen later.
• the signal Sp r of the incident vibration is not known and must be determined. This determination can be made by any means.
• obtaining the signal Sp r of the incident vibration during step b) is carried out by measuring - sound coming out of the mouth of the patient/individual, in particular using at least one microphone, or - the vibration of the lips or the trachea of the patient/individual, in particular using the measuring device used in step b).
• the latter can for example be arranged around the mouth of the individual, in particular in front of his mouth.
• the microphone(s) can be placed at the level of the measurement device or else correspond to those used for measuring the oscillations of the Pi points.
• the microphone(s) can be topped with an exponential horn in order to increase their directivity and sensitivity.
• the aperture of the microphone(s) is at least equal to 0.5 mm millimeters. If necessary, a deflector can be positioned in front of the individual's mouth to attenuate the sound waves going towards the microphone(s) and thus avoid saturating them.
• the latter can be determined using the various methods mentioned below to measure the oscillation of the Pi points.
• the incident vibration Once the incident vibration is generated, it will propagate through the entire respiratory system until it reaches the surface of the chest in the form of resulting vibrations. During its journey, the incident vibration will be transformed according to the different media crossed. In particular, its amplitude can be modified. The celerity of the vibration can also be affected and there then appears a delay or a phase shift between the resulting vibration and the incident vibration. The incident vibration will therefore be broken down into a multitude of resulting vibrations with different characteristics, each resulting vibration being characteristic of the part of the respiratory system that the incident vibration will have crossed. Thus, the study of these resulting vibrations provides a wealth of information on the state of the media crossed (dense, soft, presence of hollows, etc.) allowing the establishment of a diagnosis.
• This surface S has an area of at least 10 cm 2 and is characterized by a plurality of points Pi.
• the surface S covers the part of the bust of interest to establish a diagnosis, i.e. it covers the part of the respiratory system for which one wishes to study the resulting vibrations.
• the area of the surface S is thus adapted to the desired study.
• this surface may correspond to the surface of the front part of the thorax, to that of the rear part, to those of one or other of the lateral parts of the thorax, to that of the front or rear part of the neck, to that of the front or back part of the abdomen, or to any combination of these surfaces.
• the surface S can also correspond to the entire surface of the individual's bust.
• the surface S can be composed of one or more discontinuous surfaces.
• the surface S can for example correspond to that of the front part of the neck and to that of the front part of the thorax covering the right lung.
• Each point Pi on the surface S represents a point on the surface of the bust where the signal Sp i of a resulting vibration will be studied.
• the surface S may comprise at least 5 points Pi per 10 cm 2 , in particular at least 10 points Pi per 10 cm 2 .
• the determination of the signal Spi at each point Pi is carried out by measuring the oscillation of the surface of the bust at each point Pi.
• the measuring device is advantageously placed at a distance from the individual, and its use does not include any direct contact with the individual.
• This aspect of the invention is particularly interesting in the context of an infectious pathology such as COVID19, where any contact with the patient can lead to an infection of the operator by the patient carrying the agent responsible for the pathology.
• the measuring device used in the invention can illuminate each point Pi with waves, then analyze the signal of the waves reflected on the surface S.
• each signal Sp i is a lane-forming signal.
• the oscillation at each point Pi can be determined by successively taking images.
• the measurement of the oscillation of each point Pi in step b) is carried out by means of the reflection of ultrasonic waves on said surface S, by means of the reflection of electromagnetic waves on said surface S or by tapping successive images of said surface S.
• the measuring device may comprise an array of ultrasonic wave emission transducers and an array of reception transducers (or microphones) of ultrasonic waves.
• the measuring device may be that described in the document in the document WO2018015638.
• the measuring device may comprise a 3D camera which additionally provides a 3D image corresponding to the x y z coordinates in the space of points, in particular points Pi, of a surface of the bust, in particular the surface S, of the individual . This 3D camera makes it possible in particular to position said surface at a desired distance from the measuring device or to complete the data collected in the context of the diagnosis of a pulmonary pathology, for example for individuals suffering from chronic obstructive pulmonary disease (COPD).
• COPD chronic obstructive pulmonary disease
• the ultrasonic reception transducers can be used to obtain the signal Sp r of the incident vibration by measuring the sound leaving the mouth of the patient/individual, as seen above.
• the determination of the Spi signals in the context of the reflection of ultrasonic waves can be carried out by the method described in the document WO2018015638.
• the measuring device can be a radar or laser system.
• the measuring device carries out a series of measurements at a rate greater than at least twice the value of the highest frequency of the signal Sp r .
• the cadence can be greater than at least twice the frequency of the fundamental.
• the rate may be at least 300 measurements taken per second, in particular at least 500 measurements taken per second, in particular at least 600 measurements taken per second.
• the duration of the measurement of the oscillation of each point Pi corresponds at least to that of the duration of generation of the incident vibration.
• the data can then be segmented over shorter durations when it is the evolution of the dynamics of at least one parameter p that is studied.
• the measurement of the oscillations at each point Pi can in particular begin upstream of the generation of the incident vibration, so as to observe the modifications of oscillation of the points Pi generated by the appearance of the resulting vibrations.
• each point Pi When the oscillation of each point Pi is measured by means of the reflection of ultrasonic waves, it can be excluded from the remainder of the method the points Pi (and their signals) having too low a coherent reflectivity, in particular a lower coherent reflectivity at 0.1.
• the coherent reflectivity parameter is representative of the error in determining the speed of movement of the surface S.
• all of the points Pi can be illuminated under circumstances fault, i.e. without incident vibration. Then it can be correlated for each point Pi the signal s(t) measured over a time t with that of the same point s'(t) measured over a subsequent time t+ ⁇ t.
• the signals s(t) and s'(t) are measured over a period of, for example, 2 milliseconds. ⁇ t is tiny, of the order of a millisecond or less. Thus, in theory, these signals are almost identical and only a tiny time lag ⁇ separates them.
• Coherent reflectivity can be calculated as follows: 1- we calculate the Fourier transforms of the signals s(t) and s'(t), i.e. S(f) and S'(f) 2- the two signals s(t) and s'(t) are correlated, ie the product S(f) .
• S'(f)* 3- the coherent reflectivity is calculated by integrating the real part of the product over the operating frequency band of the measuring device, in particular from 30 kHz to 60 kHz.
• This step corresponds to the determination of the transformations undergone by the incident vibration, to detect anomalies.
• the resulting vibrations at each point Pi are analyzed at the frequency or frequencies of the incident vibration.
• the resulting vibration measured at each point Pi is the sum of multiple vibrations coming from various parts of the body.
• the parameters p of the signals Sp i it is necessary to exclude the data relating to the frequency or frequencies not corresponding to those of the incident vibration. More particularly, one or more parameters p of the signals Sp i are analyzed.
• parameter p it is understood in the invention the amplitude of a signal Sp i , a delay or a phase shift or the level of correlation of the signal Sp i with respect to the signal Sp r of the incident vibration.
• the amplitude of a signal Sp i can in particular be correlated with that of the signal Sp r of the incident vibration.
• the frequency band used in step c) is around the fundamental.
• the frequencies of the incident vibration used during step c) correspond to a band of at most 150 Hz around the fundamental frequency of the incident vibration.
• the frequency band is at most 100 Hz, in particular at most 60 Hz, for example at most 40 Hz.
• the frequency band can be centered on the fundamental frequency.
• the analysis of the parameters p of the signals Sp i can be compared at regular intervals. Indeed, the inventors discovered unexpectedly that the evolution over time of the parameters p of the Spi signals provide very relevant data for establishing a diagnosis. Indeed, these data make it possible to establish the dynamics of propagation of the incident vibration.
• the data relating to the parameters p analyzed can be distributed on a vibration map in two dimensions, or even in three dimensions.
• the dimensions of these maps can represent the special distribution (2D or 3D) of the points Pi between them.
• Each point Pi can be assigned a color depending on the value of the parameter(s) p analyzed.
• the established vibration map makes it very easy to identify areas and values of interest, from which a diagnosis will be established, in particular using a reference vibration map.
• This reference vibration map can be a map established from a sample of several individuals, in particular healthy or sick individuals, or a map previously established for the individual, in particular before his illness.
• the or one of the parameters p is the amplitude of the signal Sp i of the resulting vibration.
• This data is useful for determining what type of medium (dense, soft) the incident vibration has passed through. It should be noted that these amplitude data are raw data which may be interfered with by measurement noise from the oscillations.
• One way of reducing the noise in the case of a measurement by reflection of ultrasonic or electromagnetic waves is to illuminate the surface S in a homogeneous manner.
• the or one of the parameters p can be the amplitude of the signal Sp i of the resulting vibration correlated with the incident vibration.
• step b), or step c) comprises for each point Pi the correlation, at the frequency or frequencies of the signal Sp r , of the signal Sp i with the signal Sp r normalized in amplitude and the determination of the signal amplitude of the resulting vibration correlated with the incident vibration.
• the data obtained are advantageously less interfered with by noise, and therefore more easily exploitable.
• This data can be obtained using the following steps: 1- the Fourier transforms of the signal Sp r and of the signal Spi are calculated for each point Pi, which will be denoted Sp r (f) and Sp i (f), 2- we divide the complex spectrum of Sp r (f) by its modulus: Sp r (f)/
• step b), or step c) comprises for each point Pi the correlation, at the frequency or frequencies of the signal Sp r , of the signal Sp i , in particular normalized in amplitude, with the signal Sp r , in particular normalized in amplitude, and the determination of the delay or the phase shift with respect to the incident vibration at each point Pi.
• Such data translate a modification of the celerity of the incident vibration, and can indicate the characteristic celerity of the incident vibration in the environments crossed.
• Delay data can be obtained using the following steps: 1- we calculate the Fourier transforms of the signal Sp r and of the signal Sp i for each point Pi, which we will denote Sp r (f) and Sp i (f), 2- we divide the complex spectra of Sp r (f) and Sp i (f) by their respective moduli: Sp r (f)/
• Phase shift data can be obtained using the following steps: 1- we calculate the Fourier transforms of the signal Sp r and of the signal Sp i for each point Pi, which we will denote Sp r (f) and Sp i (f), 2- the frequency component(s) of interest is selected, their number rising to M components, and 3- the phase of each complex spectrum is subtracted from the M frequency components: arg(Sp i (f)) - arg(Sp r (f)).
• step b), or step c) comprises for each point Pi the correlation, at the frequency or frequencies of the signal Sp r , of the signal Sp i normalized in amplitude with the signal Sp r normalized in amplitude and determining the percentage correlation with the incident vibration at each point Pi.
• This data can be obtained using the following steps: 1- we calculate the Fourier transforms of the signal Sp r and of the signal Sp i for each point Pi, which we will denote Sp r (f) and Sp i (f), 2- we divide the complex spectra of Sp r (f) and Sp i (f) by their respective moduli: Sp r (f)/
• An intercorrelation of 1 means that the phases of the signals Sp i and Sp r are 100% identical.
• the dynamics of evolution over a given time of at least one parameter p of the signal SP i of each point Pi is analyzed by the identical sequential division in time of the signal Sp r and of each signal Spi and identical between the signal Sp r and each signal Sp i , then by analyzing at least one parameter p in each sequence of a signal Sp i and comparing the result obtained between each sequence for each signal Sp i .
• said at least one parameter p analyzed can be compared with a reference value p ref of the same nature and/or the change in said at least one parameter p analyzed can be compared with a change in reference p v ref .
• the reference value p ref can correspond to a value to be reached, to a value previously obtained at point Pi for the same individual or even to an average value obtained in a population of individuals for this point Pi, in particular a population of individuals healthy or sick.
• the reference evolution p v ref can correspond to an evolution to be reached, to an evolution previously obtained at point Pi for the same individual or even to an average evolution obtained in a population of individuals for this point Pi, in particular a population d healthy or sick individuals.
• the invention also relates to a method for characterizing the vibration of a surface of the bust of an individual suffering from a pathology affecting at least one organ belonging to the respiratory system, in particular with the aim of establishing a diagnosis of the response to a therapeutic treatment for said lung disease, said method comprising: a) the characterization of signals Sp i of a plurality of points Pi belonging to a surface S of the individual using the method as defined above, where the surface S covers said at least one organ affected by the pathology pulmonary, and b) comparing said at least one parameter p at each point Pi with a reference value p ref of the same nature and/or comparing the evolution of said parameter p at each point Pi with a reference evolution p vref , said value of reference p ref corresponding to a value to be reached or to the value of the parameter p at the point Pi as determined previously, in particular before taking the therapeutic treatment, the said reference evolution p vref corresponding to an evolution to be achieved or to the evolution of the parameter p at the point Pi as
• FIG. 1A is the spectrogram of the voice around the fundamental of the vocalization uttered by the subject (x-axis: frequencies in Hz; y-axis: time in seconds). The nuance scale is in decibels per Hz.
• Figure 1B is a 3D cartography of the points Pi forming the study surface of the resulting vibrations where for each point Pi is indicated its coherent reflectivity of the ultrasonic waves used to measure its oscillation (axis x, y and z in meters). The shade scale is in arbitrary units.
• FIG. 1C is a 3D cartography of the points Pi forming the study surface of the resulting vibrations where, for each point Pi, its amplitude correlated to the voice is indicated.
• the shade scale is in decibels.
• FIG. 1D is a 3D cartography of the points Pi forming the study surface of the resulting vibrations where, for each point Pi, the delay relative to the voice is indicated.
• the nuance scale is in number of time samples with an implemented sampling period of 1/500kHz.
• FIG. 2A is the voice spectrogram around the fundamental of the vocalization uttered by the subject (x-axis: frequencies in Hz; y-axis: time in seconds). The nuance scale is in decibels per Hz.
• FIG. 2B is a 3D cartography of the points Pi forming the study surface of the resulting vibrations where, for each point Pi, its amplitude is indicated. The shade scale is in decibels.
• FIG. 2C is a 3D cartography of the points Pi forming the study surface of the resulting vibrations where, for each point Pi, its amplitude correlated to the voice is indicated.
• the shade scale is in decibels.
• Figure 2D is a 3D cartography of the points Pi forming the study surface of the resulting vibrations where for each point Pi the delay with respect to the voice is indicated.
• the nuance scale is in number of time samples with an implemented sampling period of 1/500kHz.
• FIG. 2E is a 3D cartography of the points Pi forming the study surface of the resulting vibrations where, for each point Pi, its level of correlation with the voice is indicated.
• the shade scale is in percentage.
• FIGS. 3A and 3A' illustrate the surface of the subject studied in the two situations.
• FIGS. 3B and 3B' are the voice spectrograms around the fundamental of the vocalization pronounced by the subject (x-axis: frequencies in Hz; y-axis: time in seconds). The nuance scale is in decibels per Hz.
• Figures 3C and 3C' are 3D maps of the points Pi forming the study surface of the resulting vibrations where for each point Pi is indicated its coherent reflectivity of the ultrasonic waves used to measure its oscillation (x, y and z axis in meter).
• the shade scale is in arbitrary units.
• the figures 3D and 3D' are 3D maps of the points Pi forming the study surface of the resulting vibrations where, for each point Pi, its amplitude correlated to the voice is indicated.
• the shade scale is in decibels.
• FIGS. 3E and 3E are 3D maps of the points Pi forming the study surface of the resulting vibrations where, for each point Pi, the delay relative to the voice is indicated.
• the nuance scale is in number of time samples with an implemented sampling period of 1/500kHz.
• Element 9 corresponds to the spectrogram of the subject's voice over a period of slightly more than 8 seconds (x-axis: frequencies in Hz; y-axis: time in seconds). The nuance scale is in decibels per Hz.
• Elements 1 to 8 represent the dynamics of evolution of the amplitude of the signal at each point Pi correlated to the voice.
• Each element 1 to 8 is a 2D cartography of the points Pi forming the study surface of the resulting vibrations where for each point Pi is indicated its amplitude correlated to the voice.
• the shade scale is in decibels.
• Each item 1 to 8 illustrates the result obtained over different measurement times (1: 0-1 sec; 2: 1-2 sec; 3: 2-3 sec; 4: 3-4 sec; 5: 4-5 sec ; 6: 5-6 sec; 7: 6-7 sec; 8: 7-8 sec).
• the correspondence of the measurement time for each element 1 to 8 with respect to the voice of the subject is represented on element 9.
• the vibration characterization of an individual's bust was carried out using an ultrasonic imager.
• This imager comprises an array of 256 ultrasound wave emission transducers (model MA40S4S from Murata) and 256 reception microphones (model FG-23329 from Knowles) of these waves.
• This network of microphones also allows the reception of the sound emitted by the tested subject.
• the ultrasonic frequency band used is 30 to 60 kHz.
• Microphone pre-amplification is 40 dB.
• Each transmitting transducer and each microphone is fitted with an exponential horn bringing the transmitting aperture of the transmitting transducers to 13 mm and the receiving aperture of the microphones to 13 mm.
• the sampling of the reception signal and the voice of the test subject is 600 Hz.
• the sampling rate is less than 10 ns.
• the test subject is a healthy subject who is asked to pronounce the vocalization of the phoneme "A" repeated briefly.
• the resulting vibrations are characterized at the surface of his front bust from the waistband to the lower neck.
• the spectrogram of the subject's voice is shown in Figure 1A.
• Figure 1A The spectrogram of the subject's voice is shown in Figure 1A.
• the frequencies of higher amplitudes are concentrated in the band from 70 to 110 Hz (> 30 dB/Hz).
• the characterization of the resulting vibrations is carried out on this frequency band.
• Figure 1B represents the coherent reflectivity of ultrasonic waves on the study surface. The closer the value is to 1, the better the reflectivity of the waves. A reflectivity greater than 0.1 makes it possible to obtain a good interpretation of the signal received by the microphones. Also, the study surface was subsequently restricted to points for which a reflectivity was equal to or greater than 0.1.
• the signal amplitude of the resulting vibrations correlated to the subject's voice is shown in Figure 1C. As can be seen, the resulting vibrations have a high amplitude at the thoracic level and a weaker one at the level of the abdomen.
• the test subject is a healthy subject who is asked to pronounce the continuous and sustained vocalization of the phoneme "A".
• the resulting vibrations are characterized at the surface of her back bust from the waistband to the lower neck.
• a healthy subject pronounces a simple vocalization of the phoneme "A” in two situations: normal and with a mask stuck on the lower right part of the back (shown in Figures 3A and 3A').
• This mask less elastic than the skin, simulates an anomaly since it will cause an abnormal vibration of the area it covers.
• the resulting vibrations are characterized at the surface of her back bust from the waistband to the lower neck.
• Figures 3B and 3B' represent the spectrogram of the subject's voice in the two situations. These spectrograms are, as expected, almost identical.
• the frequency band kept for the normal situation is 106 to 117 Hz and the one kept for the anomaly situation is 103 to 114 Hz.
• Figures 3C and 3C' represent the coherent reflectivity of the study surface. We can see in particular that the zone of good reflectivity (>0.1) is equivalent in the two situations for the same individual. For the characterization of the resulting vibrations, the study surface was subsequently restricted to the points for which a reflectivity was equal to or greater than 0.1.
• Figures 3D and 3D' represent the amplitude of the vibration signal correlated to the voice. It can be seen here very distinctly that the area covered by the mask has a very reduced amplitude compared to the same area in the normal situation. It is thus demonstrated that the alteration of a vibration zone is highlighted in a distinct manner in the invention, making it possible to arrive at a diagnosis.
• Figures 3E and 3E' show the delay of the vibration signal relative to the voice. Here also are observed strong differences at the level of the hidden zone. The delay which is almost zero in the normal situation becomes stronger in the case of the cache. Thus, it is also demonstrated that several components of the resulting vibrations are altered by the presence of an anomaly, and well highlighted by the method of the invention.
• the test subject is a healthy subject who is asked to pronounce the vocalization of the phoneme "A" repeated briefly.
• the resulting vibrations are characterized at the surface of her back bust from the waistband to the lower neck.
• Figures 4a and 4b show the dynamics of the amplitude evolution of the signal of the resulting vibrations correlated to the voice. We can see in these figures that the amplitude remains very strong in certain areas, while it decreases or increases in others over time.
• Example 2 Differentiation of individual s healthy s and patient s affected by b chronic obstructive pulmonary disease (COPD)
• COPD chronic obstructive pulmonary disease
• This imager further comprises a 3D camera which simultaneously provides a conventional image and a 3D image (x y z of the points of the surface of the chest of a subject in front of the device).
• the subject is either a healthy individual or a patient with COPD.
• the height of the panels of the imager, carrying the network of ultrasound wave emission transducers, is adjusted or adapted to the size of the subject by placing his xiphoid appendage in the middle of the measurement zone.
• the dimension of this area is 400 mm high by 300 mm wide.
• the subject is positioned from the front (for a measurement of cardiac movements) or from behind (for a measurement of the vibrations of the lungs from a vocalization) at a distance of between 600 mm and 700 mm, again thanks to the 3D camera.
• the subject As part of a measurement of cardiac movements, the subject is asked to hold his breath with his lungs full. The subject is then asked to perform a series of ten flexions before the measurement in order to increase the amplitude of the cardiac vibrations.
• the subject As part of a measurement of the vibrations of the lungs, the subject is asked to inflate his lungs in order to perform a vocalization.
• the notion of full lungs is achieved by means of a spirometry test repeated three times in order to assess the subject's inspiratory capacity.
• the purpose of these tests is to train the subject to have the same value of inspiratory capacity three times in a row to within 5%, so when the subject appears in front of the imager, the subject is asked to inflate his lungs to the maximum. of their abilities (as in the spirometry test) before beginning vocalization or holding their breath. This manipulation makes it possible to normalize the volume of air in the lungs of the subjects.
• the subject is asked to carry out the experiment 3 times in a row using different vocalizations, each corresponding to the phonemes of “A”, “O” and “ZE”. The point of using these different phonemes is to excite different parts of the lungs. The subject is also asked to place the arms in a cross on the torso and to reproduce the same vocalizations.
• the acquisition frequency of the imager is set to 600 ips (images per second) for men and 1000 fps for women.

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• 2021
  • 2021-04-16 FR FR2103989A patent/FR3121830A1/fr active Pending
• 2022
  • 2022-04-15 WO PCT/EP2022/060183 patent/WO2022219190A2/fr not_active Ceased
  • 2022-04-15 US US18/555,145 patent/US20240188844A1/en active Pending
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