WO2019198742A1 - 嫌気性代謝閾値推定方法および装置 - Google Patents
嫌気性代謝閾値推定方法および装置 Download PDFInfo
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- WO2019198742A1 WO2019198742A1 PCT/JP2019/015577 JP2019015577W WO2019198742A1 WO 2019198742 A1 WO2019198742 A1 WO 2019198742A1 JP 2019015577 W JP2019015577 W JP 2019015577W WO 2019198742 A1 WO2019198742 A1 WO 2019198742A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
- A61B5/1118—Determining activity level
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/024—Detecting, measuring or recording pulse rate or heart rate
- A61B5/0245—Detecting, measuring or recording pulse rate or heart rate by using sensing means generating electric signals, i.e. ECG signals
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
- A61B5/352—Detecting R peaks, e.g. for synchronising diagnostic apparatus; Estimating R-R interval
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
- A61B5/355—Detecting T-waves
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/48—Other medical applications
- A61B5/4866—Evaluating metabolism
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- the present invention relates to an anaerobic metabolic threshold estimation method and apparatus, and more particularly to a technique for estimating an anaerobic metabolic threshold using an electrocardiographic waveform.
- An anaerobic metabolic threshold (AT) is known as a value for managing the exercise state of the subject.
- AT is an exercise intensity that is a turning point for switching from aerobic exercise to anaerobic exercise (see, for example, Non-Patent Document 1). It is said that the ability of anaerobic exercise improves when the subject trains with an exercise intensity higher than AT, and the ability of aerobic exercise improves when the subject trains with an exercise intensity lower than AT.
- AT has been measured by various methods, and when the lactic acid level is used as a reference, it is called a lactate threshold (LT). Further, AT based on the concentration of carbon dioxide gas in exhaled breath is called a ventilatory threshold (VT, hereinafter referred to as “VT”).
- VT ventilatory threshold
- the conventional LT measurement it is difficult to always measure LT because a small amount of blood is required.
- the conventional VT measurement requires a mask for collecting exhaled gas and a large-sized device, and it is difficult to easily measure VT. Therefore, the conventional technique cannot easily measure AT.
- the present invention has been made to solve the above-described problems, and an object thereof is to provide an anaerobic metabolic threshold estimation method and apparatus that can more easily estimate the subject's AT.
- an anaerobic metabolic threshold estimation method includes a first acquisition step of acquiring exercise intensity of exercise performed by a subject, and an electrocardiographic waveform of the subject performing exercise.
- the anaerobic metabolism threshold value estimation device acquires an exercise intensity acquisition unit for acquiring exercise intensity of exercise performed by a subject, and acquires an electrocardiogram waveform of the subject performing exercise, from the electrocardiogram waveform.
- a feature amount acquisition unit that acquires a predetermined feature amount; an estimation unit that estimates an anaerobic metabolic threshold of the subject based on the relationship between the predetermined feature amount and the acquired exercise intensity; The estimation unit estimates the anaerobic metabolic threshold of the subject based on an exercise intensity corresponding to an inflection point in a change in the predetermined feature amount with respect to the acquired exercise intensity.
- the inflection point in the change of the feature amount with respect to the exercise intensity is extracted from the relationship between the predetermined feature amount in the electrocardiogram waveform of the subject performing the exercise and the exercise intensity of the exercise performed by the subject. Then, AT is calculated based on the information of the bending point. As a result, the AT of the subject can be estimated more easily.
- FIG. 1 is a diagram for explaining the principle of the present invention.
- FIG. 2 is a diagram for explaining the principle of the AT estimation apparatus according to the embodiment of the present invention.
- FIG. 3 is a diagram for explaining the principle of the AT estimation apparatus according to the embodiment of the present invention.
- FIG. 4 is a block diagram showing a functional configuration of the AT estimation apparatus according to the embodiment of the present invention.
- FIG. 5 is a block diagram showing a hardware configuration of the AT estimation apparatus according to the embodiment of the present invention.
- FIG. 6 is a flowchart for explaining an AT estimation method according to the embodiment of the present invention.
- FIG. 1 is a diagram showing an electrocardiogram waveform (see Non-Patent Document 2 and Non-Patent Document 3).
- An AT estimation method extracts a predetermined feature amount serving as an index from a subject's electrocardiogram waveform, and manages an exercise state of the subject based on the feature amount. Is estimated.
- the height of the T wave is used as the feature quantity of the electrocardiogram waveform (electrocardiogram) (non- (See Patent Document 1 and Non-Patent Document 2).
- FIG. 2 is a diagram showing the relationship between the product of T wave height and heart rate (T wave height ⁇ heart rate) acquired by a gradual increase load test and exercise intensity.
- a value calculated by the carbonene method from the heart rate (Heart Rate Reserve: HRR) is used as the exercise intensity.
- HRR Heart Rate Reserve
- the exercise intensity is a scale representing the intensity of exercise based on the physical ability of the subject performing the exercise.
- FIG. 3 is a diagram in which AT calculated using T wave height ⁇ heart rate and AT measured by an exhalation gas measuring device are converted into heart rate (bpm) and compared.
- the vertical axis represents the AT estimated by the AT estimation method according to the present embodiment
- the horizontal axis represents the AT measured by the expiration gas measuring device.
- the AT estimation method can estimate the AT by finding a point where the value of T wave height ⁇ heart rate bends in the relationship between T wave height ⁇ heart rate and exercise intensity. I understand.
- FIG. 4 is a block diagram showing a functional configuration of the AT estimation apparatus 1 according to the first embodiment.
- the AT estimation device 1 includes a biological information acquisition unit 11, a storage unit 12, an estimation unit 13, and an output unit 14.
- the AT estimation device 1 obtains the relationship between the T wave height ⁇ heart rate and the exercise intensity when the subject performs an exercise in which the exercise intensity gradually increases as in the incremental load test.
- the AT estimation device 1 extracts a point where the value of T wave height ⁇ heart rate is bent, and calculates the exercise intensity at the bent point as AT.
- the inflection point is the vicinity where the value of exercise intensity is 80% in the relationship between T wave height ⁇ heart rate and exercise intensity, specifically, the range of 50 to 90% as shown in FIG. Exists within.
- the biometric information acquisition unit 11 includes a heart rate acquisition unit (exercise intensity acquisition unit) 111 and a T wave height acquisition unit (feature amount acquisition unit) 112.
- the biometric information acquisition unit 11 acquires information related to the heartbeat and electrocardiogram of the subject from a biosensor (not shown) having functions of an external heart rate meter and electrocardiograph attached to the subject.
- the biometric information acquisition unit 11 starts from the above-described experimental results and starts to exercise with gradually increasing exercise intensity in the subject, and then information about the heartbeat and electrocardiogram over a period of up to about 90%. Just get it.
- the heart rate acquisition unit 111 acquires a heart rate over a period in which the subject performs exercise such as a gradual increase load test in which the subject gradually increases the exercise intensity, from a biological sensor attached to the subject.
- the acquired heart rate data is stored in the storage unit 12.
- the T-wave height acquisition unit 112 acquires T-wave height data in the electrocardiogram waveform from the electrocardiogram waveform of the subject measured by the biosensor attached to the subject. Further, the T wave height acquisition unit 112 calculates a value (T wave height ⁇ heart rate) obtained by multiplying the acquired T wave height value of the subject by the heart rate acquired by the heart rate acquisition unit 111. The T wave height ⁇ heart rate data obtained by the T wave height acquisition unit 112 is stored in the storage unit 12.
- the T wave height acquisition unit 112 acquires the RS height indicating the height from the subject's electrocardiogram waveform to the peak value of the R wave and the peak value of the S wave, as shown in FIG.
- the T wave height can be normalized by the RS height.
- the T wave height acquisition unit 112 can obtain T wave height ⁇ heart rate based on the T wave height normalized and corrected by the RS height.
- the T wave height acquisition unit 112 may use the T wave height normalized by the R wave height or the S wave depth.
- the storage unit 12 stores the subject's heart rate and T wave height ⁇ heart rate data acquired by the biological information acquisition unit 11.
- the estimation unit 13 includes a bending point processing unit 131 and an AT calculation unit 132.
- the estimation unit 13 estimates the subject's AT based on the subject's heart rate and T wave height ⁇ heart rate data acquired by the biological information acquisition unit 11.
- the inflection point processing unit 131 reads the heart rate data of the subject acquired by the heart rate acquisition unit 111 and the T wave height ⁇ heart rate data obtained by the T wave height acquisition unit 112 from the storage unit 12, and The relationship between T wave height ⁇ heart rate and exercise intensity is obtained. At this time, the relationship as shown in FIG. 2 is obtained.
- the inflection point processing unit 131 calculates the inflection point in the change of T wave height ⁇ heart rate with respect to the heart rate acquired by the heart rate acquisition unit 111 based on the relationship between the T wave height ⁇ heart rate and exercise intensity of the subject. Extract. The inflection point exists in the range where the exercise intensity is 50 to 90%. The inflection point processing unit 131 calculates the exercise intensity of the subject corresponding to the inflection point of the value of T wave height ⁇ heart rate, and stores it in the storage unit 12.
- the AT calculation unit 132 calculates the AT of the subject based on the exercise intensity of the subject at the inflection point extracted by the inflection point processing unit 131. More specifically, the AT calculation unit 132 calculates the exercise intensity of the subject at the bending point extracted by the bending point processing unit 131 as AT.
- the AT calculation unit 132 stores the calculated AT value of the target person in the storage unit 12.
- the output unit 14 outputs information such as the target person's AT estimated by the estimation unit 13. More specifically, the output unit 14 displays the AT value calculated by the AT calculation unit 132 on a display screen or the like.
- the AT estimation device 1 includes an arithmetic device 102 having a CPU 103 and a main storage device 104 connected via a bus 101, a communication control device 105, a sensor 106, an external storage device 107, and a display device 108. And a program for controlling these hardware resources.
- the CPU 103 and the main storage device 104 constitute an arithmetic device 102.
- a program for the CPU 103 to perform various controls and calculations is stored in the main storage device 104 in advance.
- the communication control device 105 is a control device for connecting the AT estimation device 1 and various external electronic devices via a communication network NW.
- the communication control device 105 may receive heart rate and electrocardiographic waveform data from the below-described sensor 106 attached to the subject via the communication network NW.
- the sensor 106 is realized by a biological sensor such as a heart rate monitor and an electrocardiograph.
- the sensor 106 is worn, for example, on the chest or wrist of the subject over a period during which the subject exercises, and measures the heart rate and electrocardiographic waveform of the subject.
- the sensor 106 attached to the chest measures an electrocardiographic waveform with an electrode (not shown), detects a heartbeat from the change, and calculates the number of beats per minute from the interval between the heartbeats. Measure as
- the external storage device 107 includes a readable / writable storage medium and a drive device for reading / writing various information such as programs and data from / to the storage medium.
- a semiconductor memory such as a hard disk or a flash memory can be used as a storage medium.
- the external storage device 107 is a data storage unit 107a, a program storage unit 107b, and other storage devices (not shown), such as a storage device for backing up programs and data stored in the external storage device 107. Can have.
- the data storage unit 107a stores information on the electrocardiogram waveform and heart rate of the subject measured by the sensor 106.
- the data storage unit 107a corresponds to the storage unit 12 illustrated in FIG.
- the program storage unit 107b stores various programs for executing processing necessary for AT estimation such as heart rate and T wave height acquisition processing, inflection point processing, and AT calculation processing in the present embodiment. Yes.
- the display device 108 constitutes the display screen of the AT estimation device 1 and functions as the output unit 14.
- the display device 108 is realized by a liquid crystal display or the like.
- a biosensor with functions of a heart rate meter and an electrocardiograph (not shown) is attached to the subject's chest, wrist, etc.
- the heart rate and the electrocardiographic waveform of the subject are measured by the biosensor over a period until the exercise intensity in the subject exceeds 90% after the exercise is started.
- the heart rate acquisition unit 111 acquires heart rate data over a period during which the subject exercises (step S1).
- the T wave height acquisition unit 112 acquires electrocardiographic waveform data over a period during which the subject performs exercise, and acquires T wave height data from the electrocardiographic waveform data (step S2).
- the T wave height acquisition unit 112 acquires the RS height from the peak value of the R wave to the peak value of the S wave from the ECG waveform data, and based on the T wave height normalized by the RS height. Data of T wave height ⁇ heart rate is obtained (step S3).
- the T wave height acquisition unit 112 is a measured value of T wave height obtained by an external biological sensor or a value of T wave height ⁇ heart rate, or T wave height ⁇ heart rate normalized by RS height. A configuration for acquiring the value of may be adopted.
- the bending point processing unit 131 obtains a relationship between the acquired T wave height ⁇ heart rate and the exercise intensity converted by the heart rate (step S4).
- a bending point where the value of T wave height ⁇ heart rate bends is extracted in the relationship between the T wave height ⁇ heart rate and exercise intensity of the subject obtained by the inflection point processing unit 131, and the T wave height ⁇ heart rate is calculated.
- the exercise intensity corresponding to the value of the bending point is obtained (step S5). As described above, based on the fact that the exercise point is extracted in the range of 50 to 90%, it is possible to use only the range of 50 to 90% for the value of exercise intensity.
- the AT calculation unit 132 calculates the AT based on the value of the exercise intensity that becomes the inflection point of the T wave height ⁇ heart rate value obtained in step S4 (step S6). That is, the AT calculation unit 132 obtains the value of the exercise intensity serving as the bending point as AT. Note that the calculated AT of the subject is output by the output unit 14. Further, the output unit 14 may convert the exercise intensity obtained as AT into another index, for example, heart rate (bpm), power (Watt), and the like and output it.
- bpm heart rate
- Watt power
- the T wave height in the electrocardiographic waveform of the subject is used as the feature amount. Also, based on the relationship between T wave height x heart rate and exercise intensity, the intensity of exercise at the inflection point of the T wave height x heart rate value seen within the range of 50 to 90% of exercise intensity. Estimate the subject's AT. Therefore, it is possible to estimate the AT of the subject more easily without requiring blood collection or a large device.
- the T wave height is corrected by normalization based on the RS height, the R wave height, or the S wave depth, noise is included due to, for example, the electrode of the electrocardiograph getting wet with sweat. Even in this case, the AT can be calculated based on a more accurate T wave height.
- the exercise intensity is not limited to the heart rate, and may be changed depending on the type of exercise such as power, speed, and number of rotations and the acquired data.
- the exercise performed by the subject is not limited to the incremental load test, and may be, for example, a random exercise. Even when the subject performs a random exercise, the T wave height ⁇ heart rate may be obtained from the subject's electrocardiogram waveform, and the relationship between the T wave height ⁇ heart rate and the exercise intensity may be obtained in the same manner.
- the relationship with the exercise intensity is obtained using the data of the T wave height ⁇ heart rate of the subject.
- the inflection point can be similarly extracted from the relationship with the exercise intensity, and the value of the corresponding exercise intensity can be calculated as AT.
- the height of the R wave whose height changes according to the motion of the subject may be used as the feature quantity in the same manner as the T wave height.
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Abstract
Description
[発明の原理]
図1は、心電波形を示す図である(非特許文献2および非特許文献3参照)。本発明の実施の形態に係るAT推定方法は、対象者の心電波形から指標となる予め定められた特徴量を抽出し、その特徴量に基づいて対象者の運動状態を管理するためのATを推定する。
以下、本発明に係るAT推定方法を実施するためのAT推定装置1について詳細に説明する。
図4は、第1の実施の形態に係るAT推定装置1の機能構成を示すブロック図である。AT推定装置1は、生体情報取得部11、記憶部12、推定部13、および出力部14を備える。
生体情報取得部11は、対象者の心拍および心電に関する情報を、対象者に装着された外部の心拍計および心電計の機能を備える生体センサ(図示しない)などから取得する。このとき、生体情報取得部11は、上述した実験結果から、対象者において運動強度が徐々に増加する運動を開始してから、その運動強度が90%程度までの期間にわたる心拍および心電に関する情報を取得すればよい。
推定部13は、生体情報取得部11によって取得された対象者の心拍数およびT波高さ×心拍数のデータに基づいて、対象者のATを推定する。
より詳細には、AT算出部132は、屈曲点処理部131によって抽出された屈曲点における対象者の運動強度をATとして算出する。
次に、上述した機能構成を有するAT推定装置1のハードウェア構成について図5のブロック図を参照して説明する。
次に、上述した本発明のAT推定方法を実施するためのAT推定装置1の動作について、図6のフローチャートを参照して説明する。まず、図示しない心拍計および心電計の機能を有する生体センサが対象者の胸部や手首などに装着され、対象者は漸増負荷試験のような徐々に運動強度が増加するように設定された運動を開始する。運動を開始してから、対象者における運動強度が、例えば、90%を超える程度までの期間にわたって、生体センサにより対象者の心拍数と心電波形が計測される。
Claims (9)
- 対象者が行う運動の運動強度を取得する第1取得ステップと、
運動を行う前記対象者の心電波形を取得する第2取得ステップと、
取得された前記心電波形から、予め定められた特徴量を取得する第3取得ステップと、
前記予め定められた特徴量と取得された前記運動強度との関係に基づいて前記対象者の嫌気性代謝閾値を推定する推定ステップと、
を備え、
前記推定ステップは、取得された前記運動強度に対する前記予め定められた特徴量の変化における屈曲点に対応する運動強度に基づいて前記対象者の前記嫌気性代謝閾値を推定する
ことを特徴とする嫌気性代謝閾値推定方法。 - 請求項1に記載の嫌気性代謝閾値推定方法において、
前記予め定められた特徴量は、心電波形に含まれるT波の高さであることを特徴とする嫌気性代謝閾値推定方法。 - 請求項1に記載の嫌気性代謝閾値推定方法において、
前記予め定められた特徴量は、心電波形に含まれるT波の高さ×心拍数であることを特徴とする嫌気性代謝閾値推定方法。 - 請求項2または請求項3に記載の嫌気性代謝閾値推定方法において、
前記第3取得ステップは、心電波形に含まれるR波のピーク値からS波のピーク値までのRS高さを取得し、前記T波の高さを前記RS高さ、前記R波の高さ、または前記S波の深さのいずれかを用いて前記T波の高さを規格化する
ことを特徴とする嫌気性代謝閾値推定方法。 - 請求項1に記載の嫌気性代謝閾値推定方法において、
前記予め定められた特徴量は、心電波形に含まれるR波の高さであることを特徴とする嫌気性代謝閾値推定方法。 - 請求項1から5のいずれか1項に記載の嫌気性代謝閾値推定方法において、
前記第1取得ステップで取得される前記運動強度は、心拍数から計算した運動強度の値であることを特徴とする嫌気性代謝閾値推定方法。 - 請求項1から6のいずれか1項に記載の嫌気性代謝閾値推定方法において、
前記推定ステップは、前記予め定められた特徴量と取得された前記運動強度との関係において、前記運動強度の値が50%から90%の範囲に存在する前記屈曲点を用いて、前記対象者の前記嫌気性代謝閾値を推定することを特徴とする嫌気性代謝閾値推定方法。 - 対象者が行う運動の運動強度を取得する運動強度取得部と、
運動を行う前記対象者の心電波形を取得し、その心電波形から予め定められた特徴量を取得する特徴量取得部と、
前記予め定められた特徴量と取得された前記運動強度との関係に基づいて前記対象者の嫌気性代謝閾値を推定する推定部と、
を備え、
前記推定部は、取得された前記運動強度に対する前記予め定められた特徴量の変化における屈曲点に対応する運動強度に基づいて前記対象者の前記嫌気性代謝閾値を推定する
ことを特徴とする嫌気性代謝閾値推定装置。 - 請求項8に記載の嫌気性代謝閾値推定装置において、
前記予め定められた特徴量は、心電波形に含まれるT波の高さであることを特徴とする嫌気性代謝閾値推定装置。
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EP19786176.8A EP3777669B1 (en) | 2018-04-12 | 2019-04-10 | Anaerobic threshold estimation method and device |
AU2019252063A AU2019252063B2 (en) | 2018-04-12 | 2019-04-10 | Anaerobic threshold estimation method and device |
ES19786176T ES2958133T3 (es) | 2018-04-12 | 2019-04-10 | Método y dispositivo de estimación del umbral anaeróbico |
JP2020513420A JP6943334B2 (ja) | 2018-04-12 | 2019-04-10 | 嫌気性代謝閾値推定方法および装置 |
US17/046,046 US11529087B2 (en) | 2018-04-12 | 2019-04-10 | Anaerobic threshold estimation method and device |
CN201980025092.XA CN112040859B (zh) | 2018-04-12 | 2019-04-10 | 无氧代谢阈值估计方法和装置 |
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CN112040859A (zh) | 2020-12-04 |
AU2019252063A1 (en) | 2020-10-29 |
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US20210030296A1 (en) | 2021-02-04 |
EP3777669B1 (en) | 2023-07-26 |
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JP6943334B2 (ja) | 2021-09-29 |
US11529087B2 (en) | 2022-12-20 |
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