WO2015178439A2 - Dispositif et méthode d'aide au diagnostic de l'apnée centrale/obstructive du sommeil, et support lisible par un ordinateur comportant un programme d'aide au diagnostic de l'apnée centrale/obstructive du sommeil - Google Patents

Dispositif et méthode d'aide au diagnostic de l'apnée centrale/obstructive du sommeil, et support lisible par un ordinateur comportant un programme d'aide au diagnostic de l'apnée centrale/obstructive du sommeil Download PDF

Info

Publication number
WO2015178439A2
WO2015178439A2 PCT/JP2015/064546 JP2015064546W WO2015178439A2 WO 2015178439 A2 WO2015178439 A2 WO 2015178439A2 JP 2015064546 W JP2015064546 W JP 2015064546W WO 2015178439 A2 WO2015178439 A2 WO 2015178439A2
Authority
WO
WIPO (PCT)
Prior art keywords
apnea
central
sleep
psd
diagnosis support
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/JP2015/064546
Other languages
English (en)
Japanese (ja)
Other versions
WO2015178439A3 (fr
Inventor
佐藤紳一
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Ainy Corp
Original Assignee
Ainy Corp
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Ainy Corp filed Critical Ainy Corp
Priority to JP2015561781A priority Critical patent/JPWO2015178439A1/ja
Publication of WO2015178439A2 publication Critical patent/WO2015178439A2/fr
Publication of WO2015178439A3 publication Critical patent/WO2015178439A3/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs

Definitions

  • the present invention relates to a sleep / apnea central / occlusion type diagnosis support technique for supporting a sleep / apnea syndrome (SAS) patient's central / occlusion diagnosis by a doctor or the like.
  • SAS sleep / apnea syndrome
  • Sleep apnea is classified into three types: central sleep apnea (CSA), obstructive sleep apnea (OSA) and a mixed type (MSA: mixed sleep apnea).
  • Central sleep apnea is an apnea disease caused by abnormal function of the respiratory center
  • obstructive sleep apnea is a disease caused by obstruction of the upper airway.
  • An overnight polysomnography (PSG) test device can diagnose SAS, including central (CSA) and obstructive (OSA) determinations.
  • a respiratory belt sensor (abdominal belt sensor or chest belt sensor) is attached to the body in order to detect a respiratory state (apnea state) during sleep.
  • a respiratory state a respiratory state
  • the polarity inversion of the detection values of both the chest and abdominal belt sensors reflecting that the expansion and contraction of the chest and abdomen are in opposite phases during obstructive apnea is determined to be obstructive.
  • wearing of an abdominal belt or a chest belt may become a big burden on a test subject, and may reduce the quality of sleep.
  • the measurement signal waveform obtained by the subject's breathing has an extremely large amount of information.
  • the recorded waveform needs to be enlarged and observed for the determination of centrality (CSA) and obstructive apnea (OSA), and it takes a lot of time for doctors and technicians to diagnose CSA and OSA. It takes time and effort.
  • CSA centrality
  • OSA obstructive apnea
  • the object of the present invention is to provide quantitative analysis data using a respiratory sensor system that does not wear a breathing belt sensor to a subject during a sleep apnea test, thereby providing sleep apnea syndrome ( (SAS) It is to provide a central / occlusion type diagnosis technique of sleep apnea that supports a central / occlusion type diagnosis of a patient.
  • SAS sleep apnea syndrome
  • the present inventor has found the following characteristic facts in a raw waveform analysis of a biological signal obtained by a piezoelectric sensor.
  • the centralized apnea (CSA) and obstructive apnea (OSA) differ greatly in the PSD total value (integrated value) in the respiratory motion frequency region in the FFT analysis (the PSD total value of OSA is that of CSA). More markedly).
  • the respiratory motion frequency region can be set to 0.2 to 0.6 Hz, for example. In addition, when the respiratory motion frequency is less than 0.1 Hz, it is determined that there is apnea.
  • B In central sleep apnea (CSA) and obstructive sleep apnea (OSA), in the power spectral density (PSD) graph when FFT analysis of both is performed, from the frequency of heartbeat (for example, 1 Hz)
  • PSD power spectral density
  • C When there is arrhythmia, the cardiac cycle fluctuation becomes large, and even if it is central apnea (CSA), the PSD pattern becomes obstructive apnea (OSA) type.
  • a raw waveform data storage unit for storing raw waveform data including a subject's respiratory motion and heart sounds;
  • An apnea period detection unit that extracts a respiratory motion frequency component of the raw waveform from the raw waveform data stored in the raw waveform data storage unit and detects an apnea period;
  • An FFT processing unit that performs fast Fourier transform (FFT) processing on the data relating to the apnea period of the raw waveform data to generate a power spectral density (PSD) graph in the apnea period;
  • a PSD total value calculation unit for calculating a PSD total value in a predetermined frequency region;
  • a PSD pattern matching judgment unit for judging whether or not the generated PSD pattern matches a central apnea PSD pattern; and,
  • a display unit for displaying the raw waveform, at least a respiratory motion frequency component of the raw waveform, and the
  • a central / occlusion type diagnosis support apparatus comprising: Note that “directly placed in close contact with the subject's body” means “the sensor is placed in direct contact with the subject's skin” and “indirectly in close contact with the subject's body” "Disposed as” means that "the sensor is disposed so as to come into contact with the subject's body through sheets, pajamas, nightclothes, etc.”.
  • the sleep / apnea central / occlusion type diagnosis support apparatus is a central / occlusion type diagnosis support apparatus having a piezoelectric element as a sensing element.
  • the sleep / apnea central / occlusion type diagnosis support apparatus according to (1),
  • the raw waveform data is a sleep / apnea central / occlusion type diagnosis support apparatus further including a respiratory sound frequency component of the subject.
  • a sleep / apnea central / occlusion type diagnosis support apparatus further comprising:
  • the sleep / apnea central / occlusion type diagnosis support apparatus From the raw waveform data of the apnea period or the filtered heart sound frequency component data, the time (heart cycle) between the peaks of successive heart sounds is obtained, and one heart cycle (one sound minus one sound interval or 2 Sound-2 sound intervals) and the average of the difference between the next cardiac cycle and calculating the cardiac cycle fluctuation value,
  • a sleep / apnea central / occlusion type diagnosis support apparatus further comprising:
  • the sleep / apnea central / occlusion type diagnosis support apparatus has an analysis part,
  • the analysis unit By calculating whether the PSD total value in the predetermined frequency region is greater than or equal to a first predetermined value or less than a second predetermined value and displaying the information on the display unit, obstructive sleep apnea (OSA) or sleep Assists in the diagnosis of temporal central apnea (CSA), Central / occlusion type diagnosis support device for sleep apnea.
  • OSA obstructive sleep apnea
  • CSA temporal central apnea
  • the sleep / apnea central / occlusion type diagnosis support apparatus When the PSD total value in the predetermined frequency region is a predetermined value or less, The analysis unit If the PSD pattern is a clear CSA type, CSA is determined and output. If the PSD pattern is not a clear CSA type, a cardiac cycle fluctuation value is further calculated, and information on whether the CSA is indeterminate or mixed apnea (MSA) is displayed on the display unit depending on whether it is greater than or equal to a predetermined value. To help determine if it is obstructive apnea (OSA), central apnea (CSA), or indeterminate (or MSA), Central / occlusion type diagnosis support device for sleep apnea.
  • OSA obstructive apnea
  • CSA central apnea
  • MSA obstructive apnea
  • a raw waveform data storage step for storing raw waveform data including a subject's breathing motion and heart sound;
  • An apnea period detection step for extracting a respiratory motion frequency component of the raw waveform from the raw waveform data stored in the raw waveform data storage step and detecting an apnea period;
  • FFT processing step of performing a fast Fourier transform process on the data related to the apnea period of the raw waveform data to generate a PSD in the predetermined frequency region, PSD sum value calculation step for calculating a power spectrum density (PSD) sum value in a predetermined frequency region;
  • a PSD pattern matching determination step of determining whether or not the generated PSD pattern matches a central apnea PSD pattern; and, Displaying the raw waveform, at least the respiratory motion frequency component of the raw waveform and the PSD;
  • a sleep / apnea central / occlusion type diagnosis support method comprising:
  • the heart rate respiration sensor unit is a central / occlusion type diagnosis support method having a piezoelectric element as a sensing element.
  • the raw waveform data is a sleep / apnea central / occlusion type diagnosis support method further including a respiratory sound frequency component of the subject.
  • a sleep / apnea central / occlusion type diagnosis support method further comprising:
  • the sleep / apnea central / occlusion type diagnosis support method From the raw waveform data of the apnea period or the filtered heart sound frequency component data, the time (heart cycle) between the peaks of successive heart sounds is obtained, and one heart cycle (one sound minus one sound interval or 2 Sound-cycle interval) and the average of the difference between the next cardiac cycle and the cardiac cycle fluctuation average calculation step to calculate the cardiac cycle fluctuation value,
  • a sleep / apnea central / occlusion type diagnosis support method further comprising:
  • the sound output unit has a sound quality adjustment function (the sound quality can be adjusted in the sound output step), and can output a heart sound / breathing sound (including snoring) and / or a sound accompanying body movement.
  • a piezoelectric sensor can be used as a heartbeat respiration sensor in order to detect heart sounds, respiratory motion, etc., and other sensors (for example, a sensor using a microphone) can also be used.
  • the heart rate respiration sensor can reinforce the central / occlusion type apnea discrimination by PSG, or the heart rate respiration sensor alone constitutes a simple type SAS monitoring device.
  • the apnea period can be determined for a period of 10 seconds or more according to the American Sleep Society (AASM) standard.
  • AASM American Sleep Society
  • the respiratory amplitude is close to zero in the signal display of the respiratory motion waveform (respiratory motion frequency component) of the normal amplitude (for example, 1/5, 1/6 of the normal respiratory motion waveform, 1/7, 1/8, 1/9, or 1/10 or less)
  • the signal is continuous for 10 seconds or more.
  • the PSD total value calculation unit calculates the power spectral density (PSD) total value as A1-A2 Hz (A1: 0.1-0.3, A2 : 0.4-0.8).
  • This frequency range is preferably 0.1-0.8 Hz, 0.1-0.7 Hz, 0.1-0.6 Hz, 0.1-0.5 Hz, 0.1-0.4 Hz,. 2-0.4Hz, 0.2-0.7Hz, 0.2-0.8Hz, 0.3-0.8Hz, 0.3-0.7Hz, 0.3-0.6Hz, 0.3- 0.5 Hz, or 0.3-0.4 Hz, particularly preferably 0.2-0.5 Hz, or 0.2-0.6 Hz.
  • the PSD pattern match determination unit in the PSD pattern match determination step, normally determines whether or not the pattern matches the central apnea PSD pattern by B1-B2 Hz of the generated PSD pattern.
  • the range may be (B1: 0.5-1.0, B2: 10-60) Hz.
  • B1 is 0.5, 0.8, 1.0
  • B2 is 10, 20, 30, 40, 50, 60.
  • the first to sixth harmonics appearing in the PSD pattern are used as objects to be matched with the CSA PSD pattern.
  • the CSA-type PSD pattern has a single peak at a height where the PSD increases about 100 times from the bottom of the peak in the PSD graph, and its harmonics are about the same up to about 10 to 40 Hz. The one that appears continuously while maintaining the peak height.
  • G In the present invention, whether CSA is undecidable or mixed apnea (MSA) is determined based on whether the cardiac cycle fluctuation value is greater than or equal to a predetermined value C1. This determination can be made based on whether the cardiac cycle fluctuation value is greater than or less than a predetermined value C1 (C1: 0.1, 0.2, 0.3, 0.4, or 0.5 seconds).
  • the present invention supports the determination of central apnea (CSA) and obstructive apnea (OSA) during each apnea period. For example, a doctor and a sleep medical certified laboratory technician comprehensively analyze these individual determinations. Thereby, doctors or the like can determine whether the patient's individual sleep apnea syndrome (SAS) is central or obstructive.
  • SAS sleep apnea syndrome
  • the breathing belt sensor is not attached to the subject during the examination, the subject is not physically burdened. Therefore, it is possible to maintain a quality equivalent to that of sleep in an individual home without disturbing sleep, and support a more accurate central / obstructive diagnosis of a sleep apnea syndrome (SAS) patient.
  • SAS sleep apnea syndrome
  • FIG. 1 is a block diagram showing a diagnosis support apparatus of the present invention.
  • FIG. 2 is an explanatory view showing a usage state of the piezoelectric sensor constituting the diagnosis support apparatus of the present invention.
  • FIG. 3 is a flowchart showing the diagnosis support method of the present invention.
  • FIG. 4 is a diagram showing a raw waveform acquired from the piezoelectric sensor constituting the diagnosis support apparatus of the present invention.
  • FIG. 5 is a diagram showing a waveform obtained by extracting a respiratory frequency component from the raw waveform of FIG.
  • FIG. 6 is a diagram showing a power spectrum density (PSD) obtained by identifying an apnea period from the waveform of FIG. 5 and obtaining from the waveform information of the apnea period.
  • PSD power spectrum density
  • FIG. 6 (A) is a diagram showing a central sleep apnea PSD.
  • FIG. 6 (B) is a diagram showing an obstructive sleep apnea PSD.
  • FIG. 7 is a flowchart showing a first example of diagnosis support.
  • FIG. 8 is a flowchart showing a second example of diagnosis support.
  • FIG. 9 is a flowchart showing a third example of diagnosis support.
  • FIG. 10 is a flowchart showing a fourth example of diagnosis support.
  • FIG. 11 is a flowchart showing a fifth example of diagnosis support.
  • FIG. 1 is an explanatory diagram showing a configuration of a sleep / apnea central / occlusion type diagnosis support apparatus (hereinafter also simply referred to as “diagnosis support apparatus”) according to the present invention.
  • the diagnosis support apparatus 1 includes a piezoelectric sensor unit 10, a raw waveform data storage unit 11, an apnea period detection unit 12, an FFT processing unit 13, a PSD total value calculation unit 14, a PSD pattern match determination unit 15, a cardiac cycle.
  • a variation average calculation unit 16 a display unit 17, a sound output unit 18, and an analysis unit 19 are provided.
  • each component is shown as a functional block, and hardware such as a CPU, storage (ROM, RAM, Hard Disk, etc.), communication circuit, display circuit, measurement board, bus, etc. is not described.
  • the blocks (“ ⁇ units”) that perform the functions of the present invention are realized by the programs stored in the hardware and storage.
  • the piezoelectric sensor unit 10 is disposed, for example, under a sheet (between the body of the subject M and the bed).
  • the piezoelectric sensor unit 10 can detect the respiratory movement and heart sound of the subject M, and send the detection result to the main body 100 of the diagnosis support apparatus 1 as raw waveform data (electrical signal).
  • the diagnosis support apparatus 1 includes a piezoelectric sensor unit 10 and a main body 100.
  • the raw waveform data storage unit 11 can receive raw waveform data from the piezoelectric sensor unit 10 via the amplifier A and store it.
  • the raw waveform data includes the respiratory sound frequency component of the subject M.
  • the apnea period detection unit 12 extracts a respiratory motion frequency component from the raw waveform data stored in the raw waveform data storage unit 11, and the amplitude fluctuation value is equal to or less than a predetermined value, which is 10 seconds or more in the present embodiment.
  • the period is detected as an apnea period.
  • the FFT processing unit 13 performs a fast Fourier transform process on the data related to the apnea period of the raw waveform data to generate PSD (power spectral density) in the apnea period.
  • PSD power spectral density
  • a raw waveform, a respiratory motion frequency component of the raw waveform, and a PSD graph are displayed on the display 172 of the display unit 17.
  • the PSD total value calculation unit 14 calculates a PSD total value (integral value) in a predetermined frequency region (0.2-0.6 Hz in the present embodiment). This calculation result is displayed numerically or graphically on the display 172 of the display unit 17 together with the PSD graph. When the total PSD value is equal to or greater than a predetermined value, it is suggested to a doctor or the like that the PSD pattern is a clear OSA type.
  • the PSD pattern match determination unit 15 determines whether or not the generated PSD pattern matches the central apnea PSD pattern when the total PSD value in the predetermined frequency region is equal to or less than the predetermined value.
  • the PSD pattern match determination unit 15 determines whether or not the PSD pattern is a clear CSA type, and whether or not the PSD pattern is a CSA type (whether “matches” or “mismatch” with the CSA type) It is displayed on the display 172 of the display unit 17. With reference to this display, doctors and the like can diagnose that sleep apnea is central (CSA) when the PSD pattern “matches” with the CSA type.
  • the cardiac cycle variation average calculation unit 16 obtains a time (cardiac cycle) between peaks of consecutive heart sounds from raw waveform data of an apnea period or filtered heart sound frequency component data. Then, the average of the difference between one heart cycle (one sound—one sound interval or two sounds—two sound intervals) and the next heart cycle is calculated to obtain the average value of heart cycle fluctuation.
  • the cardiac cycle variation average value and / or the comparison result (whether the cardiac cycle variation value is greater than or equal to the predetermined value) compared with the predetermined value is displayed on the display 172 of the display unit 17.
  • MSA mixed sleep apnea
  • the display unit 17 includes a display circuit 171 and a display 172.
  • the display circuit 171 displays the raw waveform, the respiratory motion frequency component, and the PSD graph on the display 172.
  • a doctor or the like can make an accurate diagnosis with reference to the displayed raw waveform, respiratory motion frequency component, and PSD graph.
  • the sound output unit 18 can output at least a respiratory sound component included in the raw waveform data.
  • the sound output unit 18 includes a sound circuit 181 and a speaker 182.
  • the sound circuit 181 can output from the speaker 182 heart sounds, breathing sounds (including snoring), and / or sounds accompanying body movements.
  • a signal related to a heart sound, a breathing sound, and a sound accompanying body motion can be output as an electric signal from the sound signal output terminal.
  • the analysis unit 19 can calculate whether the PSD sum value during the apnea period is greater than or equal to the first predetermined value or less than the second predetermined value. Then, by displaying the information on the display unit, diagnosis of obstructive apnea (OSA) or central apnea (CSA) is supported.
  • OSA obstructive apnea
  • CSA central apnea
  • FIG. 3 shows an embodiment of the sleep / apnea central / occlusion type diagnosis support method of the present invention.
  • Sensing step (S102) Raw waveform data is detected as an electrical signal from a piezoelectric sensor arranged in close contact with the body of the subject directly or indirectly.
  • Raw waveform data storage step (S104) Raw waveform data including breathing motion and heart sound of the subject is stored.
  • the raw waveform data further includes a respiratory sound frequency component of the subject. Whether the raw waveform data includes the respiratory sound frequency component of the subject depends on the characteristics of the sensor. The sensor used in this embodiment can extract a respiratory sound frequency component.
  • OSA obstructive apnea
  • CSA central apnea
  • FIG. 4A shows raw waveform data including respiratory motion and heart sounds of a patient with central apnea
  • FIG. 4B shows raw waveform data including respiratory motion and heart sounds of a patient with obstructive apnea.
  • the apnea period is indicated by a period P_CSA
  • the apnea period is indicated by a period P_OSA.
  • FIG. 5A shows a waveform obtained by subjecting the raw waveform data of FIG. 4A to low-pass filter processing (respiration motion frequency component extraction processing), and FIG. 5B shows the raw waveform data of FIG. The waveform which performed the low-pass filter process is shown.
  • the period P_CSA shows a waveform obtained by subjecting the raw waveform data of FIG. 4A to high-pass filter processing
  • FIG. 5D shows a waveform obtained by subjecting the raw waveform data of FIG. 4B to high-pass filter processing. Show. Breathing sounds, snoring, body movements, etc. are highlighted.
  • 5A and 5C the apnea period is indicated by a period P_CSA
  • FIGS. 5B and 5D the apnea period is indicated by a period P_OSA.
  • FIG. 6A is a diagram showing a PSD graph created by subjecting the raw waveform data of the central apnea patient of FIG. 4A to FFT processing
  • FIG. 6B is the obstructive property of FIG. 4B. It is a figure which shows the PSD graph produced by performing the FFT process to the raw waveform data of an apnea patient.
  • the area of the PSD combined value for the patient with central apnea is much smaller than the area of the PSD combined value for the patient with obstructive apnea. (See symbol a in FIGS. 6A and 6B).
  • a characteristic pattern appears in the PSD related to the patient with central apnea, but a characteristic pattern appears in the PSD related to the patient with obstructive apnea. Is not shown (see symbol b in FIGS. 6A and 6B).
  • FIG. 7 is a flowchart illustrating a first example of diagnosis support.
  • the analysis step 120A obtains the calculation result of the PSD total value (0.2 to 0.6 Hz) in the PSD total value calculation step S108 (step A1), and when the calculation result is larger than the predetermined value S (step A1).
  • “YES” in step A2) is determined as obstructive sleep apnea (OSA) (step A3), and when the calculation result is equal to or less than a predetermined value S (“NO” in step A2), central apnea ( CSA) (step A4).
  • the predetermined value S can be appropriately determined according to environmental conditions, physical / physiological conditions of the subject, and the like.
  • the predetermined value S can be appropriately determined according to environmental conditions, physical / physiological conditions of the subject, and the like.
  • FIG. 8 is a flowchart illustrating a second example of diagnosis support.
  • the analysis step 120B obtains the calculation result of the PSD total value (400 to 1,000 Hz) in the PSD total value calculation step S108 (step B1), and when the calculation result is larger than the predetermined value S (step B2). "YES") is determined as obstructive sleep apnea (OSA) (step B3), and when the calculation result is equal to or less than a predetermined value S ("NO" in step B2), central apnea (CSA) (Step B4).
  • the predetermined value S can be appropriately determined according to environmental conditions, physical / physiological conditions of the subject, and the like.
  • FIG. 9 is a flowchart illustrating a third example of diagnosis support.
  • the analysis step 120C obtains the calculation result of the PSD total value in the PSD total value calculation step S108 (step C1), and when the calculation result is larger than the predetermined value S (in FIG. 9, when it is larger than six digits: "YES” in step C2) is determined as obstructive sleep apnea (OSA) (step C5).
  • OSA obstructive sleep apnea
  • step C3 when the PSD pattern is a clear CSA type (“YES” in step C3), it is determined that the patient has central apnea (CSA) (step C6).
  • the predetermined value S and the predetermined value T can be appropriately determined according to environmental conditions, physical / physiological conditions of the subject, and the like.
  • FIG. 10 is a flowchart illustrating a fourth example of diagnosis support.
  • the analysis step 120D acquires the calculation result of the PSD total value in the PSD total value calculation step S108 (step D1), and when the calculation result is larger than the first predetermined value S1 (“YES” in step D2). Is determined to be obstructive sleep apnea (OSA) (step D4).
  • OSA sleep apnea
  • step D3 when the calculation result of the PSD total value is smaller than the second predetermined value S2 (“YES” in step D3), it is determined that the central sleep apnea (CSA) (step D6), and the PSD total value
  • the calculation result is equal to or greater than the second predetermined value S2 (“NO” in step D3), it is determined that the device is “Unknown” (CSA / OSA cannot be determined or mixed apnea (MSA)) (step D5).
  • the predetermined values S1 and S2 can be appropriately determined according to environmental conditions, physical and physiological conditions of the subject, and the like.
  • FIG. 11 is a flowchart illustrating a fifth example of diagnosis support.
  • the analysis step 120E obtains the calculation result of the PSD total value in the PSD total value calculation step S108 (step E1), and when the calculation result is larger than the first predetermined value S1 (“YES” in step E2). Is determined to be obstructive sleep apnea (OSA) (step E6).
  • OSA sleep apnea
  • step E3 when the calculation result of the PSD combined value is equal to or greater than the second predetermined value S2 (“NO” in step E3), it is determined that the device is “Unknown” (CSA / OSA cannot be determined or mixed apnea (MSA)). E8).
  • step E3 when the calculation result of the PSD total value is smaller than the second predetermined value S2 (“YES” in step E3), it is determined whether or not the PSD pattern is a clear CSA type (step E4).
  • step E4 when the PSD pattern is a clear CSA type (“YES” in step E4), it is determined as central apnea (CSA) (step E7).
  • step E4 when the PSD pattern is not a clear CSA type (“NO” in step E4), a cardiac cycle variation value (BBIV) is further calculated (step E5), and BBIV is a predetermined value T (for example, 0.2). ) (“YES” in step E5) is determined to be central apnea (CSA) (step E7), and when BBIV is equal to or smaller than a predetermined value T (“NO” in step E5), Unknown (CSA) / OSA cannot be determined or mixed apnea (MSA)) (step E8).
  • the predetermined values S1, S2 and the predetermined value T can be appropriately determined according to environmental conditions, physical / physiological conditions of the subject, and the like.
  • BBIV means an average value of (n ⁇ 1) heartbeat interval differences, and is specifically obtained by the following calculation formula.
  • ABS means an absolute value.
  • k is a natural number representing the number of heartbeats, and Ik means the kth heartbeat interval (time difference between the kth heartbeat and the k + 1th heartbeat: 2 ⁇ k ⁇ n).
  • the sleep / apnea central / occlusion type diagnosis support program for executing the methods shown in FIGS. 7 to 11 can be recorded on a computer-readable recording medium.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Pulmonology (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Physiology (AREA)
  • Physics & Mathematics (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

　L'invention concerne une technique d'aide au diagnostic de l'apnée centrale/obstructive du sommeil, la technique permettant de diagnostiquer avec fiabilité l'apnée centrale/obstructive du sommeil chez un patient présentant le syndrome d'apnées du sommeil (SAS). Le dispositif selon l'invention comporte : une unité de stockage des données de formes d'ondes brutes (11) qui stocke des données de formes d'ondes brutes comprenant les mouvements respiratoires et les battements cardiaques chez un sujet; une unité de détection des phases d'apnée (12) qui extrait, à partir des données de formes d'ondes brutes stockées, une composante de fréquence des mouvements respiratoires de la forme d'onde brute, et détecte une phase d'apnée; une unité de traitement FFT (13) qui exécute une transformée de Fourier rapide sur des données comprises dans les données de formes d'ondes brutes relatives à la phase d'apnée et génère une densité spectrale de puissance (PSD) pour la phase d'apnée; une unité de calcul de valeur globale PSD (14) qui calcule une valeur globale PSD pour un domaine de fréquence prescrite; une unité de concordance de motifs PSD (15) qui évalue si le motif de la PSD générée correspond au motif de la PSD pour l'apnée centrale; et une unité d'affichage (17) qui affiche la forme d'onde brute, la composante de fréquence des mouvements respiratoires de la forme d'onde brute et la PSD.
PCT/JP2015/064546 2014-05-20 2015-05-20 Dispositif et méthode d'aide au diagnostic de l'apnée centrale/obstructive du sommeil, et support lisible par un ordinateur comportant un programme d'aide au diagnostic de l'apnée centrale/obstructive du sommeil Ceased WO2015178439A2 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP2015561781A JPWO2015178439A1 (ja) 2014-05-20 2015-05-20 睡眠時無呼吸の中枢型／閉塞型診断支援装置および診断支援方法、ならびに睡眠時無呼吸の中枢型／閉塞型診断支援プログラムを記録したコンピュータ読み取り可能な記録媒体

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
JP2014-103868 2014-05-20
JP2014103868 2014-05-20
JP2014-108628 2014-05-27
JP2014108628 2014-05-27

Publications (2)

Publication Number Publication Date
WO2015178439A2 true WO2015178439A2 (fr) 2015-11-26
WO2015178439A3 WO2015178439A3 (fr) 2016-01-14

Family

ID=54554924

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2015/064546 Ceased WO2015178439A2 (fr) 2014-05-20 2015-05-20 Dispositif et méthode d'aide au diagnostic de l'apnée centrale/obstructive du sommeil, et support lisible par un ordinateur comportant un programme d'aide au diagnostic de l'apnée centrale/obstructive du sommeil

Country Status (2)

Country Link
JP (1) JPWO2015178439A1 (fr)
WO (1) WO2015178439A2 (fr)

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2017179694A1 (fr) * 2016-04-15 2017-10-19 オムロン株式会社 Dispositif, système et programme d'analyse d'informations biologiques, et procédé d'analyse d'informations biologiques
JP2019180625A (ja) * 2018-04-05 2019-10-24 ダイキン工業株式会社 無呼吸判定装置
JP2020075136A (ja) * 2018-11-09 2020-05-21 ヘルスセンシング株式会社 生体振動信号検出装置
CN111820871A (zh) * 2019-04-17 2020-10-27 联发科技股份有限公司 生理状态监测装置及相关方法
CN116761544A (zh) * 2021-10-15 2023-09-15 科尔赛医疗有限责任公司 通过心电图、呼吸声学和胸部加速度进行智能呼吸监测的方法和装置

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5335654A (en) * 1992-05-07 1994-08-09 New York University Method and apparatus for continuous adjustment of positive airway pressure for treating obstructive sleep apnea
WO2003061471A1 (fr) * 2002-01-22 2003-07-31 Medcare Flaga Hf. Analyse de l'apnee du sommeil
US7942824B1 (en) * 2005-11-04 2011-05-17 Cleveland Medical Devices Inc. Integrated sleep diagnostic and therapeutic system and method
JP5533726B2 (ja) * 2011-02-18 2014-06-25 コニカミノルタ株式会社 睡眠時無呼吸判定装置
JP5694139B2 (ja) * 2011-12-28 2015-04-01 日本光電工業株式会社 睡眠中における無呼吸低呼吸状態の検出装置

Cited By (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2017179694A1 (fr) * 2016-04-15 2017-10-19 オムロン株式会社 Dispositif, système et programme d'analyse d'informations biologiques, et procédé d'analyse d'informations biologiques
JPWO2017179694A1 (ja) * 2016-04-15 2019-02-21 オムロン株式会社 生体情報分析装置、システム、プログラム、及び、生体情報分析方法
US11246501B2 (en) 2016-04-15 2022-02-15 Omron Corporation Biological information analysis device, system, and program
US11363961B2 (en) 2016-04-15 2022-06-21 Omron Corporation Biological information analysis device, system, and program
US11617516B2 (en) 2016-04-15 2023-04-04 Omron Corporation Biological information analysis device, biological information analysis system, program, and biological information analysis method
JP2019180625A (ja) * 2018-04-05 2019-10-24 ダイキン工業株式会社 無呼吸判定装置
JP7053994B2 (ja) 2018-04-05 2022-04-13 ダイキン工業株式会社 無呼吸判定装置
JP2020075136A (ja) * 2018-11-09 2020-05-21 ヘルスセンシング株式会社 生体振動信号検出装置
JP7177443B2 (ja) 2018-11-09 2022-11-24 ヘルスセンシング株式会社 生体振動信号検出装置
CN111820871A (zh) * 2019-04-17 2020-10-27 联发科技股份有限公司 生理状态监测装置及相关方法
CN111820871B (zh) * 2019-04-17 2023-11-03 联发科技股份有限公司 生理状态监测装置及相关方法
CN116761544A (zh) * 2021-10-15 2023-09-15 科尔赛医疗有限责任公司 通过心电图、呼吸声学和胸部加速度进行智能呼吸监测的方法和装置

Also Published As

Publication number Publication date
WO2015178439A3 (fr) 2016-01-14
JPWO2015178439A1 (ja) 2017-09-28

Similar Documents

Publication Publication Date Title
JP5303802B2 (ja) 心電図から導出された無呼吸／低呼吸指数
KR100805181B1 (ko) 특이값 분해법을 이용한 청진음의 분석
US20090247893A1 (en) Method and apparatus for measuring responsiveness of a subject
EP3329845A1 (fr) Dispositif de détermination de condition biologique et procédé de détermination de condition biologique
US20120302900A1 (en) Method and apparatus for processing a cyclic physiological signal
CN104545892B (zh) 一种基于心电身份识别的人体血压分析装置
AU2006206220A1 (en) Analysis of auscultatory sounds using voice recognition
WO2009150744A1 (fr) Dispositif de surveillance d’un état de sommeil, système de surveillance, et programme informatique
WO2015178439A2 (fr) Dispositif et méthode d'aide au diagnostic de l'apnée centrale/obstructive du sommeil, et support lisible par un ordinateur comportant un programme d'aide au diagnostic de l'apnée centrale/obstructive du sommeil
CN108175382B (zh) 基于cpc的非接触式睡眠评估方法及装置
Linschmann et al. Estimation of the respiratory rate from ballistocardiograms using the Hilbert transform
US9237862B2 (en) Diagnosis of asthma
AU2025202413A1 (en) Method and arrangement for respiratory measurement
CN101194261A (zh) 对于加强/重症监护病房患者的稳健性趋势分析的不同时标的形态描绘图
Yuasa et al. Wearable flexible device for respiratory phase measurement based on sound and chest movement
Heise et al. Unobtrusively detecting apnea and hypopnea events via a hydraulic bed sensor
JP7089650B2 (ja) 処理装置、システム、処理方法、およびプログラム
JP7122225B2 (ja) 処理装置、システム、処理方法、およびプログラム
Chyliński et al. The way of ECG signal obtaining from the respiratory wave by Savitzky-Golay filtration
Boiko et al. Accelerometer based system for unobtrusive sleep apnea detection
Mondal et al. Diagnosing of the lungs status using morphological anomalies of the signals in transformed domain
EP4487767A1 (fr) Procédé de génération de modèle de détermination d'anomalie, dispositif de détermination d'anomalie, procédé de détermination d'anomalie et modèle entraîné
Wu et al. A portable monitoring system with automatic event detection for sleep apnea level-IV evaluation
CN119866194A (zh) 信息处理系统、信息处理装置、控制方法和程序
CN117999029A (zh) 信息处理系统、检测装置、服务器装置、信息处理装置、控制方法及程序

Legal Events

Date Code Title Description
ENP Entry into the national phase in:

Ref document number: 2015561781

Country of ref document: JP

Kind code of ref document: A

121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 15796077

Country of ref document: EP

Kind code of ref document: A2

NENP Non-entry into the national phase in:

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 15796077

Country of ref document: EP

Kind code of ref document: A2