apparatus for use in diagnosing the presence of obstructive sleep apnea in a patient and method of d

专利摘要:
APPARATUS FOR USE IN THE DIAGNOSIS OF THE PRESENCE OF OBSTRUCTIVE SLEEP APNEA IN A PATIENT AND METHOD OF DIAGNOSING THE PRESENCE OF OBSTRUCTIVE SLEEP APNEA IN A PATIENT.A device for use in diagnosing the presence of obstructive sleep apnea (OSA) in a patient includes one. structured sensitivity module for measuring a parameter indicative of a tremor in the muscles of the patient's neck, tongue and/or throat while the patient is awake, the parameter not being c) airflow through the patient's airway. The sensitivity module generates one or more electrical signals based on the measured parameter. The apparatus also includes a processor operatively coupled to the sensitivity module, the processor being structured to receive the one or more electrical signals, perform an analysis of one or more electrical signals and, based on the analysis, determine whether the tremor has a frequency in at least one predetermined frequency range that is indicative of OSA.
公开号:BR112013009346A2
申请号:R112013009346-3
申请日:2011-10-12
公开日:2021-05-25
发明作者:Michael Edward Colbaugh；Ronald Dean Fligge；Vijay Kumar Iyer；Douglas Mechlenburg；Edmund Arnliot Shaw；Nathan Zimmerman
申请人:Koninklijke Philips Electronics N.V.；
IPC主号:

专利说明:

1/51 APPARATUS FOR USE IN THE DIAGNOSIS OF THE PRESENCE OF OBSTRUCTIVE SLEEP APNEA IN A PATIENT AND METHOD OF DIAGNOSIS OF THE PRESENCE OF OBSTRUCTIVE SLEEP APNEA IN A
PATIENT The present invention pertains to the diagnosis of obstructive sleep apnea and, in particular, to apparatus and methods for collecting information from a patient who is. awake and that can be used in the diagnosis of obstructive sleep apnea in the patient, . . 10 Obstructive sleep apnea (OSA) is a condition in which an individual experiences a reduction or complete stop in airflow while sleeping despite the individual continuing to attempt to breathe. These events occur when muscles relax during sleep, causing the soft tissue at the back of the throat to collapse and block the upper airway. This leads to partial reductions (known as hypopnoeas) and complete pauses (known as apnoeas) in breathing. An apnea event is defined as a cessation of airflow for at least 10 seconds during sleep. Hypopnea is defined as an abnormal respiratory event that lasts for at least 10 seconds with a reduction of at least 30% in thoracoabdominal motion or blood flow. air as compared to * a baseline value with at least 4% oxygen saturation. Most apnea events last between 10 and 30 seconds, but some persist for a minute or more. This can lead to abrupt reductions in blood oxygen saturation, with oxygen levels dropping as much as 40% or more in severe cases. These apnea events cause the individual to wake up briefly, which restores normal breathing. Since these apneas can occur tens or hundreds of times a night, the disruption caused results in q FOLLOW LINSANOA Al ASR tt A
2/51 ' : individual being excessively tired during the day.
A common measure of sleep apnea is the apnea-hypopnea index (AHI). This is a number that represents the combined number of apneas and hypopneas that occur per hour of sleep.
The following classification is often used: AHI < 5: No OSA/Healthy “ 5 < AHT <1l5: Mild OSA : 15 < AHI < 30: Moderate OSA * 10 30 < AHI OSA Severe . Obstructive sleep apnea (OSA) is usually diagnosed in a sleep laboratory.
However, most patients suffering from obstructive sleep apnea are never properly diagnosed as general practitioners often deal with the symptoms of daytime fatigue and poor sleep by prescribing sleep pills or similar medication.
Physicians may be hesitant to send patients to a sleep lab right away, due to the high cost involved and long wait times.
Commonly, patients are only referred when all other attempts at treatment have failed and the patient continues to complain about poor sleep and daytime drowsiness.
However, once the patient with suspected OSA Í is referred to a sleep laboratory, OSA is confirmed in about 85% of cases.
OSA is diagnosed in a sleep laboratory with the help of a “polysomnography” that is performed over the course of one or more nights while the patient is asleep.
Polysomnography may involve the use of an electroencephalogram (EEG - electroencephalogram), an electrocardiogram (ECG - electrocardiogram), an electroculogram (EOG " - electroculogram), an electromyogram (EMG - electromyogram) and/or respiratory chest bands and flow measurement de Eita SYNCAORIA DA de LNOEA paddles MARINA an———— —————
Ú 3/51 nasal air, blood oxygen levels and/or other physiological parameters. As a large number of sensors and devices are required for polysomnography, this procedure is not very comfortable or convenient for the patient.
Generally, apnea and hypopnea events in polysomnography data are identified by a physician who . manually inspects short intervals (approximately 30 seconds) of data, and individually ranks the 10 relevance of these intervals. Apnea events are characterized by the flow of air through the patient's nasal passage stopping (or nearly stopping) while the chest and abdominal breathing movement continues. The number of identified events and the average number of events per hour are used as an indicator of whether the patient has OSA and, if so, its severity. However, a substantial amount of effort is required to scan the data over an entire night in order to detect and count all apnea and hypopnea events and determine the AHI value for a patient.
Alternative techniques for diagnosing OSA have been proposed, which involve investigating a patient's snoring sounds. Such a technique is described in] "Investigation of Obstructive Sleep Apnea Using Nonlinear Mode Interactions in Nonstationary Snore Signals" by Ng et al, Annals of Biomedical Engineering, Vol. 37, No. 9, September 2009, pp. 1796-1806 However, this technique again requires the patient to attend a sleep lab and be monitored while sleeping.
Therefore, there is a need for a more efficient method and apparatus for assessing OSA that can be used while the patient is awake. This method and device would allow more patients with suspected OSA or FM MATA pesto from 11/05/2021, p. 15/200 — pu——<<ca <àvoa«orºr纗: |
- i 4/51 | possible to be tested and would increase the number of patients with OSA who received appropriate treatment for their condition. ! In one embodiment, an apparatus for use in the | diagnosis of the presence of obstructive sleep apnea (OSA) in a patient is provided, which includes a structured sensitivity module to measure a parameter indicative of a tremor in the patient's neck, tongue, and/or throat muscles | . while the patient is awake, the parameter is not | |, exclusively the airflow through the airways of the | - 10 patient.
The sensitivity module generates one or more signals | electrical systems based on the measured parameter.
The appliance too | includes a processor operatively coupled to the sensitivity module, the processor being structured to receive the one or more electrical signals, perform an analysis of one or more electrical signals and, based on the analysis, determine whether the tremor has a frequency in at least one predetermined frequency range that is indicative of OSA.
In another embodiment, an apparatus for use in diagnosing the presence of obstructive sleep apnea (OSA) in a patient is provided which includes a (i) first structured sensitivity module for measuring a first parameter indicative of a tremor in the muscles of the patient. the patient's neck, tongue and/or throat while the patient is awake, the first sensitivity module generating one or more first electrical signals based on the first measured parameter and (ii) a second sensitivity module structured to measure a second parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles while the patient is awake, the second parameter being different from the first parameter, the second sensitivity module generating one or more second electrical signals based on the second measured parameter.
The apparatus also includes a processor operatively coupled to the first sensitivity module | ETA AZ JEI UN It ro —
Ú 5/51 NS and the second sensitivity module, the processor being structured to: (i) receive the one or more first electrical signals, perform a first analysis of one or more first electrical signals and, based on the first analysis, perform a first determination of whether the tremor has a frequency in at least a predetermined frequency range that is indicative of OSA, (ii) receiving the um. or more second electrical signals, perform a second analysis of one or more second electrical signals and, based on the second analysis, perform a second determination of whether the tremor has a frequency in the at least one predetermined frequency range that is indicative of OSA, and (iii) determining whether the patient has OSA based on at least the first determination and the second determination.
In yet another embodiment, a method of diagnosing the presence of obstructive sleep apnea (OSA) in a patient is provided, which includes measuring a first parameter indicative of a tremor in the patient's neck, tongue, and/or throat muscles while the patient is awake, determining, based on the first parameter, whether the tremor has a frequency in at least a predetermined frequency range that is indicative of OSA, assessing whether the patient is likely to have OSA using a "second assessment methodology, the second assessment methodology is not based on measuring any parameters ' indicative of a tremor in the patient's neck, tongue and/or throat muscles, and determining that the patient has OSA only if at least the determination step determines that the tremor has a frequency in at least a predetermined frequency range and the assessment step determines that the patient is likely to have OSA.
In another embodiment, a method of diagnosing the presence of obstructive sleep apnea (OSA) in a patient is | Petition 870210042874, of 05/11/2021, p. 17/200 o.
provided, which includes measuring a parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles while the patient is awake, the parameter not being airflow through the patient's airway, determination, based in the parameter, whether the tremor has a frequency in at least one predetermined frequency range that is indicative of OSA, and determining that the patient has OSA if the determining step Ú determines that the tremor has a frequency in the. at least one - 10 preset frequency range.
In yet another embodiment, a method of diagnosing the presence of obstructive sleep apnea (OSA) in a patient is provided, which includes providing a predetermined amount of airflow resistance or pressure level above or below atmospheric pressure. for the patient to change the patient's charging pressure Or deviation of the patient's breath, after the provision step, measuring a parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles while the patient is awake, determination, based on the parameter, whether the tremor | has a frequency in at least a predetermined frequency range that is indicative of OSA, and determination that the patient has OSA is the determination step. determine that the tremor has a frequency in at least a predetermined frequency range.
In yet another embodiment, a method of diagnosing the presence of obstructive sleep apnea (OSA) in a patient is provided, which includes measuring a first parameter indicative of a tremor in the muscles of the neck, tongue, and/or throat of the patient. patient while the patient is awake, measurement of a second parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles while the patient is awake, The second [Elcio SIEISOASTA. AGIDO, sink AUEI rn —
— the " o " as 17/51 Ú parameter being different from the first parameter, taking a first determination of whether the tremor has a frequency in at least a predetermined frequency range that is indicative of OSA, based on the first parameter, taking of a second determination of whether the tremor has a frequency in the at least one predetermined frequency range that is indicative of OSA, based on the . second parameter, and determination of whether the patient has OSA based on at least the first determination and the second determination, These and other objectives, aspects and characteristics of the present invention, as well as the methods of operation and functions of the related elements of structure and the combination of parts and manufacturing economies will become apparent upon consideration of the following description and the appended claims, with reference to the accompanying drawings, all of which form part of this specification, in which like reference numerals designate corresponding parts in the several Figures. However, it is to be expressly understood that the drawings are for the purposes of illustration and description only and are not intended as a definition of the limits of the invention.
FIGURE 1 is a schematic diagram of an exemplary device that can be used to detect OSA in a patient, based on airflow data, which is = collected from the patient while he or she is awake; A FIGURE 2 is a functional diagram illustrating operations performed by or on the device of FIGURE 1; FIGURE 3 is a schematic diagram of an exemplary device that can be used in detecting OSA in a patient based on data that is collected from the patient while he or she is awake, which are based on detection of modulated impedance in the neck area Or — Petition 870210042874. of 11/05/2021, pg. 19/200 | ——— w—
The patient's throat 8/51;
FIGURE 4 is a schematic diagram of an exemplary device that can be used to detect OSA in a patient based on data that is collected from the patient while he or she is awake, which is based on the detection of possible muscle changes in the throat;
FIGURE 5 is a schematic diagram of an apparatus
. specimen that can be used in detecting OSA in a patient based on data, which is collected from the patient * 10 while he or she is awake employing actimetry;
FIGURE 6 is a schematic diagram of an exemplary device that can be used to detect OSA in a patient, based on the movement/position data that is collected from the patient while he or she is awake.
which are based both on detecting possible muscle changes in the throat and on actimetry;
FIGURE 7 is a schematic diagram of an exemplary apparatus that can be used to detect OSA in a
: patient based on data that is collected from the patient while he or she is awake employing ultrasound measurements;
FIGURE 8 is a schematic diagram of an exemplary device that can be used to detect OSA in a patient based on data that is collected from the patient while he or she is awake that employs sound generation and mn detection;
FIGURE 9 is a schematic diagram of an exemplary device that can be used to detect OSA in a patient based on data that is collected from the patient while he or she is awake that employs airway sound detection;
FIGURE 10 is a schematic diagram of an exemplary apparatus that can be used to implement an OSA detection method based on voltage measurements;
FIGURE 11 is a schematic diagram of an exemplary apparatus that can be used to implement a method of detecting OSA using a fluid filled bag; FIGURE 12 is a schematic diagram of an exemplary apparatus that can be used to implement a . OSA detection method using acoustic pharyngometry; FIGURE 13 is a schematic diagram of an exemplary apparatus that can be used to implement a method of detecting OSA using evoked nerve/potential conduction;
FIGURE 114 is a schematic diagram of an exemplary apparatus for detecting OSA that employs multiple methods and/or apparatus that detect characteristic fear associated with OSA;
FIGURES 15 and 16 are schematic diagrams of the exemplary apparatus for detecting OSA, which employs a combination of methods, including one that is based on detection of characteristic tremor associated with OSA and one that is not based on detection of characteristic tremor associated with OSA ; and FIGURE 17 is a schematic diagram of an exemplary apparatus for detecting OSA employing a method which is based on detection of the characteristic tremor associated with OSA and a charge/flow control device.
Í As used herein, the singular form of “a”, “an” and “the” include plural references, unless the context clearly mentions otherwise.
As used herein, the statement that two or more parts OR components are "coupled" shall mean that the parts are joined or operate together either directly or indirectly, That is, through one or more intermediate parts OR components, provided that one reaction occurs.
As here | [ONA A E RR a ——n -
used, "directly coupled"" means that two elements are directly in contact with each other.
As used herein, "fixedly coupled" or "fixed" means that two components are coupled so that one can move the other while maintaining a constant orientation relative to one another.
As used herein, the word “unitary” . means that a component is created as a single part or unit.
That is, a component that includes parts that are . 10 created separately and then coupled with a unit, and is not a "unitary" component or body. As used herein, the statement that two or more parts or components "fit" with each other must mean that the parts exert a force in relation to the other either directly or through one or more intermediate parts or components.
As used herein, the term "number" shall mean one or more whole numbers greater than one (ie, a plurality). The directional phrases used here, such as, for example, and among others, above, below, left, right, top, bottom, front, rear and their derivations, refer to the orientation of the elements shown in the drawings are not limiting of the claims , unless . expressly mentioned in them.
People afflicted with OSA have increased compensatory muscle activation of the upper airways (the muscles of the neck, tongue, and/or throat) during wakefulness.
This muscle activation appears to be particularly prevalent in the genioglossus muscle (GG - genioglossus), which is a muscle in the human body that runs from the chin to the tongue.
The GG muscle is the important muscle responsible for protruding (or protruding) the tongue.
High compensatory muscle activation appears to be a product of high tonic activation
11/51 i of the muscle, combined with the generation of high negative pressure during inspiration.
In addition, increased compensatory muscle activation during wakefulness results in a characteristic tremor in the upper airways.
The test carried out by the owner of the present invention determined that Tremor has a particular characteristic frequency that has an association with OSA and a dissociation in patients without OSA. ' One of this characteristic frequency has been found to be in the *10 range of 30-40 Hz, although other variations are also possible.
So there is a signature that lingers throughout the day from the attack caused by sleeping sickness OSA.
In addition, the holder of the present invention hypothesizes that tremor resulting from elevated muscle activation (eg, GG) modulates respiratory airflow (at the characteristic frequency or frequencies) during wakefulness in those suffering from OSA, and developed a system and method for diagnosing OSA, which includes detecting the modulation of respiratory airflow caused by the characteristic tremor.
Such system and method are described in detail in European Patent Application No. EP 10185347.1 entitled "Apparatus and Method for Collecting Information", the disclosure of which is incorporated herein by reference.
This system and method are also described below.
FIGURE 1 shows an exemplary apparatus 2 of the 'EP application described above that can be used in detecting OSA in a patient based on the data that is collected from the patient while he or she is awake. In the exemplary embodiment, the apparatus 2 comprises an airflow measuring device 4, such as a pneumotachograph, to provide measurements of airflow during inhalations and exhalations by a patient.
As is known, a pneumotachograph 4 comprises a nasal mask, a face mask or a mouthpiece.
“a: o O ess == : 12/51 ' | | 6 that can be used by the patient, a pneumotachometer 8 that is connected to the nasal mask, face mask or mouthpiece 6, which measures the air flow being inhaled and exhaled by the patient through the nasal mask, face mask or mouthpiece 6 and provides an outlet in terms of a differential pressure and a pressure transducer 10 which is connected to the pneumotachometer 8 and which converts the differential pressure output into a signal. electrical, preferably digital samples. ' The electrical signal is provided from the pressure transducer - * 10 10 on the pneumotachograph 4 to a processor 12 where it is processed to determine information that can be used by a physician to determine if the patient has a sleep-related breathing disorder such as OSA .
Processor 12 is connected to a screen 14 that provides a visual indication of the processing result (such as information to be used by the physician in patient diagnosis and/or, in some implementations, an indication of whether the patient: has OSA or other breathing disorder). processor 12 is also connected to a memory 16 which can store the electrical signals produced from pneumotachograph 4 prior to processing by processor 12, as well as any results or results of processing performed by processor 12 on the electrical signals. . In the illustrated embodiment, the processor 12, the screen 14 and the memory 16 are contained in a processing unit 18 which forms a separate unit from the pneumotachograph 4. In this case, the electrical signals from the | Pneumotachograph 4 can be provided to Processor 12 in the | processing unit 18 through a connecting wire, | 30 wirelessly using WiFi, Bluetooth etc., or any other suitable means.
However, in alternative implementations, the pneumotachograph 4 and the processing unit 18 can be provided within a single [AS SOURCE 05/11/2021, p. 24/200 = —... ss |
NS 13/51 support. In both cases, the device 2 is preferably implemented as a lightweight device that can be easily held or used by the patient during a test procedure, without causing the patient undue discomfort.
Although not shown in FIGURE 1, it will be appreciated that apparatus 2 (and in particular processing unit 18) may include additional components such as . a user interface to allow a user of device 2 to input patient-specific commands and/or data -« 10 to processor 12 and/or an internal power supply, such as a battery, if device 2 is to be operated independently of an external power supply.
Furthermore, in alternative embodiments, the pneumotachograph 4 can be replaced by an alternative means that can provide airflow measurements, such as a nasal cannula.
FIGURE 2 is a functional diagram illustrating the operations performed by or on the device 2. In a first step 32, the electrical signals representing the air flow to and from the patient's lungs during breathing while the patient is awake are acquired from the pneumotachograph 4. Electrical signals preferably comprise digital samples representing the magnitude (ie rate) of the | . air flow at the respective sampling times, As suggested above, the first step 32 is performed while the ' patient is awake. Airflow rate samples are passed to the ; processor 12 where they are processed to provide | information regarding the patient's breathing condition. | 30 In some embodiments, this information is presented to a physician to assist the physician in diagnosing obstructive sleep apnea. In other embodiments, Processor 12 can further process the information to provide an indication of whether the patient has OSA, which can be produced by apparatus 2 to an operator (such as a physician), for example, using screen 14. that sample raw data may contain artifacts, which may affect the quality of the analysis performed in subsequent processing steps.
Therefore, it is desirable to provide a step that assesses the quality of the raw sample data and selects a subset of the data for one or more breath cycles that should be used in the « 10 subsequent processing steps. Thus, the first processing step performed by processor 12 is a pre-processing step (step 34 in FIGURE 2) in which the raw sample data is processed to identify N breath cycles (with a single breath cycle comprising a consecutive inhalation and exhalation) that should be used in subsequent processing steps.
Preferably, the N breath cycles selected are the breath cycles that best fit an average breath cycle for the patient. In particular, N is 12, although N can have any positive integer value.
Selection of the N breath cycles is, in the exemplary embodiment, performed as follows.
First, OS . Raw sample data is separated into individual breath cycles and preferably individual inhalation and exhalation segments.
The transition points between each inhalation and exhalation (ie when the patient starts exhaling after inhaling and exhaling after inhaling) can be easily identified from the zero crossings in the sample data.
Then, the breath cycles or individual inhalation and exhalation segments are filtered using one or more criteria, for example, a minimal extension, O [STONE ASAE E RR o CTT feature —— —
215/51 i - ' deviation from a mean extent (in total and also separately for inhalation and exhalation segments) and deviation from a mean shape. The N cycles or segments that best meet the required criteria are then selected for further analysis by processor 12. In one embodiment of the invention, in order to reduce the amount of time a patient needs to be . connected to test apparatus 2, processor 12 can perform the pre-processing step while os. data is *10 being collected, and may provide an indication to the patient or other user of the device 2 that the test can be stopped once data for N breath cycles have been collected.
After the pre-processing step, processor 12 performs a frequency analysis step 36 in which the sample data is converted to frequency domain and an average frequency spectrum is calculated. In particular, a sliding window Fast Fourier Transform (FFT) is applied to each individual breath cycle to give a frequency spectrum.
In some implementations, the moving window FFT can be applied to each complete inhalation or exhalation segment. Alternatively, in other embodiments, the 'Moving Window FFT' is applied only to a portion of each inhalation or exhalation segment close to the +sas peak airflow (i.e., when the airflow rate is at a local maximum). In other words, moving window FFT is applied in and around samples where peak airflow occurs during each inhalation and exhalation. This narrow moving window approach was found to provide a better dataset for use in subsequent analysis by processor 12. The N frequency-transformed breath cycles are then averaged to provide spectra.
- 16/51' of separate midrange frequencies for inhalation and exhalation.
The frequency spectrum obtained from sample airflow data for patients with a breathing disorder such as OSA was found to differ from the frequency spectrum obtained from healthy patients.
For example, changes have been identified in certain frequency ranges or ranges below 100 Hz, most notably the ranges. frequency ranges from 18 to 22 Hz and 30 to 40 Hz.
In particular, there is an elevation in the 30-40 Hz frequency range and a *10 decrease in the 18-22 Hz frequency range for a patient with OSA compared to a healthy patient.
"Similar characteristics were found in the mean inhalation frequency spectrum.
Thus, processor 12 extracts values for one or more spectrum parameters or frequency spectra determined in frequency analysis processing step 36. In particular, the value for at least one parameter is determined from signals in one or more frequency bands. that cover frequencies that are below 100 Hz.
Several different parameters can be extracted in the extraction step of aspect 38, according to the invention.
One parameter that can be extracted is the difference between the average exhalation frequency amplitude in a 'first frequency range, eg the 20-50 Hz range, or more specifically 25-45 Hz, OR even more ' specifically, 30-40 Hz (denoted fexao-20), And the average exhalation frequency amplitude in a second frequency range, eg a range of 12-30 Hz, OR, More specifically, 15-25 Hz, OR, even more specifically, 18-22 Hz (denoted feng22). The parameter value can be given by fexo-so - fes And, according to the observation described above, the parameter value for a healthy patient will generally be negative, while The value will be eso SID2IONSZSTS sd LUNS/22A. pa, JURID st td is : 17/81 : - | usually higher for a patient with OSA. Thus, the value of this parameter can be used by a physician or by device 2 to diagnose whether the patient has OSA.
It will be appreciated by those skilled in the art that a value for a similar parameter can be derived from the difference between the average inhalation frequency amplitude in these frequency ranges or the like. . Another parameter that can be extracted is the difference. between the average amplitude of exhalation frequency in a * 10 third frequency range, for example, a range of 0-20 Hz, Or more specifically 0-15 Hz, or even more specifically 0-10 Hz (denoted fexo-10) And the average amplitude of the inhalation frequency in the same or similar frequency range, for example, the variation 0-20 Hz, Or, more specifically, 0-15 Hz, or, even more specifically, 0O0- Hz (denoted fine). The parameter value can be given by fexo-10 - fine.
The parameter value will usually be close to zero for a healthy patient, while the value will generally be higher for a patient with OSA.
So, as the first parameter above, the value of this parameter can be used by a physician or by device 2 to diagnose whether the patient has OSA.
An additional parameter that can be extracted is the 1 difference between the average frequency range in the range 0-100 Hz for inhalation or exhalation (denoted fine-100 OR soft- '200, as appropriate) and a 'noise' level in frequencies above 100 Hz. ! Those skilled in the art will appreciate that the breadth | The average exhalation or inhalation frequency in a particular frequency range can be obtained from the output of the frequency analysis step 36 by averaging the amplitude of the frequency domain signal in the specified frequency range.
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— : 218/51 | It will also be appreciated that the invention is not limited to extracting the specific parameters set forth above and that information useful for characterizing a patient's breathing condition can be obtained from various other parameters that can be readily contemplated by those skilled in the art. In particular, parameters can be extracted from frequency ranges other than . specified above. Also, it is not essential that O . parameter or parameters are based on the average amplitude over a * 10 specified frequency range, as comparable results can be derived using other mathematical operations, such as the area under the frequency spectrum trace in the frequency range or the square of the amplitude.
In addition to extraction values for one or more parameters of the frequency domain signals, processor 12 can extract values of other parameters from the time domain samples provided by the pneumotachograph 4 (either the raw data or the data after the pre-step. processing 34) during aspect extraction step 38. For example, Processor 12 can extract time domain aspects such as average breath cycle length and the average ratio of inhalation length to exhalation length, ° Once the required parameter values have been extracted from the data, processor 12 may display ' -—. .-the parameter values to a physician or other health care professional via screen 14 (or other visual output, such as a printer-generated document) for use in assisting the physician in reaching a diagnosis for the patient or the Processor 12 can perform an additional processing step to combine the parameter values into a single useful punctuation mark. In this aspect 40 combination step, Processor 12 may combine the ' Petition 870210042874, of 05/11/2021, p. 30/200 2 A a values extracted from multiple parameters into a single score that can be used to aid in the diagnosis of a breathing disorder, as a score based on the value of several parameters described above has been found to be most useful in Reliable diagnosis of a breathing disorder that individual parameter values.
For additional achievements, the score can also : be based on other patient-related parameters, such as . body mass index (BMI), age, sex, Mallampati score of » 10, etc., which can be manually entered into the device 2 by the patient or operator.
The inventors of the present invention have devised several alternative measurement devices and/or methods that can be used to detect the characteristic tremor described above and/or the volumetric changes in airway structures resulting from the characteristic tremor described above. One or more of these alternative sensing devices and/or methods may be employed alone, in combination with The method of detecting respiratory airflow modulation caused by the characteristic tremor described above, Or in any combination to improve diagnostic accuracy and/ or OSA assessment.
. According to this alternative method, it was hypothesized that the tremor resulting from increased activation of muscles (eg, GG muscle) modulates the impedance along the throat or jaw (at the characteristic frequency or frequencies) during wakefulness in which suffer from OSA. FIGURE 3 shows an exemplary device 50 that can be used to detect OSA in a patient based on the data that is collected from the patient while he or she is awake that is based on the modulated impedance detection described above. In exemplary achievement, The apparatus
- Jo " | ' 20/51 — RSTCUNS FU —— E Eos mrEgE— eee O 50 comprises a source electrode 52 and one or more collection electrodes | 54. The source electrode 52 and the electrode(s) Collection 54 are structured to be selectively positioned on opposite sides or separate surfaces of the patient's neck or head.
Apparatus 50 also includes a main holder 56 which houses an alternating current (AC) source 58, a processor 60, a memory 62 and a screen 64. In operation, a small alternating current (for example, 100 KHz, at less than 0.5 mA current) is generated by the AC source 58 and flowed from the source electrode 52 to the collection electrode(s) 54. The current and/or voltage of the signal amplitude will be modulated by movement (tremor) of the muscles of the throat (eg, The GG muscle). The electrical signal collected by the collection electrode(s) 54 is provided to processor 60 which (using one or more software program routines) examines the amplitude of the received signal in order to identify the characteristic modulation (e.g., 30-40 Hz or some other frequency variation or variations) associated with OSA, if present, to determine if The patient has OSA.
The programmed processor 60 is connected to the screen 64, which provides a visual indication of the result of the processing.
Processor 60 is also connected to memory 62 so that memory 62 can store the electrical signals collected by collection electrode(s) 54 prior to processing by processor 60, as well as any results or results of the processing performed by processor 60 on electrical signals.
The patient's blood flow pulse and respiration, as well as Other parameters, can also be detected separately from the signal collected by the collection electrode(s) 54, Ee used for diagnostic purposes.
In exemplary achievement, | the device 50 is implemented as a lightweight device that | | Petition 870210042874. of 05/11/2021, p. 32/20 o | the 21/51 can be easily held or used by the patient during a test procedure without causing the patient undue discomfort. Although not shown in FIGURE 3, it will be appreciated that apparatus 50 (and in particular holder 56) may include additional components, such as a user interface, to allow a user of apparatus 50 to enter commands and/or data specific to the patient to . processor 60 and/or an internal power supply, such as a battery, if apparatus 50 is to be operated.
* 10 regardless of an external power supply.
According to another alternative method, it has been hypothesized that tremor resulting from elevated muscle activation (eg, GG muscle) can be measured directly during wakefulness in order to identify the characteristic modulation (eg, 30-40 Hz or some other frequency variation or variations) associated with OSA to determine if the patient has OSA. In this method, possible changes in the airway muscle movement nerve (ie, possible electrical changes generated by muscle cells) are detected with an electromyogram (EMG) sensitivity technique in order to detect the characteristic modulation associated with OSA. FIGURE 4 shows an exemplary device 70 that can be used to detect OSA in a patient based on data that is collected from the patient while he or she is awake “based on the detection of possible muscle changes in the throat. In the exemplary embodiment, apparatus 70 comprises an EMG sensor 72 that comprises two or more surface electrodes that are structured to be selectively placed at locations in the neck and/or head (e.g., right-left sides of the neck well below the jaw and /or front-rear, lower neck, right-left sides of the jaw, under-jaw trots [PAIRA OZAOZATA by AUBSQI2A, paddles, 2500 — the common return electrode on the face or neck, etc.). The EMG sensor 72 detects EMG signals indicative of activation of the hypoglossal nerve (CN XII) of the genioglossus muscle (GG) or other nerves or muscles related to the airway and the head.
As an alternative to surface electrodes as described now, although the more invasive EMG sensor 72 may comprise a needle electrode adapted to be inserted into muscle tissue to measure intramuscular EMG. As seen in FIGURE 4, apparatus 70 also includes a main NS holder 10 74 which houses a processor 76, a memory 78 and a screen 80.
In operation, the EMG signals collected by the EMG sensor 72 are provided to the processor 76 which (using one or more software program routines) examines the signals in order to identify in the EMG signals the characteristic modulation (e.g., 30- 40 Hz or some other frequency variation or variations) associated with OSA, if present, to determine if The patient has OSA (the EMG ginal will be a collection of possible muscle signals from all nearby muscle activity, so that The frequency signal characteristic will be a repetitive modulation of at least a part of the signal energy). Processor 76 is connected to screen 80, which provides a visual indication of the result of processing. Processor 76 is also connected to memory 78 so that memory 78 can store the EMG signals prior to processing by processor 76, as well as any results or results of processing performed by processor 76 on the EMG signals. In the exemplary embodiment, apparatus 70 is implemented as a lightweight device that can be held or used by the patient during the testing procedure without causing undue discomfort to the patient. Although not shown in FIGURE 4, it will be appreciated that apparatus 70 (and, in particular, q Elia SIN ON282 AA UOSAICA. pis SAR E. DO————=—=————=——=< e—- -= oo 23/51 | bracket 74) may include additional components, such as a user interface to allow a user of device 70 to input patient-specific commands and/or data to processor 76 and/or an internal power supply, as a battery, if the apparatus 70 is to be operated independently of an external power supply.
According to another alternative method, Oo tremor. resulting from elevated muscle activation (eg .GG muscle) is measured. .directly during wakefulness using f- * 10 actimetry (also known as actigraphy) to identify the characteristic modulation (eg, 30-40 Hz or some other variation or frequency variations) associated with OSA to determine if the patient has OSA.
More specifically, in this method, actimetry is used to monitor neck movement to identify characteristic modulation. FIGURE 5 shows an exemplary device 90 that can be used to detect OSA in a patient based on data that is collected from the patient while he or she is awake that employs actimetry.
In the exemplary embodiment, apparatus 90 comprises one or more actimetry sensors 92 that are structured to be selectively placed at locations in the neck and/or head to detect tremor movement of the respiratory muscles. In the exemplary embodiment, each of the actimetry sensors 92 comprises a piezoelectric accelerometer or '. another based on electronics or optics coupled to a filter that filters out unwanted signals, such as those due to external vibrations. Actimetry sensor(s) 92 generate(s) electrical signals indicative of movement of muscles in the neck, tongue, and/or throat (eg, the genioglossus muscle (GE)). As seen in FIGURE 5, apparatus 90 also includes a main support 94 which houses a processor 96, | a memory 98 and a screen 100.
; | Petition 870210042874, of 05/11/2021, p. 35/200
In operation, the electrical signals generated by the actimetry sensor(s) 92 are provided to the processor 96 which (using one or more software program routines) examines the signals in order to identify the characteristic modulation in the signals (by (eg, 30-40 Hz or some other frequency range or ranges) associated with OSA, if present, to determine if the patient has OSA.
O . processor 96 is connected to screen 100, which provides a visual indication of the result of processing.
The processor | « 10 96 is also connected to memory 98 so that memory 98 can store the electrical signals generated by the actimetry sensor(s) 92 prior to processing by the processor 96, as well as any results or results of processing performed by the processor 96 on the electrical signals generated by actimetry sensor(s) 92. In the exemplary embodiment, apparatus 90 is implemented as a lightweight device that can be held or used by the patient during the test procedure without causing undue discomfort to the patient. .
Although not shown in FIGURE 5, it will be appreciated that apparatus 90 (and, in particular, bracket 94) may include additional components such as a user interface to allow a user of apparatus 90 to enter patient-specific commands and/or data. to the 'processor 96 and/or an internal power supply, such as a battery, if the apparatus 90 is to be operated:' independently of an external power supply, FIGURE 6 shows an exemplary apparatus 70' which can be used in detection of OSA in a patient based on data that is collected from the patient while he or she is awake that is based on both detection of possible throat muscle changes and actimetry. The 70' device is similar to the 70 device shown in FIGURE 4 and thus similar components are marked with ' | Petition 870210042874-tie-t7t05/2021, p. 36/200- —— - |
25/51 -: | similar reference numbers. In this realization, the EMG signals collected by the EMG sensor 72 are examined as described elsewhere here, in order to identify the | characteristic modulation (eg 30-40 Hz or some | 5 other frequency variation or variations) associated with the OSA, | if present, and the electrical signals generated by the actimetry sensor(s) 92 are analyzed and employed to remove 8 artifacts related to unwanted motion from the EMG signals. ' . 10 Yet, according to another alternative method, tremor resulting from increased muscle activation (eg, GG muscle) is measured directly during wakefulness using ultrasonic dimension measurements in order to identify the characteristic modulation (eg, 30-40 Hz or some other frequency variation or variations) associated with OSA to determine if the patient has OSA. Muscle tissue thickness measurements could be indicative of apnea similar to the way in which heart wall thickness is used in cardiology and/or muscle dimensions can be dynamically measured to detect the individual's characteristic movement (eg, movement 30-40 Hz) of the genioglossus and/or other airway obstruction muscles. The movement of the size of the tongue or throat or other airway structures can be measured in the same way to detect the modulation caused by increased compensatory muscle activation of the upper airways.
FIGURE 7 shows an exemplary device 110 that can be used to detect OSA in a patient based on data that is collected from the patient while he or she is awake that employs ultrasound measurements. In the exemplary embodiment, apparatus 110 comprises an ultrasonic transducer probe 112, which, as is well known in the art, is structured to emit ultrasonic probes in the SANA of 05/11/2021, p. 37/20 and A i 26/51 o i which will pass through the body and detect return echoes that are caused when the ultrasonic probes hit objects inside the body. These return echoes are used to identify the size, shape and distance of the probe from these objects. Generally, a gel is applied to lubricate the area of skin that exists above the internal structures that must be scanned to allow the 112 transducer probe: ultrasonic probe to slide around easily and increase the conduction of sound in the body.
- 10 In the exemplary embodiment, the ultrasonic transducer probe 112 will generate electrical signals indicative of the dimensions and movement of the muscles of the neck, tongue and/or throat (for example, the genioglossus (GG) muscle) . As seen in FIGURE 7, apparatus 110 also includes main support 114 housing a processor 116, memory 118, and | a screen 120.
In operation, the electrical signals generated by the ultrasonic transducer probe 112 based on the returned sound waves (echoes) are provided to the processor 116 which (using one or more software program routines) examines the signals in order to identify the characteristic modulation in the signals (eg, 30-40 Hz or some Other frequency range or ranges) associated with OSA, if present, to determine if the patient has OSA. The NS 25 processor 116 is connected to the screen 120, which provides a | ' visual indication of the result of the processing. The processor 116 is also connected to the memory 118 so that the memory 118 can store the electrical signals generated by the ultrasonic transducer probe 112 prior to processing by the processor 116, as well as any results or results of processing performed by the processor 116 on the electrical signals. generated by the ultrasonic transducer probe 112. In the exemplary embodiment, the apparatus 110 is implemented as a | Petition 870210042874, of 05/11/2021, p. 38/200 lightweight device that can be held or used by the patient during the testing procedure without causing undue discomfort to the patient.
Although not shown in FIGURE 7, it will be appreciated that apparatus 110 (and in particular holder 114) may include additional components, such as a user interface, to allow a user of apparatus 110 to enter commands and/or data. : patient-specific to the processor 116 and/or an internal power supply, such as a battery, if the . * 10 device 110 must be operated independently of an external power supply.
Apparatus 110 can also be used to make ultrasonic velocity measurements in order to detect the characteristic airway modulation (eg, 30-40 Hz or some other frequency variation or variations) associated with OSA.
The velocity of the surface or internal aspects of the tongue would have an oscillation characteristic of the tremor movement of the individual described here.
Tongue or throat movement or other airway structures can be measured using ultrasound to detect modulation caused by increased compensatory muscle activation of the upper airway.
In particular, the ultrasonic transducer probe 112 can be used to emit ultrasonic pulses and collect resulting reflections, with Doppler-based motion measurements being used to detect the characteristic movement (eg, movement | 30-40 Hz) of muscle genioglossus and/or other airway obstruction muscles in order to diagnose OSA.
Yet, according to another alternative method, The tremor resulting from increased muscle activation (eg, GG muscle) is measured during wakefulness using sound generation and detection in order to identify the characteristic modulation (eg, 30-40 Hz Or some other [FOR SIGNATURES ATTACH LUUSIDOA, pg, MAM oo |
SNS as/01 frequency variation or variations) associated with OSA to determine if the patient has OSA. More specifically, in this method, a sound generator with a particular tone or more complex waveform is used to emit a sound in the patient's throat. The sounds that are emitted by the patient in response to the original sound are detected and the changes between the emitted sound and the detected sound are analyzed in order to. to determine whether the characteristic modulation associated with OSA - is present. NS.
. 10 FIGURE 8 shows an exemplary apparatus 130 that can be used to detect OSA in a patient based on data that is collected from the patient while he or she is awake that employs sound generation and detection, as described now. In the exemplary embodiment, apparatus 130 includes a sound module 132 that includes a sound emitter 134 and a sound detector 136. Sound emitter 134 is a device that is structured to emit sonic (audible), subsonic, or ultrasonic sounds ( having a particular tone or more complex waveform), and may comprise, for example, and among others, a small calibrated audio speaker and microphone, or a setup similar to a professional ambient audio analyzer (which emits a tone or tones, static or time-varying, to detect sound absorption or resonant properties of a chamber or environment). Sound detector 136 is a device which is structured to detect sounds that are generated by the patient in response to Sounds generated by sound emitter 134, and may comprise, for example, and among others, a microphone. In addition, sound module 132 is structured to be selectively positioned near the outside of the mouth or in the mouth or throat, or selectively inserted below the patient's throat and pharyngeal region. When positioned as described, THE [COUNTRY TAIONSSALA de. UMSAROI, pis AMU — E— ss n o the C 29/51 i sound detector 136 is configured to detect a resonance of one or more airway chambers. The presentation of several selected audio broadcasts can also be used to “probe” different parts of the respiratory system as well. As an example, the resonant frequency of the oral cavity is different in the larger, narrower trachea or in the bronchial passages even more. narrow. When selecting a sound emitted close to at least ' one resonant frequency of the trachea, the system will be more ” . 10 sensitive to movement or changes in the size of the trachea, and less sensitive to those of the bronchial passages or oral cavity. As seen in FIGURE 8, apparatus 130 also includes a main support 138 which houses a processor 140, a memory 142 and a screen 144.
The patient's oral or tracheal cavities are expected to be modulated by the characteristic tremor of the airway muscles described elsewhere here. As a result, the resonant frequency amplitude of the sounds that are emitted by the patient in response to the original sound will be modulated by small changes in airway dimensions caused by tremors. Thus, in operation, the sound emitter 134 is caused to emit Sounds, as described elsewhere herein, and the sound detector 136 detects the sounds that are generated by the patient in response to this. The sound signals detected by sound detector 136 are provided to processor 140, which examines the signals in order to identify, from the signals (and based on the &ons originally emitted), the characteristic modulation (eg, 30-40 Hz or some other frequency variation or variations) associated with OSA, if present. Processor 140 is connected to screen 144, which provides a visual indication of the result of the processing. Processor 140 is also connected to memory 142 so that memory 142 can store the beeps detected by sound detector 136 prior to processing by processor 140, as well as any results or results of processing performed by processor 140. In the exemplary embodiment , Apparatus 130 is implemented as a lightweight device that can be held or used by the patient during the testing procedure without causing undue discomfort to the patient. Although not internet. shown in FIGURE 8, it will be appreciated that The apparatus 130 (and in particular -the holder 138) may include additional components, such as a user interface, to allow a user of the apparatus 130 to enter specific commands and/or data. the patient to the processor 140 and/or an internal power supply, such as a battery, if the apparatus 130 is to be operated independently of an external power supply.
According to another alternative method, tremor resulting from increased muscle activation (eg, GG muscle) is measured during wakefulness by detecting airway sounds in order to identify the characteristic modulation (eg, 30-40 Hz or some other frequency variation or variations) associated with OSA to determine if the patient has OSA. More specifically, the sound of air passing through the airways (during the patient's breathing) will be modulated by the characteristic muscle movements associated with OSA, described elsewhere here, because — as air passes through the airways during breathing, turbulence is altered by discrete changes in the size of the throat caused by the individual's movements. This method employs common signal processing methods to detect the characteristic modulation (eg, 30-40 Hz or some other frequency variation or variations) associated with OSA breath sounds. FIGURE 9 shows an exemplary apparatus 150 which | Petition 870210042874, of 05/11/2021, p. 42/21 =. =.
can be used in detecting OSA in a patient based on data that is collected from the patient while he or she is awake that employs airway sound detection as described now. In the exemplary embodiment, apparatus 150 includes a sound detector 152 which is structured to detect airway sounds that are generated by the patient while breathing and may comprise, for example, and a microphone. sound 152 is structured to be selectively positioned near the outside of the mouth or in the mouth or throat or selectively inserted below the throat and pharyngeal region of the patient. As seen in FIGURE 9, apparatus 150 also includes a main support 154 that it houses a processor 156, a memory 158 and a screen 160.
In operation, the sound detector 152 detects airway sounds that are generated by the patient while breathing. The sound signals detected by sound detector 152 are provided to processor 140, which (using one or more software program routines) examines the signals in order to identify characteristic modulation of the signals (e.g., 30-40 Hz or some other frequency variation or variations) associated with OSA, if present. Processor 156 is connected to screen 160, which provides a visual indication of the result of processing. Processor 156 is also connected to memory 158 so that memory 158 can store the beeps detected by sound detector 152 prior to processing by processor 156, as well as any results or results of processing performed by processor 156. exemplary, Apparatus 150 is implemented as a lightweight device that can be held or used by the patient during the testing procedure without causing undue discomfort to the patient. Although not shown in FIGURE 9, it will be appreciated that apparatus 150 | Petition 870210042874, of 05/11/2021, p. 43/200. n——————— —=.
(and, in particular, holder 154) may include additional components, such as a user interface, to allow a user of device 150 to input patient-specific commands and/or data to processor 156 and/or an internal power supply, as a battery, if the apparatus 150 is to be operated independently of an external power supply. . Still, according to another alternative method, The tremor resulting from increased muscle activation (eg - 10 GG muscle) is measured during wakefulness by detecting the tension caused by it, in order to identify the characteristic modulation (eg 30 -40 Hz or some other frequency variation or variations) associated with OSA to determine if the patient has OSA.
FIGURE 10 shows an exemplary apparatus 170 that can be used to implement such an OSA detection method.
Apparatus 170 includes a tension detector 172 which is structured to detect movement caused by the muscles of the neck, tongue and/or throat (eg, the genioglossus (GG) muscle) by detecting the tension caused by that movement.
In the exemplary embodiment, the tension detector 172 comprises a flexible substrate 174, made of, for example, and among others, a polymer material, steel or other metal, an elastic material, or fiber composite material, in which one or more strain gauges 176 are affixed.
Flexible substrate 174 is structured to be secured along its length or at its ends by an adhesive or mechanical support assembly relative to the skin or other structures of the head and/or neck or within the mouth.
Each strain gauge 176 can be, for example, a sheet strain gauge, although other types of strain gauges may also be used.
As is known in the art, a typical sheet strain gauge consists of a flexible insulating back that supports
| Petition 870210042874, of 05/11/2021, p. 44/200 2 Tax: —=——
33/51 O : a sheet metal pattern. As the object to which the strain gauge is attached is deformed, the sheet is deformed, causing its electrical resistance to change. This change in resistance, usually measured using a Wheatstone bridge, is related to voltage by the amount known as the meter factor. As seen in FIGURE 10, Apparatus 170 also includes a main support 178 that houses it. a processor 180, a memory 182 and a screen 184.
! " In operation, the electrical voltage signals generated ! - 10 by each strain gauge 176 in response to movements caused | by the muscles of the neck, tongue, and/or throat are provided to processor 180, which (using one or more software program routines ) examines the voltage signals in order to identify, from the signals, the characteristic modulation (eg, 30-40 Hz or some other frequency variation or variations) associated with the OSA, if present. Processor 180 is connected to screen 184 , which provides a visual indication of the result of processing. Processor 180 is also connected to memory 182, so that memory 182 can store the voltage signals before processing by |processor 180, as well as any results or results of processing performed. by the processor 180. In the exemplary embodiment, the apparatus 170 is implemented as a lightweight device that can be easily held or used by the patient during the testing procedure without. cause undue discomfort to the patient. Although not shown in FIGURE 10, it will be appreciated that Apparatus 170 (and in particular holder 178) may include additional components, such as a user interface, to enable | 30 a user of device 170 enters patient-specific commands and/or data to processor 180 and/or a | internal power supply, such as a battery, if apparatus 170 is to be operated independently of an external power supply.
Furthermore, in connection with apparatus 170 or the other embodiments described herein, various restraint apparatus, such as a chin rest among others, can be used to restrict movement of the patient's head and body to remove unwanted artifacts. Also, several different patient positions, such as Bench Press or | ' upright positions, can be beneficial in signaling h noise from measurements made in the. various embodiments described herein.
| - 10 Either to enhance the effect or decrease the effect being measured.
According to yet another alternative method, Tremor resulting from elevated muscle activation (eg, GG) is measured during wakefulness by detecting volumetric changes in the volume or displacement of a fluid from a pouch in order to identify the characteristic modulation ( for example, 30-40 Hz or some other frequency range or ranges) associated with OSA to determine if the patient has OSA. FIGURE 11 depicts an exemplary apparatus 190 that can be used to implement such an OSA detection method. In the illustrated embodiment, apparatus 190 includes a fluid (i.e., air or liquid) filled bag 192 that is fluidly coupled to a reservoir 194. A sensor 196 is operatively coupled to the bladder 192 and is configured to measure an amount of fluid that is displaced from the bladder 192 in the reservoir 194 as an S . - result of the forces acting on it. In this realization, a flow sensor between the bag and the reservoir or a pressure sensor in the reservoir can be used to monitor the variation in the volume of the bag, whose volume is being modulated by the movement of the neck and internal muscles. In an alternative embodiment, reservoir 194 is not present, and sensor 196 is configured to measure the volumetric changes in pocket 192 as a result of à 10042874 -det+/05/2021, paddles. AGRIBcO R p—- > —. —
35/51 " forces acting on it.
In this embodiment, sensor 196 may be a pressure sensor.
If the pouch 192 is relatively thin and conforms closely to the contour of the neck, just below the mandible, for example, and the outer surface away from the body is stiffer or thicker, then movement of the throat surface will translate to There is a small pressure fluctuation inside the bag, which can be sensed by the sensor. 196. As seen in FIGURE 11, Apparatus 190 also includes a main support 198 which houses a processor 200, a memory 202 and a screen 204. In operation, the pocket 192 (and reservoir 194, if present) is placed under the mandible, along/around the neck or in the patient's mouth (appropriate attachment means may be employed, such as one or more tapes). When bag 192 is so positioned, forces caused by movement of the neck, tongue and/or throat muscles will act on bag 192, and cause some of the fluid to be displaced in reservoir 194, if present, or cause the bag 192 to be displaced. internal volume of the bag change.
This will be sensed by sensor 196 and the electrical signals generated by sensor 196 are provided to processor 200, which (using one or more software program routines) examines the signals in order to identify characteristic modulation of the signals (e.g. , 30-40 Hz or some other frequency variation or variations) associated with OSA, if present.
Processor 200 is connected to screen 204, which provides a visual indication of the result of the processing.
Processor 200 is also connected to memory 202 so that memory 202 can store the sensor signals prior to processing by processor 200, as well as any results or results | of processing performed by processor 200. In the exemplary embodiment, apparatus 190 is implemented as a | [ PARFO STNOADNIDATA A A iSi2ND, post, 4th " o : | lightweight device that can be held or used by the | patient during the test procedure without causing | undue discomfort to the patient.
Although not shown in FIGURE 11, it will be appreciated that apparatus 190 (and in particular holder 198) may include additional components, such as a user interface, to allow a user of apparatus 190 to enter commands and/or data. patient specifics to the processor 200 and/or an internal power supply, such as a battery, if the device 190 is to be operated independently of an external power supply.
According to another alternative method, Oo tremor resulting from increased muscle activation (eg, GG muscle) is measured during wakefulness using acoustic pharyngometry in order to identify the characteristic modulation (eg, 30-40 Hz or some other variation or frequency variations) associated with OSA to determine if the patient has OSA.
As is known in the art, acoustic pharyngometry is a dynamic test that determines dimensions of the oral airway before the glottis while the patient is breathing.
In particular, acoustic pharyngometry uses an acoustic reflection technique to measure the cross-sectional area of at least a portion of the patient's upper airway * during inspiration. FIGURE 12 shows an exemplary apparatus 210 that can be used to implement this method of acoustic pharyngometry for detecting OSA.
Apparatus 210 includes a pharyngometer 212 comprising a sound source for generating sound pulses, two microphones for detecting sounds, a wavetube portion and a mouthpiece coupled to the wavetube portion.
Apparatus 210 also includes a main bracket 214 that houses a processor 216, a memory 218, and a screen 220. In operation, pharyngometer 212 causes | Petition 870210042874, of 05/11/2021, p. 48/200 : the | i 37/51" sound pulses are continuously propagated from the sound source along the wave tube portion and into the patient's airway through the mouthpiece.
As the incident sound wave travels along the patient's airway, a reflection wave is generated due to axial gradients in acoustic impedance within the airway.
Both incident and reflective Sound signals are recorded by microphones on the ; pharyngometer 212. These signals are output to the processor. 216 which uses these signals to determine . a cross-sectional area of the patient's airway along at least a portion of the length of the patient's airway using a known technique.
The processing of incident and reflected airway sound waves by the processor 216 provides an area-distance curve representing the lumen from which the patient's minimum cross-sectional area and upper airway volume can be derived.
For a more detailed discussion of an acoustic pharyngometer and its operation, see “Eccovision Acoustic Pharyngometry System Operator Manual”, published by E.
Benson Hood Laboratories, Inc., the contents of which are incorporated herein by reference.
An example of a pharyngometer suitable for use as the 212 pharyngometer is the device manufactured by Hood Industries under the trade name "Eccovision Acoustic Pharyngometry System". However, it should be understood that other pharyngometer devices, including a microphone pharyngometry, may be used in the present invention.
In accordance with a further aspect of the present embodiment, after processor 216 makes measurements of the dynamic state of the patient's upper airway, as described now, processor 216 further analyzes those measurements to determine whether the patient's airway dimensions. , at a point, set of points or all | Petition 870210042874, of 05/11/2021, p. 49/200 .
= : ee | , 38/51 - fa O RO me ma mar so mal” ns From along the length of the airways, are varying according to the characteristic modulation (eg 30-40 Hz or some other variation or Frequency variations) associated to OSA.
Processor 216 is connected to screen 220, which provides a visual indication of the result of processing.
Processor 216 is also connected to memory 218 so that memory 218 can store dimension measurements. prior to processing by processor 216, as well as any results or results of processing performed by processor 216. In the exemplary embodiment, apparatus 210 is implemented as a lightweight device that can be held or used by the patient during the test procedure without cause undue discomfort to the patient.
Although not shown in FIGURE 12, it will be appreciated that Apparatus 210 (and in particular holder 214) may include additional components such as a user interface to enable | a device user 210 enter commands and/or data | patient specifics to the processor 216 and/or an internal power supply, such as a battery, if apparatus 210 is to be operated independently of an external power supply.
In addition, the patient's upper airway measurements taken by the pharyngometer 212 in cooperation with the *processor 216 can be separately examined to detect airway dimension characteristics (not TOO based on the characteristic tremor described herein) that were found to be indicative of OSA, according to any of several methodologies known in the art.
Such a methodology is described in U.S. Patent No. 6,379,311 to Gaumond et al., assigned to the assignee of the present invention and entitled "Breathing Disorder | Prescreening Device and Method”, which is revealed here | incorporated by reference. | Petition 870210042874, of 05/11/2021, p. 50/200
39/51 | According to another alternative method, The tremor resulting from increased muscle activation (eg, GG muscle) modulates the impedance along the throat or jaw (at the characteristic frequency or frequencies) during wakefulness in OSA sufferers is detected/measured using the evoked potential/nerve conduction. Potential/evoked nerve conduction involves sensing electrodes. possible of nerve placed close to or on a 7' target nerve by a needle electrode, e-a second electrode or electrode . 10 of mechanical stimulation is applied to stimulate the target nerve or an ascending nerve (ie, another nerve site that innervates the target nerve being sensed). The reaction time, rate or amplitude of heating target nerve heating in response to the stimulus is measured in an evoked potential measurement, and the propagation time and/or intensity of the target nerve's reaction to the stimulus is measured in a nerve conduction measurement. In this realization, the evoked potential can be used to measure tremor. characteristic/movement of the GG muscle or other muscles in the patient's neck, tongue and/or throat when looking at 30-40 Hz (or other characteristic frequency) in the rate of heating of individual nerves or groups of nerves. Fatigue-related movement of the GG muscle or other* muscles of the patient's neck, tongue, and/or throat will evoke modulation at the measured rates. Nerve conduction can be used to demonstrate that the possible fatigue due to the OSA attack alters the reaction time or intensity of nerve pulses transmitted to or along the GG muscle or other muscles of the neck, tongue and/or throat of the patient and/or connected nerves.
FIGURE 13 shows an exemplary 222 device that can be used to detect OSA in a patient based on the data that is collected from the patient while he or she [ESA A —— E—— ——== —
40/51 "
is awake based on evoked nerve/potential conduction.
In the exemplary embodiment, apparatus 222 comprises one or more stimulus electrodes 223 and one or more sensitivity electrodes 224. Apparatus 222 also includes a main support 225 that houses a power source 226 that drives the one or more stimulus electrodes 223 , a processor 227, a memory 228 and a screen 229. . In operation, the one or more electrodes is made. .. of stimulus 223 stimulate the target nerve OR AN ascending » 10 nerve, and the target nerve reaction is measured by the one or more sensing electrodes 224. The electrical signals collected by the one or more sensing electrodes 224 are provided to the processor 227 , The processor 227 determines the reaction time, the rate or amplitude of heating heating of the target nerve in response to the stimulus in which case the evoked potential is employed, and the propagation time and/or intensity of the target nerve's reaction to the stimulus is measured in the case where nerve conduction is employed.
Processor 227 then analyzes these parameters (using one or more software program routines) in order to identify the characteristic modulation (eg, 30-40 Hz Or some other frequency variation or variations) associated with the OSA, if present to determine if the patient has OSA.
The programmed nd processor 227 is connected to screen 229, which provides a visual indication of the processing result. the S processor 227 is also connected to memory 228 so that memory 228 can store the electrical signals collected by one or more sensitivity electrodes 224 prior to processing by processor 227, as well as any results or results of processing performed by processor 227 in electrical signals.
Thus, several different devices and methods have been described here to detect OSA, by detecting tremor | Petition 870210042874, of 05/11/2021, p. 52/20 —=— =. if -
characteristic resulting from increased muscle activation (eg, GG muscle) that is associated with OSA.
Yet, in further embodiments, two or more of these methods and/or apparatus are used in combination in order to detect OSA with high accuracy.
FIGURE 14 depicts an exemplary apparatus 230 for detecting OSA that employs multiple methods and/or apparatus that detects the characteristic tremor herein. described.
Apparatus 230 includes a first sensing module based on characteristic tremor 232A and a | - 10 second sensitivity module based on characteristic 232B tremor.
The first sensitivity module based on characteristic tremor 232A may be any of the sensitivity modules described herein in connection with FIGURES 1 and 3 to 12 and thus may be flow measuring device 4 (FIGURE 2), oS electrodes 52 and 54 (FIGURE 3), EMG sensor 72 (FIGURE 4), actimetry sensor 92 (FIGURE 5), EMG sensor 72 and actimetry sensor 92 (FIGURE 6), ultrasound transducer probe 112 (FIGURE 7), module sound detector 132 (FIGURE 8), sound detector 152 (FIGURE 9), voltage detector 172 (FIGURE 10), a bag system including bag 192 and sensor 196 (FIGURE 11), pharyngometer 212 (FIGURE 12) , stimulus electrode(s) 223 and sensitivity electrode(s) 224 (FIGURE 13). The second sensitivity module S based on characteristic tremor 232B can be any of the sensitivity modules just described that i is different from the first sensitivity module based on characteristic tremor 232A.
Apparatus 230 also includes a main bracket 234 that houses a processor 236, a memory 238, and a screen 240. In operation, the first and second sensitivity modules based on characteristic tremor 232A, 232B will take measurements as described herein, and in conjunction with the 236 processor, will determine whether the characteristic jitter can | Petition 870210042874, of 05/11/2021, p. 53/200 = | be identified based on these measurements (as also described here). Processor 236 will then determine if the OSA is present based on this processing. In a non-limiting embodiment, processor 236 will determine that the OSA is present only if the characteristic tremor can | be identified on the basis of measurements made by the first and second sensitivity modules based on characteristic ã tremor 232A, 232B. In addition, although only two sensitivity modules based on characteristic tremor . 10 232 are shown in FIGURE 14, it will be understood that this must mean to be exemplary only and that more than two of these modules may be employed. In this case, Processor 236 can determine that OSA is present only if the characteristic jitter can be identified based on measurements made by all the sensitivity modules based on the characteristic jitter. Alternatively, processor 236 can determine that OSA is present if characteristic tremor can be identified based on measurements made by some predetermined percentage or fraction of the sensitivity modules based on characteristic tremor (e.g., at least 1/2 or 2/3 of the modules) .
In addition, rather than simply using frequency analysis to detect the characteristic tremor 1 resulting from elevated muscle activation (eg, GG) that is associated with OSA, as described herein, other types of 'waveform/signal analysis' they could also be used to detect the apnea signature, such as, among others, analysis of amplitude, area and/or temporal or sequential patterns.
In still further embodiments, one or more of the methods and/or apparatus for detecting OSA by detecting The characteristic tremor resulting from elevated muscle activation (eg muscle GG) that is associated with OSA is/are used | Petition 870210042874, of 05/11/2021, p. 54/200 in combination with an OSA detection method that is not based on characteristic tremor detection, in order to detect OSA with high accuracy. Several exemplary combinations are described below.
FIGURE 15 shows an exemplary apparatus 250 for detecting OSA that employs a combination as described now. Apparatus 250 includes a sensitivity module with . base on the characteristic tremor 232, as described elsewhere here. Apparatus 250 also employs an acoustic detection method » 10 of OSA, as described in U.S. Patent No. 7,559,903 to Moussavi et al. entitled "Breathing Sound Analysis For Detection of Sleep Apnea/Popnea Events", the disclosure of which is incorporated herein by reference. As described in more detail in U.S. Patent No. 7,559,903, the method described uses sounds transmitted through the walls of the lower neck (ie, suprasternal cut) while breathing while the subject is supine or sitting upright. and, in particular, processes breath-related sounds in the frequency range of 150 - 800 Hz. In connection thereto, apparatus 250 further includes a collector module 252. As seen in FIGURE 15, collector module 252 includes an airway microphone 254 to record airway sounds, 256 oximetry sensor to collect 'SaO data, conventional or other oximetry data (eg a structured known optics-based sensor 'to be placed on the patient's finger), and external microphone 258 to record ambient sounds. As described in the '903 patent, the 254 airway microphone may comprise a neck strap with a microphone mounted in a chamber placed over the suprasternal notch or, alternatively, a wireless microphone within the ear. The three sensors allow simultaneous data acquisition of the sound signals and the SaO data. The 250 handset also includes a | Petition 870210042874, of 05/11/2021, p. 55/200 main support 260 which houses a 262 processor, a 264 memory and a 266 screen.
As is also described in detail in the 1903 patent, The 262 processor will eliminate noise from recorded sound, separate snoring sounds, estimate acoustic flow, detect apnea and/or hypopnea episodes, and count the duration and frequency of apnea and/or hypopnea episodes. /or hypopnea. Most . specifically, the signal processing of beeps has three stages. First, an automatic algorithm finds « 10 artifacts (which normally look like pulses in the signal) and removes them from further analysis. Second, snoring sounds, if any, are identified and separated from breath sounds. Finally, the breath sounds. cleansed, signal entropy is calculated, the effect of heart sounds is removed, and apnea episodes are detected and identified using the Otsu thresholding method, described in detail in the '903 patent. In operation, the characteristic jitter based sensitivity module 232 will make measurements as described herein and, in conjunction with the processor 262, will determine whether the characteristic jitter can be identified based on these measurements (as also described herein). Processor 262 will then determine whether the OSA is present based on this processing and the processing done by processor 262 on the signals obtained by collection module 252: as described now. In a non-limiting embodiment, the processor 262 will determine that OSA is present only if the characteristic jitter can be identified based on measurements made by the sensitivity module based on the characteristic jitter 232 and if the processor 262 also detects OSA based on the obtained signals. by collection module 252. Also, although only a sensitivity module based on characteristic tremor 232 is | Petition 870210042874, dated H/05/2021, p. 56/200 shown in FIGURE 15, it will be understood that this should be exemplary only and two or more of these modules may be employed. In that case, processor 262 can determine that OSA is present only if characteristic jitter can be identified based on measurements made by all sensitivity modules based on characteristic jitter, and if processor 262 also detects OSA based on the signals. obtained by collection module 252. Alternatively, processor 262 can determine which OSA is present if the .
» 10 characteristic jitter can be identified based on measurements made by some predetermined percentage or fraction of the sensitivity modules based on the characteristic jitter (eg, at least 1/2 or 2/3 of the modules) and whether the 262 processor also detects OSA based on the signals obtained by the 252 collection module.
The measurements of the method of the 1903 patent and those based on the sensitivity modulus(s) based on characteristic tremor 232 are believed to be independent to a significant degree, since the measured physical signals each have its origin in two different mechanisms (ie muscle movement detection vs. airway breath sounds most likely caused by airway shape or resistance), plus the frequency variation ' of the two detected signals are significantly different.
FIGURE 16 shows an exemplary apparatus 270 for detecting OSA which employs a combination of an OSA detection method which is based on the characteristic tremor detection described herein and an OSA detection method which is not based on the tremor detection characteristic described here. Apparatus 270 includes a sensitivity module based on characteristic tremor 232, as described elsewhere herein. Apparatus 270 also employs an OSA detection method based on oral cavity measurements, | Petition 870210042874. of 05/11/2021, p. 57/2200 — as described in U.S. Patent Nos. 6,048,322 and 6,213,959 to Kushida entitled "Morphometric Measuring Tool" and "Morphometric Modeling Systen and Method", respectively, the disclosures of which are incorporated herein by reference. thereafter, apparatus 270 further includes an oral cavity measuring tool 272, as described in the '322 and '959 patents. Apparatus 270 also includes a main bracket 274 which houses a processor 276, a memory 278, and a screen 280.
. 10 The oral cavity measurement tool 272 is structured to measure a first value indicative of a distance between the highest point of the patient's palate and the — patient's tongue, a second value indicative of a ; overlapping of the central, right, upper and lower incisors, a third value indicating a distance between b a molar on the right side of the jaw and a molar on the left side of the jaw, and a fourth value indicating a distance between a molar on the right side of the mandible and one: molar on the left side of the mandible. The processor 276 is structured to receive these anatomical values (eg, by manual insertion or electronic transfer (wired or wireless) from the oral cavity measurement tool 272 if it is configured to do so) and determine . a morphometric model value for the patient based on anatomical values that are indicative of a united probability that the patient suffers from OSA. In one embodiment, the morphometric model value is also based on the patient's neck circumference at the level of the cricothyroid membrane and the patient's BMI. The particulars of the morphometric model are described in detail in the '322 and '959 patents.
In operation, the characteristic tremor based sensitivity module 232 will take measurements as described herein and, in conjunction with the processor 276, will determine | Petition 870210042874, of 05/11/2021, p. 58/200
47/51 i whether the characteristic tremor can be identified based on these measurements (as "also described herein). The 276 processor will then determine if OSA is present based on this processing and the morphometric model value, as described now. In In a non-limiting embodiment, the processor 262 will determine that OSA is present only if the characteristic tremor can be identified based on the measurements made by the sensitivity module based on the characteristic tremor 232 and if the morphometric model value - * 10 indicates a probability for OSA. Furthermore, although only one sensing module based on characteristic tremor 232 is shown in FIGURE 16, it will be understood that this should be exemplary only and that two or more of these modules may be employed. can determine that OSA is present only if the characteristic tremor can be identified based on measurements made by all sensor modules. reliability based on characteristic tremor and if the morphometric model value indicates a probability for OSA, Alternatively, the 276 processor can determine that OSA is | present if the characteristic tremor can be identified based on measurements made by some predetermined percentage or fraction of the sensitivity modules based on the ' characteristic tremor (eg at least 1/2 or 2/3 of the modules) and if the value of morphometric model indicate an O probability for OSA.
In addition, findings from recent research studies provide preliminary evidence that specific concentrations of substances in blood, saliva, and/or urine indicate the likelihood of OSA in certain populations. For example, an amino acid cysteine can be a biomarker for the development of OSA in obese and non-obese patients. The results showed that the plasma levels |[ PP FORO ATA of tIOGIAAA, pis, ANA — ——— and 2
48/51 | of cysteine were higher in patients with OSA compared to control subjects.
A subgroup of presumed patients (BMI < 25) with OSA also had higher cysteine levels than controls.
Researchers concluded that cysteine is a potential biomarker for OSA and that obesity does not influence its function as a biomarker.
See, for example, Chest 2011; 139(2):246-252. - Finally, it should be understood that methods of "- OSA detection that are not based on tremor detection | "* 10 characteristic different from those specifically described here | can also be employed.
Still, in additional implementations, the use of charging/respiratory flow control to precipitate ; or enhancing/enhancing tremors (or dampening tremors) may be used for measurement.
FIGURE 17 depicts an exemplary apparatus 290 for detecting OSA that employs such loading/respiratory flow control.
Apparatus 290 includes a sensing module based on characteristic a-shake 232 as described elsewhere herein.
Apparatus 290 also includes a charge/control device | flow 292 which is structured to be placed over the ; nasal openings and/or mouth of the patient, and which provides a predetermined amount of airflow resistance or 'pressure level above/below atmospheric pressure for . 25 change the patient's breath trend loading and/or pressure.
Resistance and pressure parameters can vary differently in the inspiratory and expiratory phases of breath, or any time throughout the respiratory cycle.
This change in flow and/or ambient pressure challenges or aids in the patient's breathing, increasing or decreasing the persistent effects of OSA being measured by the sensitivity module based on the characteristic tremor 232 described elsewhere here, Miscellaneous | Petition 870210042874, of 05/11/2021, p. 60/200 —
| embodiments of a suitable exemplary 292l charge/flow control device are described in U.S. Provisional Patent Application No. 61/361,037, assigned to the assignee of the present invention and entitled "System and Method for Performing Respiratory Diagnostics", the disclosure of which is incorporated herein by reference. The 290 apparatus | also includes a 294 main bracket that houses a | a processor 296, a memory 298, and a screen 300. In the illustrated embodiment, the load/control device of . .« 10 stream 292 is provided as an integral part of apparatus 290 coupled to main bracket 294 and controlled by processor 296. However, it should be understood that load/control device 292 could also be | . a separate device, separate from the main bracket 294 and simply used in conjunction with the characteristic tremor based sensitivity module 232.
In operation, the charge/flow control device 292 is first placed over the patient's nasal and/or mouth openings and is made to provide a predetermined amount of air flow resistance or pressure level above/below the atmospheric pressure to change the loading and/or pressure trend of the patient's breath in order to improve/intensify . tremors. Then, the characteristic tremor based sensitivity module 232 is used to make measurements as described herein. Processor 296 then determines whether the characteristic tremor associated with the OSA can be identified based on these measurements (as also described herein). The charge/flow control device 292 can be used with any of the particular embodiments described herein.
In addition to hyper-excited muscle activity, it is also possible to look for a Mild response to respiratory challenges or other physiological functional challenges (by [ PPA ATA IANANOA, PIS ERICO — —- = eg speech, tone formation, swallowing, whistling, movements tongue etc.) in cases where the muscle is fatigued enough to not be up to the challenge. A range of Sensitivity and Detection methods described here can be used to monitor the variations caused by this repressed physical response.
Standard questionnaires or assessment tools. Physiological (eg Berlin Questionnaire for OSA, : Epworth Sleepiness Scale questionnaire for -» 10 daytime sleepiness, Mallampati throat opening rating, BANG, BANG-STOP, etc.) can be administered together or be integrated into the functionality of the embodiments described herein, in order to . increase the sensitivity and/or specificity of the OSA assessment. The parameters of these standard assessment tools can be entered through the user interface as described herein, and the data can be mathematically combined with measured sensory data from the realizations described herein to produce an enhanced assessment that predicts OSA.
The signals and detection methods described here can also be applied during sleep as part of a PSG diagnostic session, which could possibly provide . additional information to be used in assessing the patient's diagnosis/phenotype. In addition, the 'sensors/modules of sensitivity and diagnostic methods could be incorporated into other devices such as a cannula or mask that are primarily used for therapy.
In the claims, any reference signs enclosed in parentheses should not be construed as limiting the claim. The word “comprising” or “including” does not exclude the presence of elements or steps | Petition 870210042874, of 05/11/2021, p. 62/20 : = n—
' = “51/51 r—ne. .. the à" is L . o and other than those listed in the claim. In one | device claim that enumerates several means, several of these means can be performed by one and the same piece of hardware. The word “a” or “an” preceding an element does not exclude the presence of a plurality of these elements. In any device claim that enumerates several means, several such means may be . performed by one and the same piece of hardware. The mere fact that certain elements are mentioned in '10 mutually different dependent claims does not indicate i | that these elements cannot be used in combination. | Although the invention has been described in detail by way of illustration, based on what is currently considered to be the most practical and preferred embodiments, it is to be understood that these details are for this purpose only and that the invention is not limited to the embodiments. disclosed, but rather are intended to cover modifications and equivalent provisions which fall within the spirit and scope of the appended claims. For example, it is to be understood that the present invention contemplates that, as far as possible, one or more aspects of any embodiment may be combined with one or more aspects of any other embodiment. |
To | Petition 870210042874; of TI/05/2021, p: 63/00 —— ——— = — —

权利要求:
Claims (44)
[1]
1. APPARATUS FOR USE IN THE DIAGNOSIS OF THE PRESENCE OF OBSTRUCTIVE SLEEP APNEA (OSA) IN A PATIENT, characterized in that it comprises: a structured sensitivity module to measure a parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles while the patient is awake, the parameter not being airflow through the patient's airway, the sensitivity module generates one - 10 or more electrical signals based on the parameter measured while the patient is awake; and a processor operatively coupled to the sensitivity module, the processor being structured to . receive the one or more electrical signals, perform an analysis of one or more electrical signals, and based on the analysis that 'determines whether the tremor has a frequency in at least one predetermined frequency range that is indicative of OSA, at least one change frequency is associated with and characteristic of increased compensatory muscle activation of the patient's upper airways during wakefulness.
[2]
2. APPARATUS according to claim 1, characterized in that the at least one predetermined frequency variation is below 100 Hz.
[3]
3. APPARATUS according to claim 2, characterized in that the at least one predetermined frequency range is from 30 to 40 Hz.
[4]
4. APPARATUS according to claim 1 | characterized by further comprising a CA source | 30 (58), wherein the sensing module comprises a source electrode (52) and one or more collection electrodes (54) structured to be selectively positioned on separate surfaces of the patient's neck or head, in
SS NE 2/11 that an alternating current generated from the AC source will flow from the source electrode, where the parameter comprises a modulated electrical signal collected by one or more collection electrodes, the modulated electrical being modulated by the tremor.
[5]
APPARATUS, according to claim 1, characterized in that the sensing module comprises an EMG sensor (72), in which the parameter comprises possible muscle changes in the muscles of the patient's neck, tongue and/or throat.
[6]
. 4310. APPARATUS according to claim 5, characterized in that it additionally comprises a sensor of | actimetry (92) structured to be selectively | positioned on the patient's neck or head, where oO . The processor receives actimetry signals from the actimetry sensor and uses the actimetry signals to remove “motion artifacts from one or more electrical signals when performing an analysis of one or more electrical signals.
[7]
7. APPARATUS according to claim 1, characterized in that the sensing module comprises an actimetry sensor (92) structured to be selectively positioned on the neck OR head of the patient, wherein the parameter comprises movement caused by the tremor.
[8]
8. APPARATUS according to claim 1, characterized in that the sensitivity module comprises an ultrasonic transducer probe (112) structured to emit ultrasonic probes that will pass through the patient's body and detect return echoes that are generated responsive to the emitted ultrasonic probes, wherein the parameter comprises the echoes of return.
[9]
APPARATUS according to claim 1, characterized in that the sensing module comprises a sound module (132) which includes a sound emitter (134) and a sound detector (136), wherein the sound module is structured to be selectively positioned near the outside of the patient's mouth or in the patient's mouth or throat or selectively inserted below the patient's throat and in the patient's pharyngeal region, where the sounder is structured to emit first sounds and the structured sound detector for detecting second sounds that are generated in response to the first sounds, and in which the parameter comprises . the second sounds. >=
[10]
10. APPARATUS according to claim 1, . 10 characterized in that the sensing module comprises a sound detector (152) that is structured to detect airway sounds that are generated by the patient while breathing, and wherein the parameter comprises airway sounds.
[11]
11. APPARATUS, according to claim 1, "characterized in that the sensitivity module comprises a - tension detector (172) that is structured to be selectively positioned on the patient's neck and to detect tension resulting from movement caused by the muscles of the the patient's neck, tongue and/or throat, and where the parameter comprises tension.
[12]
Apparatus according to claim 11, characterized in that the voltage detector comprises a . flexible substrate (174) having one or more strain gauges (176) affixed thereto.
'
[13]
APPARATUS according to claim 1, characterized in that the module comprises a fluid filled bag (192) structured to be positioned on the head, neck or mouth of the patient and a sensor (196) ooperatively coupled to the bag, in where The sensor is configured to measure an amount of fluid displaced from the bag or a volumetric change from the bag as a result of forces acting on the bag, and where The parameter comprises | Petition 870210042874; of 05/11/2021, p. 66/200 — - =— = = the amount of fluid displaced from the bag, the volumetric change in the bag, or the pressure change within the bag.
[14]
14. APPARATUS according to claim 1, characterized in that the sensing module comprises a pharyngometer (212) structured to propagate sound pulses in the patient's airways and detect reflection waves generated in response to the sound pulses, wherein The parameter comprises reflection waves, where one or more signals .« 10 are based on sound pulses and reflection waves, and where the analysis performed by the processor comprises the generation of a plurality of airway size measurements : patient based on one or more signs. :
[15]
15. APPARATUS according to claim 1, characterized in that the sensitivity module comprises one or more stimulus electrodes (223) and one or more sensitivity electrodes (224), one or more stimulus electrodes being structured to stimulate a target nerve or a nerve that innervates the target nerve, the nerve being associated with the muscles of the patient's neck, tongue and/or throat, where The parameter comprises one or more target nerve signals collected by the one or more sensing electrodes, o one or more target nerve signals being modulated by the tremor. .
[16]
16. APPARATUS according to claim 1, characterized in that it additionally comprises a S device. in . load/flow control (292) that is structured to be placed over the patient's nasal openings and/or mouth and to provide a predetermined amount of air flow resistance or pressure level above or below atmospheric pressure to change the pressure load or drift of the patient's breath before the sensitivity module measures the parameter.
[17]
17. APPARATUS FOR USE IN THE DIAGNOSIS OF THE PRESENCE OF [| PERO SIRIMDAZATA Aa ta SADAA, pis, AAA — - o — h
OBSTRUCTIVE SLEEP APNEA (OSA) IN A PATIENT, characterized by comprising: a first structured sensitivity module to measure a first parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles while the patient is awake, the first sensitivity module generating one or more first electrical signals. based on the first parameter measured while the patient. is awake; . .
. 10 a second sensitivity module structured to measure a second parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles while the patient is awake, the second parameter being Is different from the first parameter, the second sensitivity module generating one or more second electrical signals, based on the second parameter measured while the patient is awake; and a processor operatively coupled to the first sensitivity module and the second sensitivity module, the processor being structured to: (i) receive the one or more first electrical signals, perform a first analysis of one or more first electrical signals, and based in the first analysis, make a first determination of whether "the tremor has a frequency in at least one predetermined frequency range that is indicative of OSA, at least one predetermined frequency range being associated and characteristic of a high compensatory muscle activation of the pathways upper airways of the patient during wakefulness, (ii) receive one or more second electrical signals, perform a second analysis of one or more second electrical signals, and based on the second analysis, perform a second determination of whether the tremor has a frequency in at least one frequency variation | PPAFRRSIMRAOMZATA AaLUOMOAGA pis, MAIN — ———— —>is 4)
predetermined to be indicative of OSA, and (iii) determining whether the patient has OSA based on at least the first determination and the second determination.
[18]
18. APPARATUS according to claim 17, characterized in that the processor is structured to determine that the patient has OSA only if both the first determination and the second determination. determine that the tremor has a frequency of at least i a predetermined frequency range. . . 10
[19]
19. APPARATUS according to claim 18, characterized in that the at least one predetermined frequency variation is below 100 Hz.
[20]
20. APPARATUS according to claim 19. characterized in that the at least one predetermined frequency range is from 30-40 Hz.
.
[21]
21. APPARATUS according to claim 17, characterized in that it further comprises a third sensing module structured to measure a third parameter indicative of a tremor in the muscles of the patient's neck, tongue and/or throat while the patient is awake, the third parameter being different from the first parameter and the second parameter, the third sensitivity module generating one or more third electrical signals based on the third measured parameter, where the processor is structured to receive the one or more third electrical signals, perform a third analysis of one or more third electrical signals, and based on the third analysis, perform a third determination of whether the tremor has a frequency in the at least a predetermined frequency range that is indicative of OSA, and where the processor is structured to determine whether the patient has OSA based on at least the first determination, the second determination, and the third determination.
| Petition 870210042874, of 05/11/2021, p. 69/20 = m——. if. —.
Ú 7/11
[22]
22. APPARATUS according to claim 21, characterized in that the processor is structured to determine that the patient has OSA if at least two of the first determination, the second determination and the third determination determines that the tremor has a frequency in the hair. minus a predetermined frequency range. .
[23]
23. APPARATUS according to claim 21, characterized in that the processor is structured for . 10 determines that The patient has OSA only if each of the first determination, the second determination, and the third determination determines that the tremor has a frequency in at least a predetermined frequency range.
[24]
APPARATUS according to claim 17: characterized in that it additionally comprises a device | charge/flow control (292) which is structured to be placed over the patient's nasal openings and/or mouth and to provide a predetermined amount of air flow resistance or pressure level above or below atmospheric pressure to change the charge pressure Or deviation of the patient's breath before the first sensitivity module measures the first parameter and the second module. of sensitivity measure the second parameter.
[25]
25. METHOD OF DIAGNOSING THE PRESENCE OF OBSTRUCTIVE SLEEP APNEA (OSA) IN A PATIENT, characterized by comprising: measurement of a first parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles while the patient is awake ; determining, based on the first parameter, whether the tremor has a frequency in at least one predetermined frequency range that is indicative of OSA;
8/11 – assessment of whether the patient is likely to have OSA using a second assessment methodology, the second assessment methodology not being based on measuring any parameters indicative of a tremor in the patient's neck, tongue and/or throat muscles; and determination that the The patient has OSA only if at least the determination step determines that | . the tremor has a frequency in at least a range of | . Predetermined frequency. and the evaluation step determines . -s | .-. 10 that the patient is likely to have OSA.
[26]
26. METHOD according to claim 25, characterized in that the first parameter is not the airflow through the patient's airways.
[27]
. 27. METHOD according to claim 25, | 15 characterized in that the at least one predetermined + frequency range is below 100 Hz.
[28]
28. METHOD according to claim 27, characterized in that the at least one predetermined frequency range is from 30-40 Hz, " 20
[29]
29. METHOD, according to claim 25, characterized in that the second assessment methodology is based on measuring the sounds of the patient's airways.
|
[30]
30. METHOD, according to claim 25, : . characterized in that the second assessment methodology is based on measuring a plurality of dimensions of the patient's oral & cavity.
[31]
31. METHOD, according to claim 25, characterized in that the second assessment methodology is based on the measurement of a patient's biomarker indicative of OSA.
[32]
32. The METHOD of claim 25, further comprising the provision of a predetermined amount of air flow resistance [Ao 87021004287F4;de-H705/2021, p. H200——b
: 9/11 or pressure level above or below atmospheric pressure to the patient to change the patient's charge pressure or breath drift before the measurement step of the first parameter.
[33]
33. METHOD OF DIAGNOSING THE PRESENCE OF OBSTRUCTIVE SLEEP APNEA (OSA) IN A PATIENT, characterized by comprising: . measurement of a parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles - . 10 while the patient is awake, the parameter not being Airflow through the patient's airway; determining, on the basis of the parameter, whether the tremor has a frequency in at least one frequency range. predetermined to be indicative of OSA; and | 15 determination that the patient has OSA if the % determination step determines that the tremor has a frequency in at least a predetermined frequency range.
[34]
34. METHOD according to claim 33, characterized in that the at least one predetermined frequency variation is below 100 Hz.
[35]
35. METHOD according to claim 34, characterized in that the at least one predetermined frequency range is from 30-40 Hz.
[36]
36. METHOD according to claim 33: "characterized by further comprising the provision of a predetermined amount of air flow resistance or pressure level above or below atmospheric pressure for the patient to change the load pressure or deviation the patient's breath before the parameter measurement step.
[37]
37. METHOD OF DIAGNOSING THE PRESENCE OF OBSTRUCTIVE SLEEP APNEA (OSA) IN A PATIENT, characterized by | Petition 870210042874, of 05/11/2021, p. T/200 q—=Is—
10/11 l comprising: providing a predetermined amount of airflow resistance or pressure level above or below atmospheric pressure for the patient to change the patient's loading pressure or breath deflection; after the provision step, measurement of a parameter indicative of a tremor in the muscles of the neck, tongue and/or . patient's throat while the patient is awake; determining, on the basis of the parameter, whether the .” tremor has a frequency in at least one predetermined frequency range that is indicative of OSA; and determining that the patient has OSA if the determining step determines that the tremor has a frequency in the at least one predetermined frequency range.
'
[38]
38. METHOD according to claim 37, characterized in that the at least one predetermined frequency variation is below 100 Hz.
[39]
39. METHOD according to claim 38, characterized in that the at least one predetermined frequency range is from 30 to 40 Hz.
[40]
40. METHOD OF DIAGNOSING THE PRESENCE OF OBSTRUCTIVE SLEEP APNEA (OSA) IN A PATIENT, characterized by . understand: measurement of a first parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles while the patient is awake; measuring a second parameter indicative of a tremor in the patient's neck, tongue and/or throat muscles while the patient is awake, the second parameter being different from the first parameter; making a first determination of whether the tremor has a frequency in at least a range of : | Petition 870210042874, of 05/11/2021, p. 73/200 predetermined frequency that is indicative of OSA based on the first parameter; making a second determination of whether o The tremor has a frequency in the at least one predetermined frequency range that is indicative of OSA, based on the second parameter; and determining whether the patient has OSA based on . at least in the first determination and in the second - determination. O .
[41]
. 10 41. METHOD according to claim 40, characterized in that the determination of whether the patient has OSA comprises determination that the patient has OSA only if both the first determination and the . The second determination is to determine that the tremor has a frequency in the at least one frequency range. predetermined.
[42]
42. METHOD according to claim 40, . characterized in that at least one predetermined frequency range is below 100 Hz,
[43]
43. METHOD, according to claim 42, characterized in that at least one predetermined frequency variation is from 30-40 Hz.
[44]
44. The method of claim 40, further comprising providing a predetermined amount of air flow resistance or pressure level above or below atmospheric pressure for the patient to change the loading pressure or deviation of the the patient's breath before the steps of measuring the first parameter and measuring the second parameter.
| POA STEIOLAZATA, of III, by Jia is —tc——

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