JP7058853B2 - A system for at least detecting electrocardiographic signals - Google Patents

Description

The present invention relates to a system for at least detecting an electrocardiographic signal.

Wearable devices that can detect biometric information have been developed. Patent Document 1 discloses a neckband capable of detecting an electrocardiographic signal.

JP-A-2007-202939

It is an object of the present invention to provide a system for detecting at least an electrocardiographic signal indicating myocardial activity.

The system for detecting at least an electrocardiographic signal indicating myocardial activity of the present invention includes a detecting means for detecting an electrocardiographic signal indicating muscle activity of the body and an extraction means for extracting at least an electrocardiographic signal from the myocardial signal. To prepare for.

In one embodiment of the invention, the detection means comprises a first myoelectric sensor, the first myoelectric sensor comprises a pair of first measuring electrodes, and the system uses the detection means. The mounting means further comprises a mounting means to be mounted on a person, wherein when the detecting means is mounted on the user, one of the pair of first measuring electrodes is a specific first of the user. And the other of the pair of first measuring electrodes is in contact with the specific second portion of the user, and the pair of first measuring electrodes is in contact with the portion. It is configured not to be placed on the same muscle fiber present in.

In one embodiment of the invention, in the mounting means, when the detecting means is mounted on the user, the pair of first measuring electrodes are arranged asymmetrically with respect to the median plane of the user. It is configured as follows.

In one embodiment of the invention, the particular first part of the user and the particular second part of the user are the parts of the skin at the back of the user's neck.

In one embodiment of the invention, the particular first part of the user is the part of the skin at the back of the user's neck and the particular second part of the user is the user. The part of the skin on the clavicle.

In one embodiment of the present invention, the extraction means further extracts a masticatory signal indicating masticatory activity from the myoelectric signal.

In one embodiment of the invention, the detecting means further comprises a second myoelectric sensor, the second myoelectric sensor includes a pair of second measuring electrodes, and the mounting means is the detecting means. Is attached to the user, one of the pair of second measurement electrodes is in contact with a specific third portion of the user, and of the pair of second measurement electrodes. The other of the two is in contact with the particular fourth portion of the user, and the pair of second measurement electrodes are configured not to be placed on the same muscle fiber present in the contact portion.

In one embodiment of the invention, in the mounting means, when the detecting means is mounted on the user, the pair of second measuring electrodes are arranged asymmetrically with respect to the median plane of the user. It is configured as follows.

In one embodiment of the invention, the particular third part of the user and the particular fourth part of the user are the parts of the skin on the clavicle of the user.

In one embodiment of the invention, the particular third portion of the user is the portion of the skin at the back of the user's neck and the particular fourth portion of the user is the user. The part of the skin on the clavicle.

The system according to any one of claims 6 to 8, wherein in one embodiment of the present invention, the extraction means further extracts a masticatory signal indicating masticatory activity from the myoelectric signal.

In one embodiment of the invention, the particular first part of the user and the particular second part of the user are parts of the skin on the abdomen of the user.

In one embodiment of the present invention, the extraction means further extracts a walking signal indicating walking activity from the myoelectric signal.

In one embodiment of the invention, the system is a device configured to be wearable to the user, the device comprising said detection means and said extraction means.

In one embodiment of the invention, the system is configured to be capable of communicating with a device configured to be worn by the user and to the device over a network. The device includes the detection means, and the server device includes the extraction means.
In one embodiment of the invention, the system is configured to be capable of communicating with a device configured to be worn by the user and to the device over a network. The device includes the detection means, and the user device includes the extraction means.

INDUSTRIAL APPLICABILITY According to the present invention, it is possible to provide a system for detecting at least an electrocardiographic signal indicating myocardial activity.

It is a perspective view which shows an example of the form of the myoelectric device 100 of this invention. It is a figure which shows the arrangement example of a pair of measurement electrodes 1 and 2 in the case of measuring the myoelectric signal derived from the muscle fiber of a muscle using a conventional myoelectric sensor. It is a figure which shows an example of the arrangement of the pair of measurement electrodes 114, 115 of the myoelectric sensor when the user wears the myoelectric device 100. A pair of measurement electrodes of a conventional myoelectric sensor are arranged along the direction in which the muscle fibers of the jaw and the muscle of the throat of the subject extend (conventional electrode arrangement shown in FIG. 2A), and the myoelectric device 100 of the present invention is provided. It is a figure which shows the result of having measured the myoelectric signal by arranging a pair of measurement electrodes 114, 115 of a subject in the rear part of the neck of a subject (the electrode arrangement shown in FIG. 2B). FIG. 4 (a) is a diagram showing an example of an electrocardiographic signal waveform obtained when a pair of measurement electrodes of a conventional myoelectric sensor is placed near the heart of the left chest, and FIG. 4 (b) is a diagram. It is a figure which shows the example of the waveform of the electrocardiographic signal extracted from the myoelectric signal obtained when the pair of measurement electrodes 114, 115 of the myoelectric sensor of the myoelectric device 100 are arranged in the rear part of a neck. It is a block diagram which shows an example of the structure of the myoelectric device 100. It is a flowchart which shows an example of the process for detecting at least an electrocardiographic signal. It is a figure which shows the result of the frequency analysis of the myoelectric signal detected by the myoelectric sensor 120 in step S601. It is a perspective view which shows an example of the form of the myoelectric device 100'which is an alternative form of the myoelectric device 100. It is a figure which shows an example of the structure of the myoelectric device 100'. It is an example of the configuration of the system 10 for detecting at least an electrocardiographic signal. It is a perspective view which shows an example of the form of the myoelectric device 100 ″ which is an alternative form of the neckband type myoelectric device 100, 100 ″. It is a perspective view which shows an example of the form of the myoelectric device 100 ″ which is an alternative form of the myoelectric device 100, 100 ″, 100 ″. It is a figure which shows the state which the myoelectric device 100 ″ is attached to the abdomen of the user.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.

1. 1. Myoelectric device FIG. 1 shows an example of the form of the myoelectric device 100 of the present invention.

The myoelectric device 100 is a neckband type device that can be worn around the user's neck. The myoelectric device 100 includes a housing 110 and arms 111, 112 extending from both ends of the housing 110. An electromyographic sensor (not shown in FIG. 1) is built in the housing 110. The myoelectric sensor includes a reference electrode 113 and a pair of measurement electrodes 114 and 115. The reference electrode 113 and the pair of measurement electrodes 114 and 115 are exposed on the outer surface of the housing 110. The myoelectric sensor detects the myoelectric signal indicating the muscle activity of the body from the electric signal measured by the reference electrode 113 and the pair of measurement electrodes 114 and 115.

The user attaches the myoelectric device 100 by aligning the center of the housing 110 with the center of the back of the neck and wrapping the arms 111, 112 around the neck. The arms 111, 112 are configured such that the reference electrode 113 and the pair of measurement electrodes 114, 115 come into contact with the skin at the back of the user's neck when the user wears the myoelectric device 100. The user is not restricted in exercise by wearing the myoelectric device 100. As used herein, the term "rear" refers to a portion posterior to the human coronal plane, preferably posterior to the human coronal plane, and within ± 45 degrees laterally from the human median plane. A portion, more preferably a portion posterior to the human coronal plane and within a range of ± 30 degrees in the left-right direction from the human midline.

FIG. 2A shows an arrangement example of a pair of measurement electrodes 1 and 2 when measuring a myoelectric signal derived from a muscle fiber of a muscle using a conventional myoelectric sensor.

FIG. 2B shows an example of the arrangement of the pair of measurement electrodes 114 and 115 of the myoelectric sensor when the user wears the myoelectric device 100. At the back of the user's neck, muscle fibers 1000 of the neck muscle extend in the vertical direction.

The conventional myoelectric sensor aims to detect the myoelectric signal derived from the nearest muscle at the position where the pair of measurement electrodes are arranged, and to remove the myoelectric signal derived from other muscles as noise. In the conventional myoelectric sensor, it was common sense to arrange a pair of measurement electrodes along the direction in which the muscle fibers of the muscle to be measured extend. Since the myoelectric signal is a signal that propagates on the surface of the muscle, the S / N ratio of the myoelectric signal detected by arranging a pair of measurement electrodes along the direction in which the muscle fiber to be measured extends. This is because it can be enhanced. In the example shown in FIG. 2A, the pair of measurement electrodes 1 and 2 of the conventional myoelectric sensor are arranged so as to be located on the same muscle fiber along the direction in which the muscle fiber to be measured extends. In addition, in the conventional myoelectric sensor, a large number of electrodes are arranged to perform measurement so as not to acquire myoelectric signals derived from muscles other than the measurement target, which causes noise.

In the myoelectric sensor of the myoelectric device 100 of the present invention, not only the myoelectric signal derived from the muscle closest to the position where the pair of measurement electrodes are arranged but also the muscle at the position away from the position where the pair of measurement electrodes are arranged. The purpose is to detect the myoelectric signal of origin and to detect the myoelectric signal that was deleted as noise by the conventional myoelectric sensor. In order to achieve this object, the myoelectric device 100 of the present invention uses only a small number of electrodes (in this example, the reference electrode 113 and the pair of measurement electrodes 114 and 115), and the muscle of the present invention is used. The pair of measurement electrodes 114 and 115 of the myoelectric sensor of the electric device 100 avoids a high S / N ratio of the myoelectric signal derived from the muscle closest to the position where the pair of measurement electrodes 114 and 115 are arranged. , The pair of measurement electrodes 114, 115 are arranged so as to relatively increase the S / N ratio of the myoelectric signal derived from the muscle at a position far from the position where the measurement electrodes 114, 115 are arranged. In the example shown in FIG. 2B, the measurement electrode 114 of the myoelectric sensor is arranged on the muscle fiber 1000 at the rear of the neck, but the measurement electrode 115 is not arranged on the muscle fiber 1000 of the neck. As described above, the pair of measurement electrodes 114 and 115 of the myoelectric sensor of the myoelectric device of the present invention are not arranged on the same muscle fiber existing at the site where the pair of measurement electrodes 114 and 115 come into contact with each other.

When the myoelectric device 100 is attached to the user, the pair of measurement electrodes 114 and 115 of the myoelectric sensor of the myoelectric device 100 of the present invention includes a line connecting the pair of measurement electrodes 114 and 115 and a pair of measurement electrodes. The angle θ formed by the direction in which the muscle fiber of the nearest muscle extends at the position where 114 and 115 are arranged may be 30 degrees or more, 45 degrees or more, 60 degrees or more, or preferably 90 degrees. .. The closer θ is to 90 degrees, the more the S / N ratio of the myoelectric signal derived from the nearest muscle is significantly reduced at the position where the pair of measurement electrodes 114 and 115 are arranged, and the pair of measurement electrodes 114 and 115 are arranged. It is possible to relatively increase the S / N ratio of the myoelectric signal derived from the muscle at a position far from the position.

Further, in the example shown in FIG. 2B, the measuring electrode 114 is located on the muscle fiber 1000 of the right half of the user, while the measuring electrode 115 is symmetrically above the left half of the body with the measuring electrode 114. Is located in. As described above, the pair of measurement electrodes 114 and 115 may be positioned symmetrically with respect to the median plane of the user at the rear part of the user's neck when the myoelectric device 100 is attached to the user. This can be achieved, for example, by setting the distances from the center of the housing 110 of the myoelectric device 100 to the pair of measurement electrodes 114 and 115 to be the same distance, respectively. As used herein, the term "same distance" includes a range of ± 10 mm. As used herein, "located symmetrically with respect to the median plane" means that the angle between the line passing through the electrode and the center of the body and the median plane in front of the human coronal plane is the same in the left-right direction. The term "same angle" includes a range of ± 15 degrees.

Alternatively, the pair of measurement electrodes 114, 115 may be positioned asymmetrically with respect to the user's midline at the back of the user's neck when the myoelectric device 100 is attached to the user. This can be achieved, for example, by setting the distances from the center of the housing 110 of the myoelectric device 100 to the pair of measurement electrodes 114, 115 to be different distances. For example, one of the pair of measuring electrodes 114 is provided at a position 50-70 mm, preferably 60 mm from the center of the housing 110, and the other measuring electrode 115 of the pair of measuring electrodes is the housing 110. Provided at a position of 10-30 mm, preferably 20 mm from the center of the, when the myoelectric device 100 is attached to the user, it is asymmetrically located at the back of the user's neck with respect to the user's midplane. .. At this time, care should be taken so that the pair of measurement electrodes 114 and 115 do not overlap with the reference electrode 113. In this way, the pair of measurement electrodes 114, 115 can be placed at any angular position on the back of the user's neck. For example, in one of the pair of measurement electrodes 114, the angle formed by the line passing through the measurement electrode 114 and the center of the user's body and the median surface behind the coronal surface of the user is to the right. The measurement electrode 115 of the pair of measurement electrodes is placed at a position of 40 to 60 degrees, preferably 50 degrees, from the line passing between the electrode 115 and the center of the user's body and the coronal surface of the user. It may be arranged at a position where the angle formed with the median surface on the rear side is 5 to 15 degrees, preferably 10 degrees to the left. By arranging the pair of measurement electrodes 114 and 115 so as to be positioned asymmetrically with respect to the median plane of the user in this way, the shortest distance between the pair of measurement electrodes and the measurement target (for example, the heart) can be determined. , Can be different between electrodes. This causes a time difference between the myoelectric signal measured by one of the pair of measurement electrodes 114 and the myoelectric signal measured by the other measurement electrode 115 of the pair of measurement electrodes. This makes it possible to easily distinguish between the myoelectric signal to be measured and noise. By using a pair of measuring electrodes asymmetrically arranged with respect to the median plane, it is possible to obtain a clearer myoelectric signal than the myoelectric signal obtained from the pair of measuring electrodes arranged symmetrically with respect to the median plane. ..

In the above-mentioned example, the example in which the pair of measurement electrodes 114 and 115 come into contact with the skin at the back of the user's neck has been described, but the present invention is not limited thereto. When the pair of measuring electrodes 114, 115 are located asymmetrically with respect to the midplane of the user, one of the pair of measuring electrodes 114, 115 comes into contact with the skin at the back of the user's neck, and the pair of measuring electrodes The pair of measurement electrodes 114, 115 may be arranged so that the other of 114, 115 is in contact with the skin on the user's clavicle. At this time, care should be taken not to arrange the pair of measurement electrodes 114 and 115 on the same muscle fiber existing at the contact portion. For example, the measuring electrode 114 of the pair of measuring electrodes 114, 115 is in contact with the skin on the clavicle on the right side of the user, and the measuring electrode 115 of the pair of measuring electrodes 114, 115 is on the back of the user's neck. A pair of measurement electrodes 114, 115 may be arranged so as to be in contact with the skin on the left side. Preferably, the measuring electrode 114 of the pair of measuring electrodes 114, 115 contacts the skin on the right side of the back of the user's neck, and the measuring electrode 115 of the pair of measuring electrodes 114, 115 is on the left side of the user. A pair of measuring electrodes 114, 115 may be arranged so as to be in contact with the skin on the clavicle. Since the human heart is slightly to the left of the median plane, such electrode arrangements increase the shortest distance between the pair of measurement electrodes 114, 115 and the heart to be measured, greater between the electrodes. Can be different.

In the example shown in FIG. 2B, an example in which the measurement electrode 114 is located on the muscle fiber 1000 has been described, but the pair of measurement electrodes 114 and 115 are present at a portion where the pair of measurement electrodes 114 and 115 come into contact with each other. It suffices if it is not placed on the same muscle fiber, and it does not have to be located on the muscle fiber 1000. Rather, it is preferable that the pair of measurement electrodes 114 and 115 are not located on any of the muscle fibers in order to reduce the influence of the myoelectric signal derived from the nearest muscle fiber.

FIG. 3 shows a pair of measurement electrodes of a conventional myoelectric sensor arranged along the direction in which the muscle fibers of the jaw and the muscle of the throat of the subject extend (conventional electrode arrangement shown in FIG. 2A), and the muscle of the present invention is shown. The result of measuring the myoelectric signal is shown by arranging the electric device 100 with a pair of measurement electrodes 114 and 115 of the subject at the rear of the neck of the subject (electrode arrangement shown in FIG. 2B).

FIG. 3 shows the frequency distribution obtained from the frequency analysis result of the myoelectric signal from each myoelectric sensor. The upper graph shows the frequency distribution of the signal obtained from the conventional myoelectric sensor placed along the muscle fiber of the jaw, and the middle graph shows the conventional myoelectricity placed along the muscle fiber of the throat. The frequency distribution of the signal obtained from the sensor is shown, and the lower graph shows the frequency distribution of the signal obtained from the myoelectric sensor of the myoelectric device 100. The horizontal axis represents time series, and the vertical axis represents frequency. The upper part of the vertical axis has a lower frequency, and the lower part of the vertical axis has a higher frequency. The color on the graph indicates the intensity of the frequency component. The darker the color, the weaker the frequency component, and the brighter the color, the stronger the frequency component.

In the upper graph, the brightly colored areas over a wide frequency band indicate that the jaw muscles are activated by mastication. At the time when the jaw muscles are active due to mastication, there is a part in the lower graph that shows that the muscles are active, albeit weakly. This indicates that the myoelectric sensor of the myoelectric device 100 has detected a masticatory signal indicating masticatory activity.

In the middle graph, the brightly colored areas in the low frequency band indicate that the myocardium is active. At the time when the myocardium is active, there is a part indicating that the myocardium is active even in the lower graph. This indicates that the myoelectric sensor of the myoelectric device 100 has detected an electrocardiographic signal indicating myocardial activity.

As described above, the myoelectric sensor of the myoelectric device 100 has a pair of measurement electrodes 114 as well as a myoelectric signal derived from the muscles of the neck and / or shoulder near the position where the pair of measurement electrodes 114 and 115 are arranged. , 115 can at least detect the electrocardiographic signal of the heart at a position away from the location. In the myoelectric sensor of the myoelectric device 100, not only the myoelectric signal derived from the muscles of the neck and / or the shoulder near the position where the pair of measurement electrodes 114 and 115 are arranged, but also the pair of measurement electrodes 114 and 115 are arranged. The electrocardiographic signal of the heart and the masticatory signal by the jaw muscle may be detected at a position far from the position.

The myoelectric device 100 can at least detect an electrocardiographic signal by extracting at least an electrocardiographic signal indicating myocardial activity from the myoelectric signal detected by the myoelectric sensor of the myoelectric device 100. The process of extracting at least the electrocardiographic signal will be described later. The myoelectric device 100 obtains an electrocardiographic signal and a masticatory signal by extracting an electrocardiographic signal indicating myocardial activity and a masticatory signal indicating masticatory activity from the myoelectric signal detected by the myoelectric sensor of the myoelectric device 100. It may be detected. The process of extracting the electrocardiographic signal and the mastication signal will be described later.

FIG. 4A is an example of the waveform of the electrocardiographic signal obtained when a pair of measurement electrodes of the conventional myoelectric sensor are arranged near the heart of the left chest (conventional electrode arrangement shown in FIG. 2A). FIG. 4 (b) is shown from the myoelectric signal obtained when the pair of measurement electrodes 114 and 115 of the myoelectric sensor of the myoelectric device 100 are arranged at the rear part of the neck (electrode arrangement shown in FIG. 2B). An example of the waveform of the extracted electrocardiographic signal is shown.

In the waveform of a normal electrocardiographic signal, points P, Q, R, S, T, and U are mainly recognized as feature points. The waveform shown in FIG. 4A clearly shows points P, Q, R, S, T, and U. In the waveform shown in FIG. 4B, although the shape is altered, the existence of points P, Q, R, S, and T among the main feature points can be confirmed.

As described above, the myoelectric device 100 can extract the electrocardiographic signal of the heart at a position away from the position where the pair of measurement electrodes 114 and 115 are arranged while maintaining the feature points.

The extracted electrocardiographic signal and / or masticatory signal can be used, for example, for discovering a user's potential illness and its precursors, and for observing and managing a lifestyle. This is because the heart is one of the most visible areas of physical abnormalities, and mastication is associated with diet in the lifestyle. The electrocardiographic signal and / or masticatory signal extracted by the myoelectric device 100 is transmitted to, for example, a healthcare operator. Healthcare providers analyze electrocardiographic and / or masticatory signals and use them to monitor the physical condition of the user. The healthcare business operator can provide, for example, a healthcare application to a user terminal and present the analysis result to the user through the healthcare application.

2. 2. Configuration of the Myoelectric Device 100 FIG. 5 shows an example of the configuration of the myoelectric device 100.

The myoelectric device 100 includes a housing 110, a myoelectric sensor 120, an AD conversion unit 130, a memory unit 140, a processor unit 150, and a transmission unit 160 processor unit 150. The myoelectric sensor 120, the AD conversion unit 130, the memory unit 140, the processor unit 150, and the transmission unit 160 are arranged in the housing 110.

As shown in FIG. 1, the myoelectric sensor 120 includes a reference electrode 113 and a pair of measurement electrodes 114 and 115. The myoelectric sensor 120 can be any detection means capable of detecting a myoelectric signal indicating the muscle activity of the body. For example, the myoelectric sensor 120 may include a primary amplifier, a high-pass filter, a low-pass filter, a notch filter, and a secondary amplifier for detecting the myoelectric signal. Primary and secondary amplifiers are used to amplify the signal. High-pass filters are used to attenuate signals with frequencies below a predetermined frequency, such as signals with frequencies below 10 Hz. Low-pass filters are used to attenuate signals with frequencies above a given frequency, such as signals with frequencies above 400 Hz. Notch filters are used to attenuate signals in a predetermined range of frequencies, for example AC noise of 50-60 Hz, which is typical electrical noise. It is also possible to use a band elimination filter instead of the notch filter. The output from the myoelectric sensor 120 is an analog signal. When the myoelectric sensor 120 having such a configuration is used, a signal in the frequency band of 10 Hz to 400 Hz is obtained from the voltage signal between the reference electrode 113 and the measurement electrode 114 and the voltage signal between the reference electrode 113 and the measurement electrode 115. Can be detected as a myoelectric signal.

The AD conversion unit 130 converts the analog signal output from the myoelectric sensor 120 into a digital signal. The AD conversion unit 130 may be any circuit capable of converting an analog signal into a digital signal.

The memory unit 140 stores a program required for executing the processing of the myoelectric device 100, data required for executing the program, and the like. The memory unit 140 stores a program that realizes a process of detecting at least an electrocardiographic signal (for example, a program that realizes the process shown in FIG. 6). The memory unit 140 may be implemented by any storage means.

The processor unit 150 controls the operation of the entire myoelectric device 100. The processor unit 150 reads the program stored in the memory unit 140 and executes the program. This makes it possible to make the myoelectric device 100 function as a device that performs a desired step.

The transmission unit 160 is configured to wirelessly transmit a signal to the outside of the myoelectric device 100. It does not matter how the transmitter 160 wirelessly transmits the signal. For example, the transmission unit 160 may transmit a signal using a wireless LAN such as Wi-fi. For example, the transmission unit 160 may transmit a signal by using short-range wireless communication such as Bluetooth (registered trademark). The transmission unit 160 transmits at least an electrocardiographic signal (preferably an electrocardiographic signal and a mastication signal) extracted by the processor unit 150 to the outside of the myoelectric device 100.

In the example shown in FIG. 5, the example in which the AD conversion unit 130 is provided outside the myoelectric sensor 120 has been described, but the AD conversion unit 130 may be provided inside the myoelectric sensor 120. In this case, the output from the myoelectric sensor 120 is a digital signal indicating the myoelectric signal. In this case, the AD conversion unit 130 can be omitted from the configuration shown in FIG.

3. 3. Processing by EMG Device 100 FIG. 6 shows an example of processing for detecting at least an electrocardiographic signal. This process is performed in the myoelectric device 100.

In step S601, the myoelectric sensor 120 detects the myoelectric signal. The myoelectric sensor 120 detects an myoelectric signal using the reference electrode 113 and the pair of measurement electrodes 114 and 115.

In step S602, the processor unit 150 extracts the electrocardiographic signal from the myoelectric signal. The frequency band of various myoelectric signals differs depending on the target. The processor unit 150 of the myoelectric device 100 can extract an electrocardiographic signal from the myoelectric signal based on the frequency of the myoelectric signal.

The process shown in FIG. 6 may further include a process in which the processor unit 150 extracts a masticatory signal from the myoelectric signal as step S603.

FIG. 7 shows the result of frequency analysis of the myoelectric signal detected by the myoelectric sensor 120 in step S601. FIG. 7 is a graph showing a frequency distribution, in which the horizontal axis represents a time series and the vertical axis represents a frequency. The upper part of the vertical axis has a lower frequency, and the lower part of the vertical axis has a higher frequency. The color on the graph indicates the intensity of the frequency component. The darker the color, the weaker the frequency component, and the brighter the color, the stronger the frequency component.

As shown in FIG. 7, the frequency band of the electrocardiographic signal is lower than the frequency band of the myoelectric signal other than the electrocardiographic signal.

As described above, in the myoelectric signal detected by the myoelectric sensor 120 in step S601, the electrocardiographic signal and the myoelectric signal other than the electrocardiographic signal and noise can be clearly distinguished based on the frequency band. Therefore, in step S602, the processor unit 150 of the myoelectric device 100 can extract an electrocardiographic signal from the myoelectric signal based on the frequency band of the signal.

The processor unit 150 of the myoelectric device 100 can also extract the mastication signal from the myoelectric signal by performing appropriate processing on the myoelectric signal in step S603. In step S603, the processor unit 150 of the myoelectric device 100 performs further processing on myoelectric signals other than the electrocardiographic signal in addition to or instead of performing appropriate processing on the myoelectric signal. By doing so, the chewing signal can also be extracted.

4. Alternative Form of Myoelectric Device 100 FIG. 8 shows an example of the form of the myoelectric device 100'which is an alternative form of the myoelectric device 100.

The myoelectric device 100'is a neckband type device that can be worn around the user's neck, similarly to the myoelectric device 100. In FIG. 8, the same components as those in FIG. 1 are given the same reference numbers, and the description thereof will be omitted here.

In the myoelectric device 100', a pair of measurement electrodes 116 and 117 (a pair of second measurement electrodes) are arranged at the tips of the arms 111 and 112. The user wears the myoelectric device 100'by wrapping the arms 111, 112 around the neck. The arms 111 and 112 are configured such that when the user wears the myoelectric device 100', the pair of measurement electrodes 116 and 117 are in contact with the skin on the user's left and right clavicle, respectively. The pair of measurement electrodes 116 and 117 are on the same muscle fiber existing at the site where the pair of measurement electrodes 116 and 117 are in contact with each other, similarly to the pair of measurement electrodes 114 and 115 (a pair of first measurement electrodes). Not placed.

The pair of measurement electrodes 116 and 117 of the myoelectric sensor of the myoelectric device 100'of the present invention includes a pair of wires connecting the pair of measurement electrodes 116 and 117 when the myoelectric device 100'is attached to the user. Arranged so that the angle θ formed by the direction in which the muscle fiber of the nearest muscle extends to the position where the measurement electrodes 116 and 117 are arranged is 30 degrees or more, 45 degrees or more, 60 degrees or more, or preferably 90 degrees. Can be done. The closer θ is to 90 degrees, the more the S / N ratio of the myoelectric signal derived from the muscle closest to the position where the pair of measurement electrodes 116 and 117 are placed is significantly reduced, and the pair of measurement electrodes 116 and 117 are placed. It is possible to relatively increase the S / N ratio of the myoelectric signal derived from the muscle at a position far from the position.

The pair of measuring electrodes 116 and 117 of the myoelectric device 100'are positioned symmetrically with respect to the user's median plane on the user's clavicle when the myoelectric device 100'is attached to the user. May be good. This can be achieved, for example, by setting the distances from the center of the housing 110 of the myoelectric device 100'to the pair of measurement electrodes 116 and 117 to the same distance. Alternatively, the pair of measurement electrodes 116, 117 of the myoelectric device 100'so that when the myoelectric device 100' is attached to the user, they are asymmetrically located on the user's clavicle with respect to the user's median plane. You may do it. This can be achieved, for example, by setting the distances from the center of the housing 110 of the myoelectric device 100'to the pair of measurement electrodes 116 and 117 to different distances. For example, the measuring electrode 116 of one of the pair of measuring electrodes is provided at a position of 270 to 290 mm, preferably 280 mm from the center of the housing 110, and the other measuring electrode 117 of the pair of measuring electrodes is the housing 110. Provided at a position of 230-250 mm, preferably 240 mm from the center of the, when the myoelectric device 100 is attached to the user, it is asymmetrically located at the back of the user's neck with respect to the user's midplane. .. In this way, the pair of measurement electrodes 116, 117 can be placed at any position on the user's clavicle. By arranging the pair of measurement electrodes 116 and 117 so as to be positioned asymmetrically with respect to the median plane of the user, the shortest distance between the pair of measurement electrodes and the measurement target (for example, the heart) can be set between the electrodes. Can be different. This causes a time difference between the myoelectric signal measured by one of the pair of measurement electrodes 116 and the myoelectric signal measured by the other measurement electrode 117 of the pair of measurement electrodes. This makes it possible to easily distinguish between the myoelectric signal to be measured and noise. By using a pair of measuring electrodes asymmetrically arranged with respect to the median plane, it is possible to obtain a clearer myoelectric signal than the myoelectric signal obtained from the pair of measuring electrodes arranged symmetrically with respect to the median plane. ..

The myoelectric device 100'includes two myoelectric sensors (ie, a first myoelectric sensor 120 ₁ and a second myoelectric sensor 120 ₂ ; not shown in FIG. 8). A portion other than the pair of measurement electrodes 116 and 117 of the first myoelectric sensor 120 ₁ and the second myoelectric sensor 120 ₂ is built in the housing 110. The configuration of the first myoelectric sensor 120 ₁ and the second myoelectric sensor 120 ₂ is the same as the configuration of the myoelectric sensor 120 shown in FIG. Similar to the myoelectric sensor 120 shown in FIG. 5, the first myoelectric sensor 120 ₁ and the second myoelectric sensor 120 ₂ may detect a signal in a frequency band of, for example, 10 Hz to 400 Hz as a myoelectric signal. can. The first myoelectric sensor 120 ₁ detects a myoelectric signal using the reference electrode 113 and the pair of measurement electrodes 114 and 115, and the second myoelectric sensor 120 ₂ has the reference electrode 113 and the pair of measurement electrodes. The myoelectric signal is detected using 116 and 117.

The signal detected by the first myoelectric sensor 120 ₁ has a low signal strength of the electrocardiographic signal, but the level of the myoelectric signal other than the electrocardiographic signal and the noise is lower than that, and the S / N ratio of the electrocardiogram is high. expensive. Therefore, in the signal detected by the _first myoelectric sensor 1201, it is possible to easily distinguish the electrocardiographic signal from the myoelectric signal other than the electrocardiographic signal and noise, but it is obtained by the electrocardiographic signal. The reliability of the information is low.

The signal detected by the second myoelectric sensor 120 ₂ has a high signal strength of the electrocardiographic signal, but also has a large amount of other myoelectric signals and noise, and the S / N ratio of the electrocardiogram is small. Therefore, in the signal detected by the _second myoelectric sensor 1202, it is not easy to distinguish the electrocardiographic signal from the myoelectric signal other than the electrocardiographic signal and noise, but the signal strength of the electrocardiographic signal is the first. It is larger than the signal strength of the electrocardiographic signal detected by the myoelectric sensor 120 ₁ .

As described above, the first myoelectric sensor 120 ₁ and the second myoelectric sensor 120 ₂ have advantages and disadvantages. By using the first myoelectric sensor 120 ₁ and the second myoelectric sensor 120 ₂ in combination, the myoelectric device 100'can compensate for the weaknesses while maintaining the advantages of these myoelectric sensors. ..

For example, the myoelectric device 100'uses the signal detected by the first myoelectric sensor 120 ₁ as an index for distinguishing an electrocardiographic signal from a myoelectric signal other than the electrocardiographic signal and noise. The electrocardiographic signal and the myoelectric signal other than the electrocardiographic signal and noise may be distinguished from the signal detected by the second myoelectric sensor 120 ₂ based on the index. This determines, for example, the time of the electrocardiographic signal from the signal detected by the first myoelectric sensor 120 ₁ and the time of the myoelectric signal other than the electrocardiographic signal and the noise, and the second myoelectric sensor. Of the signals detected by 120 ₂ , the signal at the time determined as the time of the electrocardiographic signal is determined to be the electrocardiographic signal, and the time determined as the time of the myoelectric signal other than the electrocardiographic signal and the noise. Is achieved by determining that the signal is a myoelectric signal other than an electrocardiographic signal and noise. Thereby, the electrocardiographic signal and the myoelectric signal other than the electrocardiographic signal and the noise can be distinguished from the signal detected by the second myoelectric sensor 120 ₂ with high accuracy. In that case, the myoelectric device 100'can obtain highly reliable information by extracting the electrocardiographic signal from the signal detected by the second myoelectric sensor 120 ₂ .

Alternatively, the myoelectric device 100'may use one of the two myoelectric sensors 120 ₁ and 120 ₂ as the main sensor and the other sensor as a spare sensor. The myoelectric sensor 120 needs to be in contact with the human body, and cannot measure the myoelectric signal unless it is in proper contact. Since the myoelectric sensor may have poor contact when the user moves, the myoelectric device 100'should use one of the two myoelectric sensors 120 ₁ and 120 ₂ as a backup. You may do it. This can reduce the risk of measurement omission due to improper contact.

In the above-mentioned example, a pair of measurement electrodes 114 and 115 in contact with the skin at the back of the user's neck and a pair of measurement electrodes 116 and 117 in contact with the skin on the left and right clavicle of the user have been described. However, the present invention is not limited to this. If the pair of measurement electrodes 114, 115 and the pair of measurement electrodes 116, 117 are located asymmetrically with respect to the user's midplane, for example, one of the pair of measurement electrodes 114, 115 is on the user's neck. It contacts the posterior skin, the other of the pair of measurement electrodes 114, 115 contacts the skin on the user's clavicle, and one of the pair of measurement electrodes 116, 117 is the skin of the posterior part of the user's neck. The pair of measuring electrodes 114, 115 and the pair of measuring electrodes 116, 117 may be arranged so that the other of the pair of measuring electrodes 116, 117 is in contact with the skin on the user's clavicle. .. At this time, care should be taken not to dispose the pair of measurement electrodes 114, 115 and the pair of measurement electrodes 116, 117 on the same muscle fiber existing at the contact site. For example, the measurement electrode 114 of the pair of measurement electrodes 114, 115 contacts the skin on the clavicle on the right side of the user, and the measurement electrode 115 of the pair of measurement electrodes 114, 115 is located at the rear of the user's neck. Touching the skin on the left side, the measuring electrode 116 of the pair of measuring electrodes 116 and 117 touching the skin on the right side of the back of the user's neck, and the measuring electrode 117 of the pair of measuring electrodes 116 and 117 is used. A pair of measuring electrodes 114, 115 and a pair of measuring electrodes 116, 117 may be arranged so as to be in contact with the skin on the clavicle on the left side of the person.

FIG. 9 shows an example of the configuration of the myoelectric device 100'. In FIG. 9, the same components as those in FIG. 5 are given the same reference numbers, and the description thereof will be omitted here.

The myoelectric device 100'includes a first myoelectric sensor 120 ₁ and a second myoelectric sensor 120 ₂ . The signal output from the first myoelectric sensor 120 ₁ and the signal output from the second myoelectric sensor 120 ₂ are provided to the AD conversion unit 130. The AD conversion unit 130 converts the analog signals output from the first myoelectric sensor 120 ₁ and the second myoelectric sensor 120 ₂ into digital signals, and provides each digital signal to the processor unit 150.

In the example shown in FIG. 9, an example in which the AD conversion unit 130 is provided outside the first myoelectric sensor 120 ₁ and the second myoelectric sensor 120 ₂ has been described, but the AD conversion unit 130 is the first. It may be provided inside the myoelectric sensor 120 ₁ and the second myoelectric sensor 120 ₂ . In this case, the output from the first myoelectric sensor 120 ₁ and the second myoelectric sensor 120 ₂ is a digital signal indicating the myoelectric signal. In this case, the AD conversion unit 130 can be omitted from the configuration shown in FIG.

The processing by the myoelectric device 100'is the same as the processing shown in FIG. In step S601, at least one of the first myoelectric sensor 120 ₁ and the second myoelectric sensor 120 ₂ detects the myoelectric signal. In step S602, the processor unit 150 extracts an electrocardiographic signal using one or both of the myoelectric signal from the first myoelectric sensor 120 ₁ and the myoelectric signal from the second myoelectric sensor 120 ₂ . do. For example, the processor unit 150 may use the electrocardiographic signal from the first myoelectric sensor 120 ₁ as an index to extract the electrocardiographic signal from the signal from the second myoelectric sensor 120 ₂ . .. Alternatively, the processor unit 150 extracts the electrocardiographic signal from the myoelectric signal from the first myoelectric sensor 120 ₁ only when the second myoelectric sensor 120 ₂ cannot detect the myoelectric signal. May be good.

The process by the myoelectric device 100'including a process in which the processor unit 150 of the myoelectric device 100' extracts a mastication signal from the myoelectric signal as step S603, similarly to the process shown in FIG. You may. In this case, the processor unit 150 of the myoelectric device 100'can also extract the mastication signal from the myoelectric signal by performing appropriate processing on the myoelectric signal in step S603. In step S603, the processor unit 150 of the myoelectric device 100'is further processed for myoelectric signals other than the electrocardiographic signal in addition to or instead of performing appropriate processing for the myoelectric signal. It is also possible to extract the chewing signal by performing the above.

In the example shown in FIGS. 1 to 9, it has been described that the processor unit 150 of the myoelectric devices 100 and 100'extracts at least an electrocardiographic signal from the myoelectric signal detected by the myoelectric sensor. Is not limited to this. The process of extracting at least the electrocardiographic signal can be performed by another information processing device including a processor unit. For example, the process of extracting at least an electrocardiographic signal can be executed by the processor unit of the server device that communicates with the myoelectric device 100. Alternatively, at least the process of extracting the electrocardiographic signal can be executed by the processor unit of the user apparatus.

Hereinafter, the system 10 for detecting at least an electrocardiographic signal will be described.

5. System for at least detecting an electrocardiographic signal FIG. 10 shows an example of a configuration of a system 10 for at least detecting an electrocardiographic signal.

In the example shown in FIG. 10, the system 10 includes an electromyographic device 100, a server device 200, and a user device 300. The myoelectric device 100, the server device 200, and the user device 300 are connected via the network 400. Here, the type of the network 400 does not matter. For example, the myoelectric device 100, the server device 200, and the user device 300 may communicate with each other via the Internet or may communicate with each other via a LAN.

The server device 200 includes an interface unit 210, a memory unit 220, and a processor unit 230. The server device 200 is connected to the database unit 240.

The interface unit 210 controls communication with the myoelectric device 100, the database unit 240, or the user device 300. The interface unit 210 may control communication by any method.

The memory unit 220 stores a program required for executing the process, data required for executing the program, and the like. For example, the memory unit 220 may store a program for realizing a process of extracting at least an electrocardiographic signal from a myoelectric signal (for example, the process of steps S602 and / or S603 of FIG. 6). Here, it does not matter how the program is stored in the memory unit 220. For example, the program may be pre-installed in the memory unit 220. Alternatively, the program may be installed in the memory unit 220 by being downloaded via the network 400, or may be installed in the memory unit 220 via a storage medium such as an optical disk or USB. May be good.

The processor unit 230 controls the operation of the entire server device 200. The processor unit 230 reads the program stored in the memory unit 220 and executes the program. This makes it possible to make the server device 200 function as a device that executes a desired step.

The database unit 240 may store the user of the myoelectric device 100 and the myoelectric signal transmitted from the myoelectric device 100 in association with each other. The database unit 240 can store any other data. The server device 200 may provide a healthcare application to the user device 300 so that the user device 300 can use the data stored in the database unit 240.

The user device 300 includes an interface unit 310, a display unit 320, a memory unit 330, and a processor unit 340.

The interface unit 310 controls communication with the myoelectric device 100 or the server device 200. The interface unit 310 may control communication by any method.

The display unit 320 may be any display that displays the screen.

The memory unit 330 stores a program required for executing the process, data required for executing the program, and the like. For example, the memory unit 330 may store a program for realizing a process of extracting at least an electrocardiographic signal from a myoelectric signal (for example, the process of steps S602 and / or S603 of FIG. 6). Here, it does not matter how the program is stored in the memory unit 330. For example, the program may be pre-installed in the memory unit 330. Alternatively, the program may be installed in the memory unit 330 by being downloaded via the network 400, or may be installed in the memory unit 330 via a storage medium such as an optical disk or USB. May be good.

The processor unit 340 controls the operation of the entire user device 300. The processor unit 340 reads the program stored in the memory unit 330 and executes the program. This makes it possible to make the user device 300 function as a device that executes a desired step.

In the above configuration, the process of detecting the myoelectric signal (for example, the process of step S601 in FIG. 6) is executed by the myoelectric device 100, and at least the process of extracting the electrocardiographic signal from the myoelectric signal (for example, FIG. The process of step S602 and / or S603 of 6) may be executed by the server device 200. In this case, it is possible to omit the user device 300 from the system 10. In this case, the processor unit 150 of the myoelectric device 100 transfers the myoelectric signal detected by the myoelectric sensor 120 to the server device 200 without performing extraction processing on the myoelectric signal detected by the myoelectric sensor 120. The transmission may be made, and the processor unit 230 of the server device 200 may at least extract the electrocardiographic signal from the myoelectric signal received from the myoelectric device 100.

In this case, it is sufficient for the memory unit 140 of the myoelectric device 100 to store a program that realizes the process of detecting the myoelectric signal (for example, the process of step S601 in FIG. 6), and at least the electrocardiographic signal is stored from the myoelectric signal. It is not necessary to store a program that realizes the extraction process (for example, the process of steps S602 and / or S603 of FIG. 6). As a result, the capacity of the memory unit 140 of the myoelectric device 100 can be reduced, and the processing by the processor unit 150 of the myoelectric device 100 can be simplified.

Alternatively, in the above-described configuration, the process of detecting the myoelectric signal (for example, the process of step S601 in FIG. 6) is executed by the myoelectric device 100, and at least the process of extracting the electrocardiographic signal from the myoelectric signal (for example). , The process of steps S602 and / or S603 of FIG. 6) may be executed by the user apparatus 300. In this case, it is possible to omit the server device 200 from the system 10. In this case, the processor unit 150 of the myoelectric device 100 transfers the myoelectric signal detected by the myoelectric sensor 120 to the user device 300 without performing extraction processing on the myoelectric signal detected by the myoelectric sensor 120. The transmission may be made, and the processor unit 340 of the user apparatus 300 may at least extract the electrocardiographic signal from the myoelectric signal received from the myoelectric device 100.

In this case, it is sufficient for the memory unit 140 of the myoelectric device 100 to store a program that realizes the process of detecting the myoelectric signal (for example, the process of step S601 in FIG. 6), and at least the electrocardiographic signal is stored from the myoelectric signal. It is not necessary to store a program that realizes the extraction process (for example, the process of steps S602 and / or S603 of FIG. 6). As a result, the capacity of the memory unit 140 of the myoelectric device 100 can be reduced, and the processing by the processor unit 150 of the myoelectric device 100 can be simplified.

In the system 10 shown in FIG. 10, the myoelectric device 100'may be used instead of the myoelectric device 100. In this case, the processor unit 150 of the myoelectric device 100'is the first without performing the extraction process for the myoelectric signal detected by the first myoelectric sensor 120 ₁ or the second myoelectric sensor 120 ₂ . The myoelectric signal detected by the myoelectric sensor 120 ₁ or the second myoelectric sensor 120 ₂ may be transmitted to the server device 200 or the user device 300. In this case, it is sufficient for the memory unit 140 of the myoelectric device 100'to store a program that realizes the process of detecting the myoelectric signal (for example, the process of step S601 in FIG. 6), and the electrocardiographic signal is input from the myoelectric signal. It is not necessary to store at least a program that realizes the process of extraction (for example, the process of steps S602 and / or S603 of FIG. 6). As a result, the capacity of the memory unit 140 of the myoelectric device 100'can be reduced, and the processing by the processor unit 150 of the myoelectric device 100'can be simplified.

In the examples shown in FIGS. 1 to 10, the myoelectric devices 100 and 100', which are neckband type devices, have been described, but the form of the myoelectric devices 100 and 100'is not limited to this. The myoelectric device 100 can be in any form.

FIG. 11 shows an example of the form of the myoelectric device 100 ″ which is an alternative form of the neckband type myoelectric device 100, 100 ′. The myoelectric device 100 ″ is a neck strap type device that can be hung from the neck. The myoelectric device 100 ″ has the same components as the myoelectric devices 100, 100 ″.

The myoelectric device 100'' includes a housing 110 (first housing), a pair of measuring electrodes 116, 117 (a pair of second measuring electrodes), a second housing 118, and a neck strap 119. To prepare for. Since the configuration of the first housing 110 is the same as the configuration of the housing 110 shown in FIG. 5, the description thereof will be omitted here. Since the configuration of the pair of measurement electrodes 116 and 117 is the same as the configuration of the pair of measurement electrodes 116 and 117 shown in FIG. 8, the description thereof will be omitted here. The second housing 118 houses circuits (eg, a battery and associated circuits, etc.) required for the myoelectric device 100 ″.

When the user attaches the myoelectric device 100 by lowering the neck strap 119 from the neck, the pair of measuring electrodes 114, 115 arranged in the housing 110 is the rear part of the user's neck due to the weight of the second housing 118. The pair of measurement electrodes 116, 117 touches the skin on the left and right clavicle of the user.

In the example shown in FIG. 11, an example in which the myoelectric device 100'' includes a pair of measurement electrodes 116 and 117 has been described, but the pair of measurement electrodes 116 and 117 are omitted from the myoelectric device 100''. Is also within the scope of the present invention.

In the examples shown in FIGS. 1 to 11, the myoelectric devices 100, 100', 100'' having a pair of measuring electrodes arranged at the rear of the neck have been described, but the site where the pair of measuring electric powers are arranged is. , Not limited to the back of the neck. The pair of measuring electrodes are placed at any part of the body. The portion where the pair of measurement electrodes are arranged is preferably a portion where the user can easily attach the myoelectric device in order to arrange the pair of measurement electrodes. For example, the pair of measuring electrodes may be placed on the user's abdomen.

FIG. 12A shows an example of the form of the myoelectric device 100'''' which is an alternative form of the myoelectric device 100, 100', 100'', and FIG. 12B shows the myoelectric device 100'''' in the abdomen of the user. It shows how it was attached to.

The myoelectric device 100 ″ is a belt-type device that can be wrapped around the abdomen and worn as shown in FIG. 12B in order to arrange a pair of measurement electrodes on the abdomen. As used herein, the term "abdomen" refers to the portion between the human thoracic cavity and the pelvis. In FIG. 12A, the same components as those in FIG. 1 are given the same reference numbers, and the description thereof will be omitted here. The myoelectric device 100 ″ has the same configuration as the myoelectric device 100 shown in FIG.

The myoelectric device 100 ″ includes a housing 110 and belt portions 171 extending from both ends of the housing. In FIG. 12A, the center 110C of the housing 110 is shown located on the right side of FIG. 12A. The belt portion 171 is configured to be closely attached to the user. For example, the belt portion 171 may be attached in close contact with the user by providing an adjuster (not shown) capable of adjusting the length of the belt portion 171. For example, the belt portion 171 may be made of a stretchable material so as to be closely attached to the user.

An electromyographic sensor (not shown in FIGS. 12A and 12B) is built in the housing 110. The myoelectric sensor includes a reference electrode 113 and a pair of measurement electrodes 114 and 115. The pair of measurement electrodes 114 and 115 are provided on the housing 110 and are exposed on the outer surface of the housing 110, while the reference electrode 113 is provided on the belt portion 171 and is exposed on the outer surface of the belt portion 171. ing. The reference electrode 113 exposed on the outer surface of the belt portion 171 is connected to the myoelectric sensor inside the housing 110 by wire or wirelessly.

The user wears the myoelectric device 100 ″ by aligning the center 110C of the housing 110 with the center of the anterior part of the abdomen and wrapping the belt portion 171 around the abdomen. The user can easily wear the myoelectric device 100 "" as if he were wearing a belt. The belt portion 171 is configured such that the reference electrode 113 and the pair of measurement electrodes 114, 115 come into contact with the skin of the user's abdomen when the user wears the myoelectric device 100 ″. The user is not restricted in exercise by wearing the myoelectric device 100 ″ ″. Since the myoelectric device 100 ″ is configured so that the belt portion 171 is closely attached to the user, the myoelectric device 100 ″ is more closely attached to the user. Even if the user changes his / her posture, the myoelectric device 100 ″ can be in close contact with the skin of the abdomen and can continue to stably detect the myoelectric signal. The myoelectric device 100 ″ can stably detect the myoelectric signal even while the user is lying down and sleeping, for example.

Similar to the above-mentioned myoelectric device 100, the pair of measurement electrodes 114 and 115 of the myoelectric device 100'''is not arranged on the same muscle fiber existing at the site where the pair of measurement electrodes 114 and 115 come into contact with each other. ..

Further, the pair of measurement electrodes 114 and 115 of the myoelectric device 100'''' is the same as the above-mentioned myoelectric device 100, when the myoelectric device 100'''' is attached to the user, the pair of measurement electrodes 114 The angle θ formed by the line connecting 115 and the direction in which the muscle fiber of the muscle closest to the position where the pair of measurement electrodes 114 and 115 are arranged is 30 degrees or more, 45 degrees or more, 60 degrees or more, or. It can be preferably arranged to be 90 degrees. The closer θ is to 90 degrees, the more the S / N ratio of the myoelectric signal derived from the nearest muscle is significantly reduced at the position where the pair of measurement electrodes 114 and 115 are arranged, and the pair of measurement electrodes 114 and 115 are arranged. It is possible to relatively increase the S / N ratio of the myoelectric signal derived from the muscle at a position far from the position.

The pair of measurement electrodes 114, 115 of the myoelectric device 100'''' are located symmetrically with respect to the user's median plane in the user's abdomen when the myoelectric device 100''' is attached to the user. You may do so. This can be achieved, for example, by setting the distances from the center 110C of the housing 110 of the myoelectric device 100 ″ to the pair of measurement electrodes 114 and 115 to be the same distance, respectively. Alternatively, the pair of measuring electrodes 114, 115 of the myoelectric device 100'''' is asymmetrical with respect to the user's median plane in the user's abdomen when the myoelectric device 100''' is attached to the user. It may be located. This can be achieved, for example, by setting the distances from the center 110C of the housing 110 of the myoelectric device 100 ″ to the pair of measurement electrodes 114, 115 to different distances. For example, one of the pair of measuring electrodes 114 is provided at a position 20-60 mm, preferably 40 mm from the center 110C of the housing 110, and the other measuring electrode 115 of the pair of measuring electrodes is the housing. Provided at a position 130-170, preferably 150 mm from the center 110C of the 110, the myoelectric device 100 is asymmetrically located in the user's abdomen with respect to the user's median plane when worn by the user. .. In this way, the pair of measurement electrodes 114, 115 can be arranged at any angular position on the user's abdomen. For example, the angle between the pair of measurement electrodes 114 and 115 between the line passing through each electrode and the center of the user's body and the median plane in front of the coronal plane of the user is at a position of 45 degrees in the left-right direction. It may be arranged. Alternatively, for example, the angle formed by the measurement electrode 114 of one of the pair of measurement electrodes between the line passing through the electrode 114 and the center of the user's body and the median surface in front of the coronal surface of the user is in the left direction. The measurement electrode 115 of the pair of measurement electrodes is placed at a position of 5 to 25 degrees, preferably 15 degrees, from the line passing between the electrode 115 and the center of the user's body and the coronal surface of the user. It may be arranged at a position where the angle between the front center surface and the center surface is 55 to 75 degrees, preferably 65 degrees to the right. By arranging the pair of measurement electrodes 114 and 115 so as to be positioned asymmetrically with respect to the median plane of the user in this way, the shortest distance between the pair of measurement electrodes and the measurement target (for example, the heart) can be determined. , Can be different between electrodes. This causes a time difference between the myoelectric signal measured by one of the pair of measurement electrodes 114 and the myoelectric signal measured by the other measurement electrode 115 of the pair of measurement electrodes. This makes it possible to easily distinguish between the myoelectric signal to be measured and noise. By using a pair of measuring electrodes asymmetrically arranged with respect to the median plane, it is possible to obtain a clearer myoelectric signal than the myoelectric signal obtained from the pair of measuring electrodes arranged symmetrically with respect to the median plane. ..

Moreover, the cross section of the abdomen is generally elliptical and larger than the cross section of the substantially circular neck. Therefore, when the pair of measurement electrodes 114, 115 are arranged so as to be positioned asymmetrically with respect to the median plane, the myoelectric device 100'''' to be attached to the abdomen is the myoelectric device 100, 100', which is attached to the neck. Compared to 100'', the shortest distance between the pair of measurement electrodes and the measurement target (for example, the heart) can be made larger and different between the electrodes. This makes it possible to obtain a clearer myoelectric signal than the myoelectric devices 100, 100 ″, 100 ″ worn on the neck.

In the myoelectric devices 100, 100', 100'' worn on the neck, the myoelectric sensor detected not only the electrocardiographic signal but also the masticatory signal indicating the masticatory activity by the jaw muscle, but the myoelectric device worn on the abdomen. At 100'''', the myoelectric sensor can detect a walking signal indicating walking activity instead of the chewing signal. The gait signal indicating walking activity may include, for example, a myoelectric signal derived from the muscle of the thigh and a myoelectric signal derived from the muscle of the lower leg. The myoelectric device 100 ″ can extract an electrocardiographic signal and / or a walking signal from the detected signal by, for example, a process such as an extraction process based on the frequency described above.

The process by the myoelectric device 100 ″ is the same as the process shown in FIG. In the process by the myoelectric device 100''', in addition to the process shown in FIG. 6, as step S603', the processor unit 150 of the myoelectric device 100'''is a process of extracting the walking signal from the myoelectric signal. It may be further included. In this case, the processor unit 150 of the myoelectric device 100 ″ can also extract the walking signal from the myoelectric signal by performing appropriate processing on the myoelectric signal in step S603 ′. In step S603', the processor unit 150 of the myoelectric device 100'''in addition to or instead of performing appropriate processing on the myoelectric signal, for myoelectric signals other than the electrocardiographic signal. The walking signal can also be extracted by further processing.

The extracted electrocardiographic signal and / or walking signal can be used, for example, for the detection of potential illness and its precursors of the user and the observation and management of lifestyle, as well as the masticatory signal. This is because walking is related to exercise in the lifestyle. The electrocardiographic signal and / or the walking signal extracted by the myoelectric device 100 ″ is transmitted to, for example, a healthcare operator. The healthcare provider analyzes the electrocardiographic signal and / or the walking signal and uses it for monitoring the physical condition of the user. The healthcare business operator can provide, for example, a healthcare application to a user terminal and present the analysis result to the user through the healthcare application.

The myoelectric device 100 ″ can include a pressure sensor and / or a perimeter detection sensor in addition to the configuration shown in FIG.

The pressure sensor is a sensor capable of detecting the pressure applied to the myoelectric device 100 ″. Since the pressure applied to the myoelectric device 100'''' by the abdomen changes according to the user's breathing, the user's breathing is detected by detecting the change in the pressure applied to the myoelectric device 100''''. Can be detected.

The perimeter detection sensor is a sensor capable of detecting the perimeter when the myoelectric device 100 ″ is attached. Since the circumference of the myoelectric device 100'''' changes according to the user's breathing, the change in the circumference of the myoelectric device 100'''' when worn should be detected using a circumference detection sensor. Can detect the user's breathing.

Information about the detected breathing can be used, for example, to detect potential diseases of the user's respiratory system (eg, sleep apnea syndrome, etc.) and their precursors. Information about respiration detected by the myoelectric device 100 ″ is transmitted to, for example, a healthcare provider. Healthcare providers analyze breathing information and use it to detect illnesses in users. The healthcare business operator can provide, for example, a healthcare application to a user terminal and present the analysis result to the user through the healthcare application.

The electrode arrangement of the reference electrode 113, the pair of measurement electrodes 114, 115, or the pair of measurement electrodes 116, 117 in the above-mentioned example is an example, and other electrode arrangements are also within the scope of the present invention.

For example, in the myoelectric device 100'''', the reference electrode 113 may be located at the center (backbone portion) of the posterior part of the user's abdomen when the myoelectric device 100'''' is attached to the user. good. This can be achieved, for example, by making the distance from the center 110C of the housing 110 of the myoelectric device 100 ″ to the reference electrode 113 the same in the left-right direction. At this time, if the skin around the spine portion is raised, a gap is formed between the myoelectric device 100'''' and the spine portion when the myoelectric device 100'''' is attached, and the reference electrode 113 May cause poor contact with the skin. Such poor contact is caused, for example, so that the reference electrode 113 is positioned laterally from the center (backbone portion) of the rear part of the user's abdomen when the myoelectric device 100'''is attached to the user. It can be avoided by setting. For example, the reference electrode 113 may be provided at a position of 20 to 60 mm, preferably 40 mm, to the left or right from a position at the same distance in the left-right direction from the center 110C of the housing 110. As a result, the reference electrode 113 is displaced from the center (backbone portion) of the rear part of the user's abdomen when the myoelectric device 100 ″ is attached to the user. The reference electrode 113 can be placed at any angular position around the user's abdomen. For example, the reference electrode 113 has an angle of 5 to 25 degrees to the right or left between the line passing through the reference electrode 113 and the center of the user's body and the median plane posterior to the coronal plane of the user. It may be preferably arranged at a position of 15 degrees. Alternatively, poor contact between the reference electrode 113 and the skin can be avoided by changing the height of the reference electrode 113 so that it is in close contact with the spine instead of shifting the position of the reference electrode 113 in the left-right direction. can.

For example, in the example shown in FIG. 1, the reference electrode 113 and the pair of measurement electrodes 114 and 115 are located at the center of the housing 110 in the vertical direction, but the reference electrode 113 and the pair of measurement electrodes 114 and 115 are in the housing. It may be arranged so as to be offset in the vertical direction from the center of the 110. For example, the reference electrode 113 and the pair of measurement electrodes 114 and 115 may be displaced downward from the center of the housing 110 so as to be arranged near the bottom surface of the housing 110. At this time, an R is attached to the surface near the bottom surface where the reference electrode 113 and the pair of measurement electrodes 114 and 115 are arranged, and the shape is curved so as to follow the shape of the user's neck in the vertical direction. The 113 and the pair of measurement electrodes 114, 115 can be brought into close contact with the skin at the back of the user's neck. Further, in addition to or instead of adding an R to the surface near the bottom surface where the reference electrode 113 and the pair of measurement electrodes 114 and 115 are arranged, the body contact surface of the housing 110 is provided in the circumferential direction of the user's neck. The concavely curved shape along the shape prevents the formation of a gap between the neck and the myoelectric device 100, and the reference electrode 113 and the pair of measurement electrodes 114 and 115 are attached to the rear part of the user's neck. Can be more closely attached to the skin. This makes it possible to stably detect the myoelectric signal.

For example, in the example shown in FIG. 12A, the reference electrode 113 is provided on the belt portion 171 so as to be exposed on the outer surface of the belt portion 171 and the pair of measurement electrodes 114 and 115 are provided on the housing 110 to provide the housing 110. However, in place of or in addition to the reference electrode 113, one or both of the pair of measurement electrodes 114, 115 is provided on the belt portion 171 of the belt portion 171. It may be arranged so as to be exposed on the outer surface. Alternatively, the reference electrode 113 may be provided on the housing 110 like the pair of measurement electrodes 114 and 115 so as to be exposed on the outer surface of the housing 110.

As in the example described above, it is preferred that the myoelectric device comprises only three electrodes (reference electrode 113, pair of measurement electrodes 114, 115). The myoelectric device of the present invention can detect the myoelectric signal in a manner capable of extracting the myoelectric signal to be measured even with a small number of electrodes due to the unique electrode arrangement. However, the number of electrodes of the myoelectric device of the present invention is not limited to this. The myoelectric device of the present invention can be provided with any number of electrodes as long as the effects of the present invention can be obtained. For example, the myoelectric device 100 ″ may include a pair of second measurement electrodes 116, 117, similar to the myoelectric devices 100 ″ and 100 ″. Alternatively, the myoelectric device 100 ″ may include more measuring electrodes.

The present invention is not limited to the above-described embodiment. It is understood that the invention should be construed only by the claims. It will be understood by those skilled in the art that from the description of a specific preferred embodiment of the present invention, an equivalent range can be implemented based on the description of the present invention and common general technical knowledge.

The present invention is useful as providing a system for at least detecting an electrocardiographic signal indicating myocardial activity.

10 System 100, 100', 100'', 100''' Myoelectric device 110 Housing 111, 112 Arm 113 Reference electrode 114, 115 Pair of measurement electrodes 116, 117 Pair of measurement electrodes 118 Second housing 119 Neck strap 120 Myoelectric sensor 130 AD conversion unit 140 Memory unit 150 Processor unit 160 Transmission unit 171 Belt unit 200 Server device 300 User device 400 Network

Claims (18)

A system for detecting at least an electrocardiographic signal indicating myocardial activity.
A detection means for detecting a myoelectric signal indicating muscle activity of a body, wherein the detection means includes a first myoelectric sensor and a second myoelectric sensor, and the first myoelectric sensor is used. The second myoelectric sensor is configured to detect a myoelectric signal having a high S / N ratio of the electrocardiographic signal from the skin of the neck of the user, and the second myoelectric sensor is the S / of the electrocardiographic signal from the skin of the neck of the user. The first myoelectric sensor and the second myoelectric sensor are configured to detect a myoelectric signal having a low N ratio, and the first myoelectric sensor and the second myoelectric sensor are not arranged on the same muscle fiber .
It is an extraction means for extracting at least an electrocardiographic signal and a mastication signal indicating chewing activity from the myoelectric signal, and the extraction means is the electrocardiogram from the myoelectric signal detected by the first myoelectric sensor. The time of the number and the time of the chewing signal and the noise are determined, and among the myoelectric signals detected by the second myoelectric sensor, the signal of the time determined as the time of the electrocardiographic signal is used. Of the myoelectric signals detected by the second myoelectric sensor, which is determined to be an electrocardiographic signal, the signal at the time determined as the time of the mastication signal and noise is regarded as the mastication signal and noise. By determining, it comprises an extraction means configured to distinguish and extract the electrocardiographic signal from the mastication signal and noise from the myoelectric signal detected by the second myoelectric sensor. system. The first myoelectric sensor includes a pair of first measuring electrodes.
The system further comprises a mounting means for mounting the detecting means to the user .
In the mounting means, when the detecting means is mounted on the user, one of the pair of first measurement electrodes comes into contact with the specific first portion of the user, and the pair. The other of the first measuring electrodes of the above contacts a specific second portion of the user, and the pair of first measuring electrodes are placed on the same muscle fiber present in the contacting portion. The system according to claim 1, which is configured not to be. The mounting means is configured such that when the detecting means is mounted on the user, the pair of first measuring electrodes are arranged asymmetrically with respect to the median plane of the user. Item 2. The system according to item 2. The system of claim 2 or 3, wherein the particular first part of the user and the particular second part of the user are parts of the skin at the back of the user's neck. The particular first part of the user is the part of the skin at the back of the user's neck and the particular second part of the user is the part of the skin on the clavicle of the user. The system according to claim 2 or 3, which is a part. The second myoelectric sensor includes a pair of second measuring electrodes.
In the mounting means, when the detecting means is mounted on the user, one of the pair of second measurement electrodes comes into contact with a specific third portion of the user, and the pair. The other of the second measuring electrodes of the above is in contact with a specific fourth portion of the user, and the pair of second measuring electrodes are placed on the same muscle fiber present in the contacting portion. The system according to any one of claims 2 to 5, which is configured not to be used. The mounting means is configured such that when the detecting means is mounted on the user, the pair of second measuring electrodes are arranged asymmetrically with respect to the median plane of the user. Item 6. The system according to item 6. The system of claim 6 or 7, wherein the particular third part of the user and the particular fourth part of the user are parts of the skin on the clavicle of the user. The particular third part of the user is the part of the skin at the back of the user's neck and the particular fourth part of the user is the part of the skin on the clavicle of the user. The system according to claim 6 or 7. A system for detecting at least an electrocardiographic signal indicating myocardial activity.
A detection means for detecting a myoelectric signal indicating muscle activity of a body, wherein the detection means includes a first myoelectric sensor and a second myoelectric sensor, and the first myoelectric sensor is used. The second myoelectric sensor is configured to detect a myoelectric signal having a high S / N ratio of the electrocardiographic signal from the skin of the abdomen of the user, and the second myoelectric sensor is the S / of the electrocardiographic signal from the skin of the abdomen of the user. The first myoelectric sensor and the second myoelectric sensor are configured to detect a myoelectric signal having a low N ratio, and the first myoelectric sensor and the second myoelectric sensor are not arranged on the same muscle fiber.
It is an extraction means for extracting at least an electrocardiographic signal and a walking signal indicating walking activity from the myoelectric signal, and the extracting means is the electrocardiographic signal from the myoelectric signal detected by the first myoelectric sensor. The time of the number and the time of the walking signal and the noise are determined, and among the myoelectric signals detected by the second myoelectric sensor, the signal of the time determined as the time of the electrocardiographic signal is used. Among the myoelectric signals detected by the second myoelectric sensor, the signal at the time determined as the time of the walking signal and the noise is determined to be the walking signal and the noise. By determining, the extraction means configured to distinguish and extract the electrocardiographic signal, the walking signal and the noise from the myoelectric signal detected by the second myoelectric sensor.
The system. The first myoelectric sensor includes a pair of first measuring electrodes.
The system further comprises a mounting means for mounting the detecting means to the user.
In the mounting means, when the detecting means is mounted on the user, one of the pair of first measurement electrodes comes into contact with the specific first portion of the user, and the pair. The other of the first measuring electrodes of the above contacts a specific second portion of the user, and the pair of first measuring electrodes are placed on the same muscle fiber present in the contacting portion. The system according to claim 10, which is configured so as not to be. The mounting means is configured such that when the detecting means is mounted on the user, the pair of first measuring electrodes are arranged asymmetrically with respect to the median plane of the user. Item 11. The system according to item 11. The second myoelectric sensor includes a pair of second measuring electrodes.
In the mounting means, when the detecting means is mounted on the user, one of the pair of second measuring electrodes comes into contact with a specific third portion of the user, and the pair. The other of the second measuring electrodes of the above is in contact with a specific fourth portion of the user, and the pair of second measuring electrodes are placed on the same muscle fiber present in the contacting portion. The system according to any one of claims 11 to 12, which is configured not to be used. The mounting means is configured such that when the detecting means is mounted on the user, the pair of second measuring electrodes are arranged asymmetrically with respect to the median plane of the user. Item 13. The system according to item 13. The system of claim 11 or 12 , wherein the particular first part of the user and the particular second part of the user are parts of the skin on the abdomen of the user. The system is a device configured to be wearable by the user.
The system according to any one of claims 1 to 15 , wherein the device includes the detection means and the extraction means. The system includes a device configured to be wearable to the user and a server device configured to be able to communicate with the device over a network.
The system according to any one of claims 1 to 15 , wherein the device includes the detection means and the server device includes the extraction means. The system includes a device configured to be wearable to the user and a user device configured to be able to communicate with the device over a network.
The system according to any one of claims 1 to 15 , wherein the device includes the detection means and the user device includes the extraction means.

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