KR20190075260A - Emg measuring band for optimizing electrode position - Google Patents

Abstract

The present invention relates to an electromyogram band with an optimized electrode position which uses a small number of electrodes if possible even when relative positions of a plurality of muscles existing in a wearing body portion are unspecified to accurately detect desired electromyograms of the plurality of muscles, operates at low power as a wearable device, and obtains and transmits optimal electromyograms within a wireless transmission capability. The electromyogram band with an optimized electrode position includes a main electrode pair (11) for a first target muscle, and a plurality of pairs (12) of sub electrodes for second target muscles existing on unspecified positions with respect to the first target muscle. An optimal pair among the plurality of pairs (12) of sub electrodes is used. Research associated with the present invention was carried out by receiving support for the design global expert corporation support project (bio-signal composite monitoring wireless wearable band technology development and design capacity enhancement, project number: 10077813) of the Korean ministry of trade, industry and energy.

Description

EMG MEASURING BAND FOR OPTIMIZING ELECTRODE POSITION "

The present invention accurately detects electromyograms of desired multiple muscles using as few electrodes as possible, despite the relative location indefinite of multiple muscles present in the body part of the wearer, and as a wearable device, The present invention relates to an electromyogram band in which an electrode position that can be configured to transmit and receive an optimal electromyogram in an optimal position is optimized.

The research related to the present invention has been carried out by the Ministry of Commerce, Industry and Energy in the promotion of a global design specialized enterprise (bio-signal composite monitoring, wireless wearable band technology development and design capability enhancement, bio-signal composite monitoring wireless wearable band technology development and design capacity enhancement, ).

The electromyogram is a signal obtained by detecting the current change caused by the movement of the muscles. The electromyogram is obtained as a difference signal between potential signals detected at each electrode by bringing at least two spaced apart electrodes into contact with the skin of the muscular region.

Since these electromyograms must be obtained during exercise using muscles, they are obtained by installing electrodes in a wearable band type wearable body and are used for analyzing the exercise situation.

However, in order to accurately analyze the exercise situation, it is necessary to analyze and obtain the electromyogram of all the muscles used in the exercise, but it is difficult to obtain the electromyogram of all the muscles practically.

Thus, in order to obtain as many EMGs as possible during exercise, Japanese Patent Application No. 10-1501661 allows a plurality of EMG sensors to be arranged along the circumferential direction of the band.

However, the position of the muscles can not be specified because the physical conditions vary from person to person, so that the number of electromyography sensors is more than necessary in the registration number 10-1501661.

In addition, since the wearable device must be slim to be worn without inconvenience and operate at low power so as to be able to be used for a long time, the EMG is configured to be wirelessly transmitted to the smartphone in which the analysis program is installed and operated, Should be configured to perform with low power. Therefore, a limited transmission rate must be provided for low power wireless transmission, and Patent No. 10-1501661 lacks measures for this.

KR 10-1501661 B1 2015.03.05.

Therefore, it is an object of the present invention to provide an electromyogram of a plurality of muscles which are provided with an electrode at a minimum position but which are not positionally specified, and which can be used as a wearable device, And to provide an electromyogram band in which an electromyogram of a muscle can be accurately obtained and an electrode position capable of wireless transmission can be optimized.

In order to achieve the above object, the electromyogram band according to the present invention includes a pair of main electrodes 11 and a pair of main electrodes 11, which are positioned by a mark 16 so as to be in contact with a first target muscle 2 of a body part 1 to be worn, , A plurality of sub electrode pairs (12) arranged at intervals along the circumferential direction so as to be dispersed and contacted in a region where second target muscles having a position and a specific position are present with a first target muscle as a reference point in a body part (1) And acquires an electromyogram signal detected through the first target muscle 2 and the second target muscle 3 by the signal processor 13 and transmits the electromyogram signal through the wireless communication module 14.

The signal processing unit 13 is configured to transmit the electromyogram signal of the second target muscle 3 to be transmitted in real time together with the electromyogram signal of the first target muscle 2 within the limit of the limited real time wireless transmission capability of the wireless communication module 14 Electrode pair 12 according to the magnitude of the EMG signal detected in the sub-electrode pair 12 of the first sub-electrode pair 12.

According to the embodiment of the present invention, the signal processor 13 uses the main electrode pair 11 as an in-phase signal drive electrode for applying the in-phase signal when the sub electrode pair 12 is selected, and the main electrode pair 11 And the selected sub-electrode pair 12 is used as the in-phase signal drive electrode when the electromotive force signal is detected.

According to the embodiment of the present invention, the signal processing unit 13 intermittently performs the selection process of the sub-electrode pair 12 while detecting a signal with the main electrode pair 11 and the selected sub electrode pair 12, The sub electrode pair 12 to be selected and the in-phase signal drive electrode can be changed.

According to the embodiment of the present invention, when the frequency component of the commercial electricity detected through the sub-electrode pairs before the selection of the sub-electrode pairs is less than a predetermined lower limit, Phase signal to the main electrode pair 11, the correction is carried out in accordance with the magnitude of the in-phase signal detected for each electrode to eliminate the impedance unbalance between the electrodes for each sub-electrode pair, And an inphase in-phase signal is applied through the in-phase signal drive electrode defined in the sub-electrode pair before the electromotive force signal is obtained by the selected sub-electrode pair 12, and then the impedance unbalance between the electrodes is corrected with respect to the main electrode pair 11 Correction is performed according to the size of the in-phase signal detected for each electrode.

According to the embodiment of the present invention, the signal processing unit 13 excludes, from the selection target, those in which the in-phase signal remaining in the electromyogram signal detected in the plurality of sub electrode pairs 12 exceeds the predetermined upper limit value.

According to the embodiment of the present invention, the signals detected by the two electrodes at the mounting position are individually amplified in the positions where the main electrode pair 11 and the sub electrode pairs 12 are installed, Processing means (113, 123) for acquiring two-channel digital data, wherein the means for amplifying relatively large amplified detection signals is different from that of the signal processing means 13) normalize the two-channel digital data so that the same-phase noise power is equalized, and then combine the same so that the common-mode noise is removed to obtain an EMG signal.

The present invention configured as described above enables precise detection of the electromyogram of the first target muscle (2) by wearing the first target muscle (2) most important among the plurality of muscles to detect the electromyogram, Electromyograms of the second target muscle 3 are detected in a plurality of the sub-electrode pairs 13 arranged in the region where the second target muscle 3 is present. Therefore, The number of pairs can be reduced to a minimum, and only the electrode pair at the optimum position is used within the limit of the real-time detection capability, so that it can be used as a wearable device capable of low-power operation and slimness.

1 is a perspective view of an electromyogram band 10 according to a first embodiment of the present invention;
FIG. 2 is a view showing a state in which an electromyogram band 10 according to a first embodiment of the present invention is worn on a body part 1 after connected to a receiving terminal 20 composed of a smart phone through short-range wireless communication State of use.
Fig. 3 schematically shows the type and position of the muscles of the body part 1 wearing the electromyogram band 10; Fig.
4 is an electric circuit block diagram of the electromyogram band 10 according to the first embodiment of the present invention.
5 is a detailed block diagram of the signal processing unit 13 shown in Fig.
6 is a flowchart of an electromyogram measurement method performed by the signal processing unit 13. Fig.
FIG. 7 is a configuration diagram showing a modified configuration of the first detection unit 1331; FIG.
8 is a perspective view of an electromyogram band according to a second embodiment of the present invention;
9 is a configuration diagram of preprocessing sections 113 and 123 in an electromyogram band according to the second embodiment of the present invention.
10 is a detailed block diagram of the signal processing unit 13 in the electromyogram band according to the second embodiment of the present invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Hereinafter, preferred embodiments of the present invention will be described with reference to the accompanying drawings.

1 is a perspective view of an electromyogram band 10 according to a first embodiment of the present invention. 1, the electric signal lines 111 and 121 embedded in the electromyogram band 10 and the signal processing unit 13, the wireless communication module 14, and the battery (not shown) accommodated in a space in a section of the electromyogram band 10, A cover 16 for forming a surface on the surface of the electromyogram band 10 corresponding to the main electrode pair 11 and indicating the position of the main electrode pair 11, Some of the sub electrode pairs 12c and 12d, which are hidden and hidden from the sub electrode pairs 12 (12a, 12b, 12c, and 12d), are indicated by dotted lines.

Fig. 2 is a state diagram showing a state in which the user walks the electromyogram band 10 shown in Fig. 1 while wearing the body part 1. Fig. According to the use state diagram shown in Fig. 2, the body part 1 wearing the EMG band 10 is upper arm, and EMG signals of the upper arm muscles are detected in the EMG band 10 during dumbbell exercise, To the receiver 20, thereby allowing the receiver 20 to analyze the EMG signal.

3 is a schematic view showing a section of the body part 1 wearing the electromyogram band 10. Since the body part 1 wearing the electromyogram band 10 is a upper arm, a plurality of muscles present in the upper arm are schematically shown in Fig.

The electromyogram band 10 according to the embodiment of the present invention is formed in a band shape having both ends so that the body part 1 to be measured for electromyogram is wrapped roundly and then the fastening means 17 provided at both ends are mutually connected So that it can be fixed to the body part 1, and the elastic band 17 can be partly stretched and stretched, so that it can be worn on the body part 1 having a different thickness.

Although the fastening means 17 at both ends are shown to be mutually engaged by the engagement of the projections and the grooves, in order to prevent easy disengagement, the fastening means 17 is composed of a magnet having a magnetic force so as to stably maintain the engagement state Or may be replaced with a different fastening means known in the art.

Although the elastic band 17 is shown to be provided in a section where the electric signal lines 111 and 121 are not embedded, the electric signal lines 111 and 121 can be stretched and contracted, It is also applicable to a period in which the electric signal lines 111 and 121 are buried.

An internal space is formed in one portion of the electromyogram band 10 to accommodate the signal processing unit 13, the wireless communication module 14, and the battery 15. [

A main electrode pair (11) is provided on an inner surface of the wearer's body part (1) to be visually recognizable by a mark (16) on the surface, and a pair of main electrodes And a plurality of sub electrode pairs 12 arranged at intervals.

The main electrode pair 11 is composed of two electrodes 112 connected to the signal processing unit 13 by electric signal lines 111 embedded in the electromyogram band 10 along the circumferential direction. The muscles of the body part 1 wrapped by the electromyogram band 10 exist in a direction penetrating the inside of the electromyogram band 10 wrapped around the electromyogram band 10 so that the two electrodes 112 of the main electrode pair 11 are spaced apart To place them along the longitudinal direction of the muscles.

Here, the mark 16 indicating the position of the main electrode pair 11 is provided on the outer surface of the position where the main electrode pair 11 is provided, so that the number of the body parts 1 covered with the electromyogram band 10 The main electrode pair 11 can be brought into contact with the muscle in accordance with a desired specific muscle position.

Referring to FIG. 3, the main biceps twin muscle is most important for analyzing the exercise situation at the time of dumbbell exercise, and the main electrode pair 11 is divided into the first target muscle 2 (16) so as to be in contact with the skin covering the skin (16).

Thus, the electromyogram signal generated in the first target muscle 2 can be accurately detected through the main electrode pair 11.

Since the first target muscle 2 differs depending on the kind of exercise and the body part to be worn, the first target muscle 2 determined according to the type of exercise and the body part to be worn is prepared in the manual and the EMG band 10 ) Users should refer to the instruction manual and make sure that they are used according to the type of exercise and the area of wear.

However, in order to accurately analyze the physical condition according to the exercise, it is preferable to obtain an electromyogram signal for a large number of muscles used in the exercise, if possible, and perform a comprehensive analysis together with the electromyogram signal of the first target muscle (2).

For this reason, in the muscles present in the body part 1 wrapped with the electromyogram band 10, the remaining muscles other than the first target muscle 2 are defined as the second target muscles 3, And an electromyogram signal is obtained by the plurality of sub-electrode pairs (12: 12a, 12b, 12c, 12d).

Each of the sub electrode pairs 12 (12a, 12b, 12c, 12d) also penetrates two electrodes 122 connected to the signal processing unit 13 by the embedded electric signal line 121 like the main electrode pair 11 But is different from the main electrode pair 11 in the installation position and is not intended to be matched to the position of the second target muscle 3 artificially.

Since the position of the second target muscle 3 with the first target muscle 2 as a reference point is different for each individual and the body part, even if the position of the first target muscle 2 is specified, the position of the second target muscle 3 Is difficult to specify.

In the case where the body part 1 worn as shown in FIG. 3 is upper-arm, except for the upper-arm two-legged muscle defined by the first target muscle 2, the upper arm is divided into three upper arms, Muscles such as muscles inside the muscles, muscles inside the upper arm and the upper arm are present. Of these muscles, one or more second target muscles 3 can be defined, but the position of the second target muscles 3 differs depending on the difference in the individual upper arm thickness.

However, in the case of detecting the electromyogram by wearing on the body parts such as the lower arm, the upper leg, and the lower leg, the second target muscle 3 with the first target muscle 2 as the reference point It is difficult to specify the position, and there may be one muscle or two or more muscles to be determined as the second target muscle 3 for each body part.

Thus, the plurality of sub electrode pairs 12 (12a, 12b, 12c, and 12d) are spaced apart from the main electrode pairs 11 in the circumferential direction and spaced apart from each other, It is expected that there will be a possibility to obtain an accurate EMG signal in close proximity.

At this time, since the region in which the second target muscle 3 exists (or a part of the wrapped portion) can be roughly determined with the first target muscle 2 as a reference point, (Or a part of the wrapping portion) of the sub-electrode pairs 12 in a distributed manner.

As will be described later, the signal processing unit 13 selects among the plurality of sub-electrode pairs 12 (12a, 12b, 12c, and 12d) capable of obtaining the electromyogram signal within the limits of the real- The electromyogram signal of the second target muscle 3 by the first target muscle 2 and the selected sub electrode pair 12 by the main electrode pair 11 is acquired in real time and then transmitted through the wireless communication module 14 do.

As described above, when the contact position of the main electrode pair 11 is specified and then the sub electrode pair 12 is selected to simultaneously detect the electromyograms of a plurality of muscles, It is possible to greatly reduce the number of sub-electrode pairs and to simplify the configuration of the EMG band and to obtain and analyze an optimal electromyogram signal under a limited condition of low power operation and wireless communication capability limit as a wearable device.

On the other hand, since the region where the second target muscle 3 is set as the reference point of the first target muscle 2 differs for each body part, the plurality of sub electrode pairs 12 are located in the existing region of the second target muscle 3 It is also conceivable to separately manufacture the electromyogram bands 10 for the parts of the body to be worn so that they are arranged to be aligned with each other. However, one type of electromyogram band 10 in which the plurality of sub electrode pairs 12 are arranged in consideration of the second target muscle 3 at different wearing positions is manufactured and used for various body parts, It is convenient to reduce the cost of purchasing the product.

For example, in the case of the upper arm shown in FIG. 3, the second target muscle (3) is selected as the second target muscle (3) for the upper limb and the upper limb and the upper limb for the upper limb and the upper limb is statistically determined Electrode pairs 12 are provided so as to concentrate on the second target muscle 3 and the sub-electrode pairs 12 to increase the probability that the electromotive force signals of the second target muscle 3 can be detected at a sufficiently large power. In addition, sub-electrode pairs are not used in the section between the boundary of the area where the main electrode pairs 11 are provided and the boundary between the areas where the plural sub-electrode pairs 12 are provided. Therefore, And the number of the sub-electrode pairs 12 is reduced accordingly.

The signal processing unit 13 is operated by the electric power of the battery 15. The signal processing unit 13 receives the one channel electrophoresis signal by the main electrode pair 11 and the plurality of channel electromyogram signals by the plural pairs of sub- May be transmitted through the wireless communication module 14.

However, the battery 15 is built in the electromyogram band 10, which is a wearable device, and has a limited power supply capability as means for supplying required power. Accordingly, it is preferable that the electromyogram band 10 is constructed so as to be capable of low-power operation.

In addition, since the EMG signal of a plurality of channels detected by the EMG band 10 is transmitted in real time, the receiving terminal 20 can analyze the muscle state during exercise in real time, And has a more limited real-time wireless transmission capability when employing a low-power wireless communication technology.

Generally, the receiving terminal 20, which transmits EMGs acquired during a workout in the wearable device, uses a smart phone equipped with an EMG analysis application, so that it is connected to the receiving terminal 20 by Bluetooth over a short distance. At this time, It uses Bluetooth 4.0 (BLE: Bluetooth Low Energy, low power Bluetooth) the most.

In general, according to Bluetooth 4.0 standard, 4 ~ 6 packets of 20 bytes size can be transmitted in a connection interval period. As a concrete example, the iPhone 5 can provide a transmission speed of 32 kbps by 30 ms connection interval and 6 packet transmission, ms connection interval and 4-packet transmission, the transmission speed can be 84kbps. Actually, it is used with a transmission speed of 16kbps ~ 24kbps for stable operation.

The transmission rate is also limited by the number of data bits and the sampling period applied to acquire the electromyogram signal with sufficiently precise digital data.

Consequently, in order to meet low power operation, real-time transmission and data precision, it is preferable to limit EMG signals for two to four muscles, i.e., two to four channel wireless transmissions.

Further, when the electromyogram band 10 is configured to acquire a living body signal other than the EMG signal or a motion signal (acceleration / velocity / position signal) together with the EMG and transmit it in real time, the wireless communication speed is further restricted. To overcome these limitations, Bluetooth 4.2 or later versions can be used, though the power consumption is relatively large, but the transmission speed is more than several hundred Kbps. However, there is still a limitation in the transmission speed. In the case of operating in the low power mode to reduce the power consumption The transmission speed must be further reduced.

Even if a plurality of sub-electrode pairs 12 are provided to obtain an electromyogram signal of the second target muscle 3, the first target muscle 2 obtained from the main electrode pair 11, The electromyogram signal of the second target muscle 3 to be transmitted together with the electromyogram signal of the sub-electrode pair 12 should be obtained.

The signal processing unit 13 performs a general control operation for this purpose.

The signal processing unit 13 will be described with reference to the electric circuit block diagram shown in Fig. 4 and the signal processor 13 shown in Fig. 5 with reference to the detailed block diagram.

The signal processing unit 13 includes a first switch unit 131 for selecting any one of a plurality of sub electrode pairs 12a, 12b, 12c and 12d, A second switch portion 132 for selecting any one of all electrode pairs including the main electrode pair 12 (12a, 12b, 12c, 12d) And acquires the power of the inphase signal or the inphase signal through the electromyogram signal acquiring section 133 and the electromyogram signal acquiring section 133 for acquiring the electromyogram signals through the pair 12 and transmitting them through the wireless communication module 14 An in-phase signal applying unit 135 for applying an in-phase signal through an electrode pair selected by the second switch unit 132, 2 switch 132, and controls the electromyogram acquisition process and the in-phase signal application process. It is configured to.

5, the electromyogram signal acquisition unit 133 includes a first detection unit 1331 that is directly connected to the main electrode pair 11 to detect an EMG signal of the first target muscle 2, A second detection unit 1332 connected to the selected sub electrode pair 12 to detect an electromyogram signal of the second target muscle 2 and an electromyogram signal of the first target muscle 2 detected, And a packet generating unit 1333 for generating a packet for wirelessly transmitting the electromyogram signal of the second target muscle 2 and transmitting the generated packet through the wireless communication module 14. [

The first detection unit 1331 and the second detection unit 1332 individually amplify the analog signals input through the two electrodes using the amplifiers G and then perform a differential operation using a differential operation converter (ADC) Thereby obtaining an electromyogram signal as digital data. Here, the amplifier G is configured to control the amplification degree by the control unit 136 in order to eliminate the impedance imbalance between the electrodes. The differential operation converter (ADC) is constructed by integrating the differential operator and the analog - to - digital converter.

The inphase signal acquisition unit 134 has a function of detecting the power of the in-phase signal or the inphase signal in the analog signal input to the first detection unit 1331 and the second detection unit 1332 and the function of detecting the power of the first detection unit 1331 and the second detection unit 1332 And a function of detecting the power of the residual in-phase signal in the digitized EMG signal output from the detection unit 1332. [ The analog signal to be detected is delivered to the in-phase signal applying unit 135, and the power of the detected in-phase signal is transmitted to the control unit 136.

The second switch unit 132 may be connected to only one of the two electrodes of each electrode pair, but may be connected to two electrodes at the same time.

The operation of the signal processing unit 13 controlled by the control unit 136 will be described with reference to the flow chart of the EMG measurement method shown in Fig.

First, the first switch unit 131 is controlled to receive a signal from any one of the plurality of sub electrode pairs 12 to detect the in-phase signal power P of the signal before being processed by the second detection unit 1332 (step S10 ).

If the detected in-phase signal power P is less than the predetermined lower limit value P _LOW (S11), it is determined that the in-phase signal by commercial electric power having a frequency of 60 Hz (or 50 Hz) Phase signal to the human body via the main electrode pair 11 (S12). To this end, the in-phase signal applying unit 135 applies the in-phase signal through the main electrode pair 11 by connecting the in-phase signal applying unit 135 to the main electrode pair 11 by controlling the second switch unit 132 .

The in-phase signal drive electrode refers to an electrode that artificially generates and applies in-phase signals by itself. Here, an artificial in-phase signal does not necessarily have a commercial electric frequency.

On the other hand, the in-phase signal drive electrode may be an electrode for a right leg drive (RLD) that amplifies and applies in-phase signals that can be detected through the in-phase signal acquisition unit 134, When the in-phase signal of the component is sufficiently high above the lower limit value (P _LOW ), it is used as a right-hand drive circuit in obtaining the EMG signal in the following.

While the in-phase signal is detected in the sub-electrode pair 12 as described above, the first detection unit 1331 is not activated, only the second detection unit 1332 is activated, and the first switch unit 131 is controlled, (12) are sequentially selected one by one to perform a correction operation for eliminating the impedance unbalance (S20).

Impedance imbalance is caused by the impedance imbalance of the two electrodes and the impedance imbalance of the two electrical signal lines connecting the two electrodes to the second detector 1332. The gain of the amplifier (G) of the second detector 1332 is adjusted by detecting the magnitude of the in-phase signal input through the two electrodes by the in-phase signal obtaining unit 134 and by using the same size of the in- Or the impedance of the amplifier (G) of the second detector 1332 is adjusted so that the in-phase signal power remaining in the digital EMG signal output from the second detector 1332 becomes smaller than a predetermined magnitude, And performs a correction operation. Here, the amplification degree of the amplifier G obtained for each of the sub electrode pairs 12 is stored so as to be applicable to the sub electrode pairs 12 in the following description.

Next, while applying the correction information for eliminating the impedance unbalance to each of the sub-electrode pairs 12, the first switch unit 131 is controlled to sequentially select the sub-electrode pairs 12 one by one, After detecting the electromyogram signal (S30), the sub electrode pair 12 is selected in accordance with the detected electromyogram signal (S31). In this process, a preliminary exercise is performed by a separate guide means for guiding the preliminary exercise, thereby obtaining an electromyogram signal generated according to the preliminary exercise.

The selection criterion is set such that the number of remaining channels excluding the channel to be allocated to the main electrode pair 11 is maximized within the limited real time wireless transmission capability of the wireless communication module 14, The first selection criterion for selecting the number of the electromyogram signals in a descending order according to the magnitude of the detected electromyogram signal (i.e., power or energy), and the first selection criterion for selecting the number of the remaining electromyogram signals And a second selection criterion for excluding from the selection that the size of the in-phase signal exceeds a predetermined upper limit value. Of course, a sub-electrode pair is selected by applying a first selection criterion among those excluded by applying a second selection criterion.

That is, the main electrode pair 11 is temporarily used as an in-phase signal drive electrode to solve the impedance unbalance problem of each sub-electrode pair, and after obtaining an electromyogram accurately through each sub-electrode pair, Of the sub-electrode pairs.

By selecting the sub-electrode pairs according to such a selection criterion, it is possible to exclude the sub-electrode pairs in which the electrode contact state is poor and the electromyogram signal is difficult to obtain accurately, and the electromyogram signal is strongest nearest to the second target muscle 3 It is possible to select a sub electrode pair that can be obtained with a signal of an accurate pattern.

After the sub-electrode pair is selected, the selected sub-electrode pair is connected to the second detection unit 1332 by controlling the first switch unit 131. If the in-phase signal is weakly detected (S40) , Controls the second switch unit 132 to designate any one of the unselected sub-electrode pairs as the in-phase signal drive electrode, and activates the in-phase signal applying unit 135 to apply the in-phase signal through the designated sub-electrode pair .

Here, it is preferable that the sub-electrode pair designated as the in-phase signal drive electrode has the weakest electromyogram signal among a plurality of sub-electrode pairs. Of course, it is better to designate the in-phase signal drive electrode, except that the residual in-phase signal of the electromyogram signal to be detected is large.

Thereafter, a correction operation for eliminating the impedance unbalance is performed on the main electrode pair 11 (S50). That is, by using the sub-electrode pair as the in-phase signal drive electrode, it is possible to obtain the amplification of the amplifier G of the first detection unit 1331 for eliminating the impedance unbalance between the two electrodes provided in the main electrode pair 11.

The first detection unit 1331 obtains the electromyogram signal of the first target muscle 2 through the main electrode pair 11 and the second detection unit 1332 obtains the electromyogram signal of the selected target muscle 2 Since the electromyogram signal of the second target muscle 2 is obtained through the electrode pair 12, these electromyogram signals are acquired, packets are generated, and wireless transmission is performed (S60).

That is, while the sub-electrode pair 12 closest to the second target muscle 3 is selected during the full-scale exercise, the unselected sub-electrode pairs are used as in-phase signal drive electrodes, The electromyogram can be obtained with a signal of an accurate pattern.

The controller 136 may perform a calibration process (S20) for eliminating the impedance unbalance for each sub-electrode pair, and a calibration process (S20) for adjusting the position of the electromyogram band 10, A step S51 of designating the in-phase signal drive electrode or a step S50 of correcting the impedance unbalance of the main electrode pair is performed intermittently during the exercise (steps S30 and S31) Thereby enabling to change the sub electrode pair 12 to be selected and the in-phase signal drive electrode, as well as to compensate for fluctuating impedance unbalance.

In the meantime, although only one sub electrode pair 12 is shown in the accompanying drawings, it is possible to select two or more sub electrode pairs 12 within a range allowed by the real time wireless transmission capability of the wireless communication module 14 In this case, the first switch unit 131 allows two or more sub-electrode pairs 12 to be selected at the same time, and the second detecting unit 1332 is also provided with the number of the selected sub-electrode pairs 12 To-one correspondence with the selected sub electrode pairs 12. 3, among the remaining muscles except for the first target muscle 2, a long-forked and a long-forearmed limb are defined as a second target muscle 3, and four sub-electrode pairs 12a, 12b, 12c, and 12d, it is possible to select the sub-electrode pair 12a that can obtain the electromyogram signal with the greatest intensity in the vicinity of the upper arm and the longer arm, It is possible to select the sub electrode pair 12c which can obtain the EM wave signal of the next order magnitude close to the proximal branch. If the two sub electrode pairs 12a and 12c including the subordinate can be selected, Select.

7 is a block diagram showing a modified configuration of the first detection unit 1331. As shown in FIG.

Referring to FIG. 7, the first detection unit 1331 includes two amplifiers G (1, 2, 3, 4, and 5) for unequally amplifying the detection signals of two electrodes individually as disclosed in the registered patent No. 10-1579517 _H and G _L and two pre-processing means 13313 and 13314 constituted by one differential operation converter (ADC) for differential calculation and digital data acquisition, and two preprocessing means 13313 and 13314 relatively The detection signals to be greatly amplified are made different from each other to generate digital data of two channels.

That is, the preprocessing means 13313 and 13314 which connect the high gain amplifier G _H to the + input terminal of the differential operation converter ADC and the low gain amplifier G _L to the negative input terminal of the differential operation converter ADC And two digital data of two channels are generated.

Here, the detection signals of the respective electrodes are supplied to the two preprocessing units 13313 and 13314, respectively, and are supplied to the high gain amplifier G _H on one side and to the low gain amplifier G _L on the other side.

The common noise power of the two electrode detection signals becomes different due to the impedance unbalance between the electrodes. At this time, the common-mode noise obtained by amplifying the low-power common-mode noise by the high gain amplifier (G _H ) The noise of the signals obtained by the two preprocessing units 13313 and 13314 becomes the same phase if they are larger than the in-phase noise obtained by amplification by the amplifier G _L. Thus, the noise introduced through the two electrodes appears as in-phase noise, and the noise also appears as a common-mode noise in a signal obtained by the two preprocessing units 13313 and 13314.

To this end, the gains (or amplification degrees) of the high gain amplifier G _H and the low gain amplifier G _L should be appropriately set in accordance with the degree of the impedance unbalance. Alternatively, in the case where the in-phase noise appears as a large power in the signal obtained by the synthesizer 13312 as described in the Japanese Patent No. 10-1579517, the noise of the signal obtained by the processing by the preprocessing means 13313 and 13314 becomes a phase It is necessary to change the gain little by little until the in-phase noise does not appear in the signal obtained by the synthesizer 13312 so as to have an appropriate value. For example, the gain difference between the high gain amplifier (G _H ) and the low gain amplifier (G _L ) can be increased gradually.

The first detection unit 1331 includes a power normalization unit 13311 for normalizing the generated two-channel digital data so that the in-phase noise power is equalized, and a second normalization unit 13311 for synthesizing two-channel digital data , Thereby obtaining an electromyogram signal in which the common-mode noise is suppressed.

That is, two preprocessing units 13313 and 13314 for performing differential arithmetic after artificially amplifying the potential signals detected by the two electrodes are amplified to obtain a digital signal in which the in-phase signal is partially suppressed and the EMG signal is raised, The digital signals obtained by the preprocessing means 13313 and 13314 are subjected to power normalization in the digital signal processing region and then synthesized to obtain an EMG signal from which the inphase signal is removed.

The configuration diagram of Fig. 7 is described in detail in Japanese Patent Registration No. 10-1579517, so that further explanation is omitted.

Similarly, the second detection unit 1332 can be configured in the same manner as that shown in FIG.

On the other hand, the power normalization unit 13311 and the combiner 13312 are not provided in the first detection unit 1331 and the second detection unit 1332, but instead are provided in the receiving end 20, and 2 Channel digital data to be wirelessly transmitted to the receiving terminal 20 to obtain the EMG signal from the power normalization unit 13311 and the synthesizer 13312. [ In this case, too, the number of choices of the sub-electrode pairs 12 is reduced to half because it is limited to the limited real-time wireless transmission capability of the wireless communication module 14.

8 is a perspective view of an electromyogram band, and Fig. 9 is a cross-sectional view of a pre-processing unit 113, 123 (see Fig. And FIG. 10 is a block diagram of the signal processing unit 13. As shown in FIG. As shown in the block diagram of FIG. 9, the preprocessing units 113 and 123 shown in FIG. 8 can be manufactured in a small and thin size, so that the preprocessing units 113 and 123 are installed on the outer surface of the band so as to have a perspective view.

Referring to FIG. 8, preprocessing units 113 and 123 are provided for each of the sub-electrode pairs 12 as well as the main electrode pair 11.

As shown in FIG. 9, the preprocessing units 113 and 123 are respectively connected to two electrodes provided at the electrode pair at the installation position. The preprocessing units 113 and 123 individually amplify the potential signals detected at the two electrodes unequally and then perform differential computation The preprocessing means for converting the digital signal into digital data is provided in two sets.

The electric signal lines 111 and 121 for connection with the signal processing unit 13 are connected directly to the signal processing unit 13 in addition to the signal detection lines 111a and 121a for transmitting the digital data obtained by the two pre- And signal application lines 111b and 121b are provided for use as in-phase signal drive electrodes.

In the signal processing unit 13, the second switch unit 132 is connected to the signal applying lines 111b and 121b to selectively use the in-phase signal drive electrode. The connection of the signal detection lines 111a and 121a is the same as in the first embodiment.

The first detection unit 1331 and the second detection unit 1332 are provided with a power normalization unit 13311 for normalizing the digital data received through the two paths of the signal application lines 111b and 121b so that the in- And synthesizers 13312 and 13332 for synthesizing the normalized digital data to obtain an electromyogram signal with no in-phase noise removed.

That is, each of the preprocessing units 113 and 123 does not obtain an EMG signal, but generates a digitized two-channel signal in the same manner as the two-channel electrode signal obtained through the two electrodes, thereby generating the electric signal lines 111 and 121 To the signal processing unit (13).

Thus, even if signal distortion occurs in the electric signal lines 111 and 121, the signal processing unit 13 can receive the signal without error. The first detection unit 1331 and the second detection unit 1332 of the signal processing unit 13 digitally process the two-channel signal to obtain an accurate EMG signal.

This constitution corresponds to a constituent element shown in Fig. 7 divided into a portion for obtaining a two-channel digital signal and a portion for obtaining a normalization and an EMG signal.

Of course, the power normalization units 13311 and 13321 receive the in-phase signal power obtained from the in-phase signal acquisition unit 134 and normalize them.

The amplifiers G _H and G _L provided in the preprocessing units 113 and 123 are identical to each other so that the signal processor 13 can select a sub electrode pair according to the signal amplitude. In the second embodiment, if the amplification degree of the amplifiers (G _H , G _L ) is appropriately selected as a fixed value, it is possible to firmly cope with the impedance imbalance between the electrodes and suppress the common-mode noise. However, by adding signal lines to the electric signal lines 111 and 121 for adjusting amplification of the amplifiers G _H and G _L of the preprocessing units 113 and 123, the electromyogram signals The amplification degree of the amplifiers G _H and G _L of the preprocessing units 113 and 123 may be controlled by the control unit 136 so that the residual in-phase signal of the pre-processing units 113 and 123 becomes smaller.

8, a detachable conductive pad 19 is attached to the electrode of the main electrode pair 11 and the electrode of the sub electrode pair 12 in the second embodiment of the present invention. The conductive pad 19 may be made of a material that can be adhered to the electrode and the skin, has adhesive both surfaces for easy removal from the skin, and has good electrical conductivity between the both surfaces and permits deformation. That is, even if the electrode position changes due to the swinging motion of the electromyogram band 10 during exercise, the position of the skin on which the electromyogram is detected is kept intact, thereby reducing the distortion of the electromyogram signal.

While the present invention has been particularly shown and described with reference to exemplary embodiments thereof, it is to be understood that the invention is not limited to the disclosed exemplary embodiments, . ≪ / RTI > Accordingly, such modifications are deemed to be within the scope of the present invention, and the scope of the present invention should be determined by the following claims.

1: body part 2: first target muscle 3: second target muscle
10: EMG band
11: main electrode pair
111: electric signal line 112: electrode
113:
12, 12a, 12b, 12c, 12d: sub-electrode pairs
121: electric signal line 122: electrode
123:
13: Signal processor
131: first switch unit 132: second switch unit
133 EMG signal acquisition unit 1331 first detection unit
1332: second detection unit 1333: packet generation unit
134: In-phase signal acquisition unit 135: In-phase signal application unit
136:
14: Wireless communication module 15: Battery
16: cover 17: fastening means
18: Elastic band 19: Conductive pad
20: Receiver

Claims (6)

The main electrode pair 11 being positioned by the mark 16 so as to contact the first target muscle 2 of the body part 1 to be worn and wrapped and the first target muscle 1 to be worn on the body part 1 to be worn, And a plurality of sub-electrode pairs (12) arranged at intervals along the circumferential direction so as to be dispersed and brought into contact with the region where the second target muscle is located, An electromyogram signal detected through the target muscle 3 is acquired by the signal processing unit 13 and then transmitted through the wireless communication module 14,
The signal processing unit 13 is configured to transmit the electromyogram signal of the second target muscle 3 to be transmitted in real time together with the electromyogram signal of the first target muscle 2 within the limit of the limited real time wireless transmission capability of the wireless communication module 14 Electrode band obtained through the selected sub-electrode pair 12 according to the magnitude of the EMG signal detected in the sub electrode pair 12 of the EMG band. The method of claim 1, wherein
The signal processing unit 13 uses the main electrode pair 11 as an in-phase signal drive electrode for applying the in-phase signal when selecting the sub electrode pairs 12 and the main electrode pair 11 and the selected sub electrode pairs 12 ) Is used to detect electromyogram signals, the electromyogram band that uses unselected sub-electrode pairs as in-phase signal drive electrodes. The method according to claim 2, wherein
The signal processing unit 13 intermittently performs a selection process of the sub electrode pairs 12 while detecting a signal with the main electrode pair 11 and the selected sub electrode pair 12 to select the sub electrode pair 12 to be selected, And an electromyogram band that can change the coincidence signal drive electrode. The method according to claim 2, wherein
If the frequency component of the commercial electricity detected through the sub-electrode pair is lower than a predetermined lower limit before the sub-electrode pair is selected, the signal processing unit 13 generates an artificial phase signal through the in- After the signal is applied, the correction for eliminating the impedance imbalance between the electrodes for each sub-electrode pair is performed according to the size of the in-phase signal detected for each electrode,
An inphase in-phase signal is applied through the in-phase signal drive electrode defined in the sub-electrode pair before the electromotive force signal is obtained by the main electrode pair 11 and the selected sub electrode pair 12, Wherein the compensation for impedance imbalance is performed according to the size of the coherent signal detected for each electrode. The method of claim 1, wherein
The signal processing unit (13) excludes, from the selection target, those whose coincidence signal remaining in the electromyogram signal detected in the plurality of sub electrode pairs (12) exceeds a predetermined upper limit value. The method according to claim 1,
In the position where the main electrode pair 11 and each sub electrode pair 12 are installed, the means for separately amplifying the signals detected by the two electrodes at the mounting position separately, And preprocessing sections (113, 123) for acquiring two-channel digital data are arranged so that detection signals amplified by relatively large amplitudes are made different in the two-
The signal processing unit 13 normalizes the two-channel digital data so that the same-phase noise power is equalized, and then synthesizes the same so that the common-mode noise is removed, thereby obtaining an EMG signal.

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