JP5698163B2 - ECG signal transmission device - Google Patents

Description

  The present invention relates to an electrocardiogram signal transmission apparatus that can reliably transmit an electrocardiogram signal acquired from a living body to an electrocardiograph.

  Conventionally, for example, an electrocardiograph as disclosed in Patent Document 1 below is used for diagnosis of a heart disease. The electrocardiograph is composed of an electrocardiograph body that creates an electrocardiogram, an electrode for acquiring an electrocardiogram signal from a living body, and a cord for connecting the electrode to the electrocardiograph body.

  There are a variety of electrocardiograms used to diagnose heart disease. One of the ECG methods is Holter ECG. The Holter electrocardiography method is effective for diagnosing heart diseases that cannot be measured in a short time, such as arrhythmia, by continuously acquiring electrocardiograms over 24 hours.

  Although it is not a diagnosis of a heart disease, for example, as disclosed in Patent Document 2 below, a driver's electrocardiogram is continuously acquired during a test run of a car, and a driver's stress is measured. Has been tried.

JP 2009-518153 A JP 2007-139499 A

  However, when acquiring a Holter electrocardiogram or measuring driver stress, an electrocardiographic signal must be reliably transmitted from the electrode to the electrocardiograph body during the measurement period. This is because if the electrocardiogram signal is not successfully transmitted between the electrode and the electrocardiograph body due to external noise picked up by the cord or poor contact of the cord, the electrocardiogram signal must be re-acquired.

  Therefore, an object of the present invention is to provide an electrocardiographic signal transmission apparatus that can reliably transmit an electrocardiographic signal acquired from a living body to an electrocardiograph.

In order to achieve the above object, an electrocardiographic signal transmission device according to the present invention includes an electrocardiograph connection portion, an electrocardiographic induction wire, a multicore wire, and a relay portion. The electrocardiograph connection is connected to an electrocardiograph that creates an electrocardiogram. The ECG induction wire is connected to an electrode that acquires an ECG signal from a living body. One end of the multi-core electric wire is connected to the electrocardiograph connection portion, and the other end is connected to the electrocardiographic induction wire. The connection between the electrocardiographic induction wire and the multi-core electric wire is performed at the relay portion, and the connection portion between the electrocardiographic induction wire and the multi-core electric wire is accommodated. The relay unit includes a display lamp that displays a transmission state of the electrocardiogram signal, and has a lighting control unit that controls lighting of the display lamp. The lighting control unit is a noise removing unit that removes noise of the electrocardiogram signal, noise An amplifying unit that amplifies the electrocardiogram signal after the signal is removed, and an electrocardiographic signal level comparing unit that compares the amplified electrocardiographic signal with a stored voltage level. When the electrocardiogram signal is normally transmitted to the electrocardiograph, the display lamp is turned on. When the electrocardiogram signal from the living body is not normally transmitted to the electrocardiograph, the display lamp is blinked, and the electrode and the heart When a contact failure occurs with the electrometer, and the electrocardiogram signal from the living body is not transmitted to the electrocardiograph, the display lamp is turned off .

  The relay unit is provided with electromagnetic shielding for preventing external noise from entering, and the relay unit includes a display lamp for visually checking the transmission state of the electrocardiogram signal.

  According to the electrocardiogram signal transmission apparatus according to the present invention configured as described above, it is possible to prevent the intrusion of external noise and to visually check the transmission state of the electrocardiogram signal. Can be reliably transmitted.

1 is an external view of an electrocardiogram signal transmission device according to Embodiment 1. FIG. It is a figure which shows the core conductor which comprises an electrocardiogram induction wire. It is a figure where it uses for description of the formation process of an electrocardiogram induction wire. It is a figure where it uses for description of the formation process of an electrocardiogram induction wire. It is a figure where it uses for description of the connection process of an electrocardiogram induction wire and an electrode. It is a figure where it uses for description of the connection process of an electrocardiogram induction wire and an electrode. It is a figure where it uses for description of the connection process of an electrocardiogram induction wire and an electrode. It is a figure where it uses for description of the connection process of an electrocardiogram induction wire and an electrode. It is a figure where it uses for description of the connection process of the multicore electric wire and the electrocardiographic induction wire in a relay part. It is an external view of the base stand which comprises a relay part. It is a block diagram of the lighting control part which controls the lighting state of a display lamp. It is an external view of the electrocardiogram signal transmission device according to the second embodiment. It is a block diagram which shows the structure of the amplifier which amplifies the weak signal from an electrode.

  Embodiments of an electrocardiogram signal transmission apparatus according to the present invention will be described below in the first and second embodiments.

[Embodiment 1]
First, the electrocardiographic signal transmission apparatus according to the first embodiment will be described.

(Configuration of ECG signal transmission device)
FIG. 1 is an external view of an electrocardiographic signal transmission apparatus according to this embodiment. The electrocardiogram signal transmission device 100 is formed by an electrocardiograph connection unit 200, a multicore electric wire 300, and a relay unit 400.

  The electrocardiograph connection unit 200 is connected to an electrocardiograph (not shown). One end of the multi-core electric wire 300 is connected to the electrocardiograph connection part 200. The other end of the multi-core wire 300 is connected to the electrocardiographic induction wire 50. The electrocardiographic induction wire 50 is connected to an electrode (not shown) that acquires an electrocardiographic signal from a living body. The connection between the multicore electric wire 300 and the electrocardiographic induction electric wire 50 is performed by the relay unit 400.

  The electrode is attached to a living body and detects an electrocardiographic signal when the heart beats. An electrocardiograph is an apparatus that creates an electrocardiogram by arranging electrocardiographic signals detected by electrodes in time series.

  The multi-core electric wire 300 is a 10-core round electric wire that is electromagnetically shielded. A 10P connector 210 having 10 connection portions is connected to one end of the multi-core electric wire 300 for connection to an electrocardiograph. In addition, 10 electrocardiographic induction wires 50 that connect 10 electrodes are connected to the 10 core wires at the other end of the multicore wire 300. The connection between the ten core electric wires and the ten electrocardiographic induction wires 50 is performed in the relay unit 400.

  The connection portions where the connection portions of the 10P connector 210 and the core wires of the multicore wire 300 are connected are covered with the insulating resin 220 and integrated. This is because the connection strength between the 10P connector 210 and the multi-core electric wire 300 is increased and the usability of the electrocardiographic signal transmission device 100 is improved.

  The relay unit 400 includes a display lamp 450. In the display lamp 450, the electrode is correctly attached to the living body, the electrode and the electrocardiograph are connected to the electrocardiogram signal transmission device 100 without causing poor contact, and the electrocardiogram signal from the living body is normally transmitted to the electrocardiograph. Lights up when Further, the display lamp 450 has an electrode that is not correctly attached to the living body, or a contact failure occurs between the electrocardiogram signal transmission device 100 and the electrode or the electrocardiogram signal transmission device 100 and the electrocardiograph. When the electrocardiogram signal from the living body is not normally transmitted to the electrocardiograph, the blinking is repeated. The display lamp 450 is not turned on when a failure such as a contact failure occurs in the connection between the multi-core electric wire 300 and the electrocardiographic induction wire 50 in the relay unit 400. Therefore, by visually observing the lighting state of the display lamp 450, it can be confirmed whether or not the electrocardiogram signal is normally transmitted to the electrocardiograph.

  Further, the relay unit 400 is provided with electromagnetic shielding that prevents intrusion of external noise. Specifically, a conductor such as a metal plate, a metal tape, or a metal foil is attached to the inside of the case forming the relay unit 400. These conductors are grounded. These conductors shield electromagnetic waves that enter from the outside. The relay unit 400 connects each core wire of the multicore wire 300 and each electrocardiographic induction wire 50 via a resistor (described later). For this reason, the distance of the connection part of the multicore electric wire 300 and the electrocardiographic induction electric wire 50 becomes long, and it becomes easy to infiltrate external noise. The relay unit 400 prevents intrusion of external noise by the above configuration.

  Since the electrocardiogram signal transmission apparatus according to the present embodiment has the above-described configuration, the electrocardiogram signal acquired from the living body can be reliably transmitted to the electrocardiograph.

  In the present embodiment, the configuration of the electrocardiographic induction wire 50 is not affected by external noise, and the connection between the electrocardiographic induction wire 50 and the electrode is devised so as to be strong against bending stress and tensile force. . In addition, the relay unit 400 is devised to securely connect the multicore electric wire 300 to the electrocardiographic induction electric wire 50. Furthermore, a structure that can prevent intrusion of external noise by the relay unit 400 is employed. The relay unit 400 includes a lighting control unit that controls the lighting state of the display lamp 450 according to the transmission state of the electrocardiogram signal.

  Hereinafter, the configuration of the electrocardiographic induction wire 50, the connection between the electrocardiographic induction wire 50 and the electrode, the connection between the multicore wire 300 and the electrocardiographic induction wire 50 in the relay unit 400, the configuration of the relay unit 400, the display lamp The configuration of the lighting control unit that controls the lighting state of 450 will be described.

(Configuration of ECG induction wire)
First, the configuration of the electrocardiographic induction wire 50 will be described. FIG. 2 is a diagram showing a core conductor constituting an electrocardiographic induction wire.

  As shown in FIG. 2, the core conductor 20 has a support 10 serving as a core as a central axis. The support 10 is like a twisted yarn in which long fibers are twisted. A winding 15 in which about 10 thin conductive wires having a diameter of about 0.1 mm are bundled around the outer periphery of the support 10 is wound. The winding 15 is wound horizontally or obliquely on the support 10. Since the core conductor 20 is a twisted yarn in which the support 10 twists a fiber, the tensile strength is 20 kg or more. In addition, since the winding 15 is laterally wound or obliquely laterally wound around the outer periphery of the support 10, the core conductor 20 can withstand severe bending, being soft in the bending direction. Therefore, the core conductor 20 is excellent in softness and resistance to bending and tensile strength, and is convenient as a core wire of the electrocardiographic induction wire 50.

  Next, as shown in FIG. 3, the outer surface of the core conductor 20 shown in FIG. As the insulating resin 25, polyethylene (PE), polypropylene (PP), polystyrene (PS), vinyl chloride resin, or the like is used.

  Then, as shown in FIG. 4, a conductive resin such as vinyl carbon resin 30 is thinly coated on the outer surface of the insulating resin 25 so as to shield electromagnetic waves from the outside. Further, a winding 35 in which about 10 thin conductive wires having a diameter of about 0.1 mm are bundled around the outer surface of the vinyl carbon resin 30 is wound. The winding 35 forms an electromagnetic shield 40. The winding 35 winds the outer surface of the vinyl carbon resin 30 horizontally or diagonally. When the outer surface of the electromagnetic shield 40 is covered with an insulating resin such as a soft insulating vinyl resin 45, an electrocardiographic induction wire 50 is formed.

  The core conductor 20 that is the core wire of the electrocardiographic induction wire 50 is double-electromagnetically shielded by the vinyl carbon resin 30 and the electromagnetic shield 40. For this reason, the core conductor 20 which transmits an electrocardiogram signal can completely shield the electromagnetic wave from the outside, and can prevent intrusion of external noise. The electrocardiographic induction wire 50 is wound in a horizontal direction or an oblique horizontal direction around the winding wire 15 and the winding wire 35, so that it is soft in the bending direction and can withstand severe bending.

(Connection between electrocardiographic induction wires and electrodes)
Next, the connection between the electrocardiographic induction wire and the electrode will be described.

  When connecting the electrocardiographic induction wire and the electrode, as shown in FIG. 5, first, the insulating vinyl resin 45, the electromagnetic shield 40, and the vinyl carbon resin 30 at the tip of the electrocardiographic induction wire 50 are simultaneously peeled by about 25 mm. Then, the core conductor 20 is exposed.

  Next, the insulating resin 25 of the core conductor 20 is peeled off by about 15 mm to expose the core conductor 20. As shown in FIG. 2, the core conductor 20 is one in which a winding 15 is laterally wound or obliquely laterally wound with the support 10 as a central axis.

  Then, the core conductor 20 is inserted into the crimping terminal caulking hole of the electrode connection terminal 500, and the inserted portion of the core conductor 20 is crushed from above and below the connection terminal 500 as shown in FIG. 6. Thereby, the core conductor 20 and the electrode connection terminal 500 are wisely connected, and the electrocardiographic induction wire 50 and the electrode are connected.

  Next, the connection part between the electrocardiographic induction wire 50 and the connection terminal 500 is integrated with the insulating resin 60. The integration of the connecting portions may be performed using a molding die.

  Further, as shown in FIG. 7, a soft resin 65 is molded and coated so as to cover the connection portion between the electrocardiographic induction wire 50 and the electrode connection terminal 500. When the connection portion is covered with the soft resin 65, the connection portion between the electrocardiographic induction wire 50 and the connection terminal 500 is sensible, and the electrocardiographic induction wire 50 side becomes soft, so that the handling feeling is improved.

  Further, since the winding 15 of the core conductor 20 is laterally wound or obliquely laterally wound, the core conductor 20 is soft in the bending direction and can withstand severe bending. Therefore, the connection portion between the core conductor 20 and the connection terminal 500 is a connection portion excellent in anti-double bending.

  Furthermore, as shown in FIG. 8, before inserting the core conductor 20 into the crimp terminal crimping hole of the connection terminal 500, the core conductor 20 exposed long is tied or entangled in a round shape. The core conductor 20 protruding from the anchor 70 is inserted into the crimping terminal crimping hole of the connection terminal 500, and the insertion portion of the core conductor 20 is inserted from above and below the connection terminal 500 as shown in FIG. It may be crushed.

  And if the connection part of the electrocardiogram induction wire 50 and the connection terminal 500 is integrated with the insulating resin 60, the tensile strength from the bidirectional | two-way of the electrocardiogram induction wire 50 and the connection terminal 500 will increase. Further, even if the strong bending is repeated, the induction wire 50 is not unwound from the connection terminal 500 or disconnected.

  Even if the ECG electric wire 50 and the connection terminal 500 are not connected wisely, the ECG electric wire 50 may be disconnected from the connection terminal 500 due to the anchoring action of the anchor 70 in the insulating resin 60. Does not happen. Further, even if the bending is repeated frequently or pulled strongly, the connection between the electrocardiographic induction wire 50 and the connection terminal 500 is sufficiently maintained, and the connection portion of the core conductor 20 is disconnected from the connection terminal 500, causing a problem. Never do.

(Connection between multicore wire and ECG wire in the relay)
Next, the connection between the multicore wire 300 and the electrocardiographic induction wire 50 in the relay unit 400 will be described. FIG. 9 is a diagram for explaining a connection process between the multicore electric wire and the electrocardiographic induction wire in the relay unit.

  As shown in FIG. 9, ten electrocardiographic induction wires 50 are connected to each of the ten core wires 310 of the multicore wire 300. FIG. 9 illustrates a case where one core wire 310 and one electrocardiographic induction wire 50 of the multicore wire 300 are connected for easy understanding.

  When connecting the multicore electric wire 300 and the electrocardiographic induction wire 50, the core electric wire (copper wire) of the multicore electric wire 300 is exposed, and the connection portion of the core electric conductor 20 of the electrocardiographic induction wire 50 is exposed. Then, the 100 KΩ resistor 80 is connected to the core wire of the multicore wire 300 and the core conductor 20 of the electrocardiographic induction wire 50. To connect the core wire of the multi-core wire 300 and the resistor 80, the core wire is inserted into the crimping terminal crimping hole of the connection component 85, and one terminal of the resistor 80 is inserted into the crimping terminal crimping hole of the connection component 85. Then, the both ends of the connecting component 85 are crushed from above and below. The resistor 80 and the core conductor 20 are connected by inserting one terminal of the resistor 80 into the crimping terminal crimping hole of the connection component 95 and inserting the core conductor 20 into the crimping terminal crimping hole of the connection component 95. This is done by crushing both ends of the connection component 95 from above and below.

  The 100 KΩ resistor 80 connected to the core wire of the multi-core wire 300 and the core conductor 20 of the electrocardiographic induction wire 50 uses an AED when the heartbeat is stopped (the instantaneous high voltage of 5000 V is applied to the living body). When a high-frequency electric scalpel is used, a high voltage is applied to the living body, so that the applied high voltage serves to prevent direct entry into the electrocardiograph.

  Also, the toroidal core 90 is attached to one terminal of the resistor 80. The toroidal core 90 is attached to remove electromagnetic waves generated in the electrocardiographic induction wire 50, the relay unit 400, and the multi-core wire 300. Although the entire ECG electric wire 50 can completely shield electromagnetic interference from the outside, the ECG electric wire 50 and the multi-core electric wire 300 are bent at the time of acquiring an electrocardiogram. This becomes noise and adversely affects the electrocardiogram signal. The toroidal core prevents this.

(Configuration of the relay unit)
Next, the configuration of the relay unit 400 will be described. FIG. 10 is an external view of the base board 440 constituting the relay unit 400.

  The base platform 440 is rectangular and includes six concave groove portions 445 extending linearly in one direction. Each groove portion 445 accommodates a connection portion between the core wire of the multicore wire 300 and the electrocardiographic induction wire 50. The walls 446 forming the six groove portions 445 have a certain thickness in order to take an insulation distance between the connecting portions between the core wire of the multicore wire 300 and the electrocardiographic induction wire 50.

  Two base stands 440 are stacked, and one base stand 440 is covered with a lid 460. The two base stands 440 are laminated with the groove portions 445 facing the same direction. The lid 460 is placed over the base 440 having the groove 445 opened. FIG. 10 shows one of the two bases 440 and a lid 460 that covers the bases 440.

  Ten electrocardiographic induction wires 50 are connected to the ten core wires of the multicore wire 300. Therefore, each core wire has a connection portion with the electrocardiographic induction wire 50. The connecting portions of the 10 core wires and the 10 electrocardiographic induction wires 50 forming the multicore wire 300 are distributed one by one to the groove portions 445 of the two bases 440.

  Connection portions connected to the six electrodes attached to the chest are housed and fixed in the groove portions 445 of one base stand 440. Connection portions connected to the four electrodes attached to the foot portion and the hand portion are housed and fixed in the groove portion 445 of the other base 440.

  When the connection portion between the core wire of the multi-core electric wire 300 and the electrocardiographic induction wire 50 is stored in the groove portion 445 of the two substrate bases 440, the lid 460 is put on the base table 440 where the groove portion 445 is open. When two bases 440 are stacked and covered with a lid 460, they are stored in a case. The case is provided with electromagnetic shielding to prevent external noise from entering on the inner wall or outside thereof. For example, a conductor such as a metal plate, a metal tape, or a metal foil is attached to the inside or outside of the case. These conductors shield electromagnetic waves that enter from the outside.

  In addition, the case houses a lighting control unit (a substrate having a battery) that controls lighting of the display lamp 450. In order to insulate electromagnetically the connecting portion between the core wire of the multi-core electric wire 300 and the electrocardiographic induction wire 50, the lighting control unit can perform independent electromagnetic shielding separately from the electromagnetic shielding of the connecting portion. is there. For example, the outside of the lighting control unit is covered with a conductor such as a metal plate, a metal tape, or a metal foil.

(Configuration of lighting control unit)
Next, the configuration of the lighting control unit that controls the lighting state of the display lamp 450 will be described. FIG. 11 is a configuration diagram of a lighting control unit 600 that controls the lighting state of the display lamp 450.

  The lighting control unit 600 includes a noise removal unit 610, an amplification unit 620, and an electrocardiogram signal level comparison unit 630.

  The noise removing unit 610 is a circuit that removes noise included in an electrocardiographic signal acquired by an electrode. Examples of noise include a voltage applied to a living body when using an AED, a voltage applied to a living body when using a high-frequency electric knife, and the like.

  The amplification unit 620 is a circuit that amplifies the electrocardiogram signal from which noise has been removed.

  The electrocardiogram signal level comparison unit 630 is a circuit that compares the voltage level of the amplified electrocardiogram signal with a plurality of voltages stored in the electrocardiogram signal level comparison unit 630.

  The electrocardiogram signal level comparison unit 630 stores, as the first voltage, a voltage obtained by multiplying the voltage level of the electrocardiogram signal acquired when the electrode is correctly attached to the living body by a constant (amplification factor). . In addition, the second voltage is lower than the first voltage and the electrode is not correctly attached to the living body, and the electrocardiogram signal transmission device 100 and the electrode or the electrocardiogram signal transmission device 100 and the electrocardiogram. The voltage which can detect that there is a poor contact with the meter is stored. As the third voltage, a voltage substantially lower than the second voltage and close to 0 volts is stored.

(Operation of lighting control unit)
The electrocardiogram signal level comparison unit 630 turns on the display lamp 450 when the voltage level of the amplified electrocardiogram signal is equal to or higher than the first voltage.

  The practitioner who is performing the electrocardiogram measurement sees the lighting of the display lamp 450, the electrode is correctly attached to the living body, the electrode and the electrocardiograph are connected to the electrocardiogram signal transmission device 100 without causing poor contact, and the living body It can be recognized that the electrocardiographic signal from is normally transmitted to the electrocardiograph.

  The electrocardiogram signal level comparison unit 630 causes the display lamp 450 to blink if the voltage level of the amplified electrocardiogram signal is lower than the first voltage and equal to or higher than the second voltage.

  The practitioner who is performing the electrocardiogram measurement sees the blinking of the display lamp 450, the electrode is not correctly attached to the living body, or the electrocardiogram signal transmission device 100 and the electrode or the electrocardiogram signal transmission device 100 and the electrocardiograph. It is possible to recognize that an electrocardiogram signal from the living body is not normally transmitted to the electrocardiograph due to a contact failure occurring during the period.

  Further, the electrocardiogram signal level comparison unit 630 turns off the display lamp 450 if the voltage level of the amplified electrocardiogram signal is lower than the third voltage.

  The practitioner who is measuring the electrocardiogram recognizes that the connection between the multi-core electric wire 300 and the electrocardiographic induction wire 50 is defective in the relay unit 400 when the indicator lamp 450 is turned off. it can.

  As described above, according to the electrocardiogram signal transmission device according to the first embodiment, since electromagnetic shielding is performed, it is possible to prevent the intrusion of external noise, and the transmission state of the electrocardiogram signal can be visually observed. Thus, the electrocardiogram signal can be reliably transmitted to the electrocardiograph. Therefore, the electrocardiogram signal transmission apparatus according to the present embodiment is very effective in an electrocardiogram examination method in which an electrocardiogram signal must be acquired over a long period of time.

[Embodiment 2]
Next, an electrocardiographic signal transmission apparatus according to the second embodiment will be described. In the electrocardiogram signal transmission apparatus according to the second embodiment, the 10P connector 210 of the electrocardiogram signal transmission apparatus according to the first embodiment is replaced with a USB connector, and an amplifier is provided in the relay unit 400. This embodiment is the same as the first embodiment except that a USB connector is used and an amplifier is provided in the relay unit.

(Configuration of ECG signal transmission device)
FIG. 12 is an external view of an electrocardiographic signal transmission apparatus according to this embodiment. The electrocardiogram signal transmission device 100 is formed by an electrocardiograph connection unit 700, a multicore electric wire 300, and a relay unit 400.

  The electrocardiograph connection unit 700 is connected to an electrocardiograph (not shown) or a PC (personal computer) functioning as an electrocardiograph. One end of the multi-core electric wire 300 is connected to the electrocardiograph connection portion 700. The other end of the multi-core electric wire 300 is connected to the electrocardiographic induction electric wire 50 via an amplifier described later. The electrocardiographic induction wire 50 is connected to an electrode (not shown) that acquires an electrocardiographic signal from a living body. The connection between the multi-core electric wire 300 and the electrocardiographic induction wire 50 is performed by an amplifier provided in the relay unit 400.

  The electrode is attached to a living body and detects an electrocardiographic signal when the heart beats. An electrocardiograph is an apparatus that creates an electrocardiogram by arranging electrocardiographic signals detected by electrodes in time series.

  The multi-core electric wire 300 is a 10-core round electric wire that is electromagnetically shielded. A USB connector 710 for connecting to an electrocardiograph is connected to one end of the multicore electric wire 300. In addition, 10 electrocardiographic induction wires 50 that connect 10 electrodes are connected to the 10 core wires at the other end of the multi-core wire 300 through an amplifier. The connection between the 10 core wires and the amplifier, and the connection between the amplifier and the 10 electrocardiographic induction wires 50 are made at 10 terminals provided on the ultrathin flat substrate on which the amplifier is formed. In the state where the connection component 95 shown in FIG. 9 is removed, the 10 core wires 310 of the multi-core wire 300 and the core conductor 20 of the electrocardiographic induction wire 50 are connected to the 10 terminals provided on the board. The

  The relay unit 400 includes a display lamp 450. In the display lamp 450, the electrode is correctly attached to the living body, the electrode and the electrocardiograph are connected to the electrocardiogram signal transmission device 100 without causing poor contact, and the electrocardiogram signal from the living body is normally transmitted to the electrocardiograph. Lights up when Further, the display lamp 450 has an electrode that is not correctly attached to the living body, or a contact failure occurs between the electrocardiogram signal transmission device 100 and the electrode or the electrocardiogram signal transmission device 100 and the electrocardiograph. When the electrocardiogram signal from the living body is not normally transmitted to the electrocardiograph, the blinking is repeated. The display lamp 450 is not turned on when a failure such as a contact failure occurs in the connection between the multi-core electric wire 300 and the electrocardiographic induction wire 50 in the relay unit 400. Therefore, by visually observing the lighting state of the display lamp 450, it can be confirmed whether or not the electrocardiogram signal is normally transmitted to the electrocardiograph.

  Further, the relay unit 400 is provided with electromagnetic shielding that prevents intrusion of external noise. Specifically, a conductor such as a metal plate, a metal tape, or a metal foil is attached to the inside of the case forming the relay unit 400. These conductors are grounded. These conductors shield electromagnetic waves that enter from the outside. The relay unit 400 connects each core wire of the multicore wire 300 and each electrocardiographic induction wire 50 via an amplifier and a resistor (described later). For this reason, the distance of the connection part of the multicore electric wire 300 and the electrocardiographic induction electric wire 50 becomes long, and it becomes easy to infiltrate external noise. The relay unit 400 prevents intrusion of external noise by the above configuration.

  Since the electrocardiogram signal transmission apparatus according to the present embodiment has the above-described configuration, the electrocardiogram signal acquired from the living body can be amplified and reliably transmitted to the electrocardiograph.

  In the present embodiment, the configuration of the electrocardiographic induction wire 50 is not affected by external noise, and the connection between the electrocardiographic induction wire 50 and the electrode is devised so as to be strong against bending stress and tensile force. . In addition, the relay unit 400 is devised to securely connect the multicore electric wire 300 to the electrocardiographic induction electric wire 50. Furthermore, a structure that can prevent intrusion of external noise by the relay unit 400 is employed. The relay unit 400 includes an amplifier (described later) that amplifies a weak electrocardiogram signal, digitizes the signal, and outputs the digitized signal to the USB connector 710. Further, the relay unit 400 includes a lighting control unit that controls the lighting state of the display lamp 450 according to the transmission state of the electrocardiogram signal.

  FIG. 13 is a block diagram showing a configuration of an amplifier that amplifies a weak ECG signal from the ECG signal detection electrode. This amplifier is provided in the relay unit 400. First, the configuration of the relay unit will be described with reference to FIG.

(Configuration of the relay unit)
The base platform 440 is rectangular and includes six concave groove portions 445 extending linearly in one direction. Each groove portion 445 accommodates the core wire of the multicore wire 300 and the electrocardiographic induction wire 50. The walls 446 forming the six groove portions 445 have a certain thickness in order to take an insulation distance between the connecting portions between the core wire of the multicore wire 300 and the electrocardiographic induction wire 50.

  Two base stands 440 are stacked, and one base stand 440 is covered with a lid 460. The two base stands 440 are laminated with the groove portions 445 facing the same direction. The lid 460 is placed over the base 440 having the groove 445 opened. FIG. 10 shows one of the two bases 440 and a lid 460 that covers the bases 440.

  The amplifier 750 having the configuration shown in FIG. 13 is connected to the 10 core wires of the multicore wire 300. In addition, ten ECG induction wires 50 are connected to the terminals of the amplifier 750. Therefore, the 10 core wires forming the multicore wire 300 and the 10 electrocardiographic induction wires 50 are connected via the amplifier 750.

  Connection portions connected to the six electrodes attached to the chest are housed and fixed in the groove portions 445 of one base stand 440. Connection portions connected to the four electrodes attached to the foot portion and the hand portion are housed and fixed in the groove portion 445 of the other base 440.

  The core wire of the multi-core wire 300 and the electrocardiographic induction wire 50 are housed in the groove portions 445 of the two bases 440, and an ultrathin substrate on which the amplifier 750 is formed is placed on the groove portion 445, and the groove portion 445 is opened. The base 440 is covered with the lid 460. When two bases 440 are stacked and covered with a lid 460, they are stored in a case. The case is provided with electromagnetic shielding to prevent external noise from entering on the inner wall or outside thereof. For example, a conductor such as a metal plate, a metal tape, or a metal foil is attached to the inside or outside of the case. These conductors shield electromagnetic waves that enter from the outside.

  In addition, the case houses a lighting control unit (a substrate having a battery) that controls lighting of the display lamp 450. In order to achieve electromagnetic insulation between the ultrathin substrate on which the amplifier 750 is formed, the core wire of the multi-core wire 300, and the connection portion between the substrate and the electrocardiographic induction wire 50, the lighting control unit Apart from that, independent electromagnetic shielding is possible. For example, the outside of the lighting control unit is covered with a conductor such as a metal plate, a metal tape, or a metal foil.

  An amplifier 750 formed on an extremely thin substrate includes an analog amplifier 760 and an A / D converter 770 as shown in FIG. The analog amplifier 760 is an amplifier having a large amplification factor using an operational amplifier, and amplifies weak currents output from a total of 10 electrodes to a current of about several volts with a total of 10 operational amplifiers. The A / D conversion unit 770 converts the electrocardiogram signal amplified by the analog amplifier 760 into a digital signal using ten A / D converters. The converted digital signal is transmitted through an electrocardiograph or a USB connector attached to a PC having an electrocardiograph function. An electrocardiograph or a PC having an electrocardiograph function creates an electrocardiogram based on a transmitted digital signal. Note that the amplifier 750 includes a unit having four operational amplifiers and four A / D converters on one base, and a unit having six operational amplifiers and six A / D converters on the other side. The amplifier is stored in the base board, and one amplifier is stored in each of the two base boards 440.

  As described above, according to the electrocardiogram signal transmission device according to the second embodiment, since electromagnetic shielding is performed, intrusion of external noise can be prevented, and the transmission state of the electrocardiogram signal can be visually observed. Thus, the electrocardiogram signal can be reliably transmitted to the electrocardiograph. Furthermore, since a USB connector is used, an electrocardiogram can be easily created even with a commonly used PC. Moreover, since a weak electrocardiogram signal can be amplified and output, a more stable output can be obtained. Therefore, the electrocardiogram signal transmission apparatus according to the present embodiment is very effective in an electrocardiogram examination method in which an electrocardiogram signal must be acquired over a long period of time.

20 core conductor,
50 ECG induction wires,
80 resistors,
100 ECG signal transmission device,
200 ECG connection,
210 10P connector,
220 insulating resin,
300 Multi-core wire,
400 relay section,
440 base stand,
445 groove,
450 indicator lamp,
460 lid,
500 connection terminals,
600 lighting controller,
610 noise removal unit,
620 amplification unit,
630 ECG signal level comparison unit,
700 ECG connection,
710 USB connector,
750 amplifier,
760 analog amplifier,
770 A / D converter.

Claims (8)

An electrocardiograph connection connected to the electrocardiograph;
An electrocardiographic wire connected to an electrode for acquiring an electrocardiogram signal from a living body;
A multi-core wire having one end and the other end is connected to the electrocardiograph connection portion is connected to the ECG cable,
A relay portion that houses a connection portion between the electrocardiographic induction wire and the multi-core wire ,
The relay part is subjected to electromagnetic shielding to prevent intrusion of external noise ,
The relay unit is
Equipped with an indicator lamp that displays the electrocardiogram signal transmission status
A lighting control unit for controlling lighting of the display lamp;
The lighting control unit includes a noise removing unit that removes noise from the electrocardiogram signal, an amplification unit that amplifies the electrocardiogram signal after the noise is removed, and a heart that compares the amplified electrocardiogram signal with a stored voltage level. An electric signal level comparison unit;
The electrocardiogram signal level comparison unit turns on the display lamp when an electrocardiogram signal from the living body is normally transmitted to the electrocardiograph, and an electrocardiogram signal from the living body is normal to the electrocardiograph. The indicator lamp blinks when not being transmitted to the electrocardiograph, and when there is a contact failure between the electrode and the electrocardiograph and the electrocardiogram signal from the living body is not transmitted to the electrocardiograph, the indicator lamp is turned on. An electrocardiographic signal transmission device characterized by being extinguished . The electromagnetic shielding of the relay part is
2. The electrocardiogram signal transmission device according to claim 1, wherein the electrocardiogram signal transmission device is performed by attaching a conductor such as a metal plate, a metal tape, or a metal foil to the inside of the case forming the relay portion . The electrocardiographic induction wire is
It has a core electrical conductor in which a conducting wire is wound around the outer periphery of the support that becomes the core,
The core conductor is covered with an insulating resin, the insulating resin is further covered with a conductive resin, and a conductor different from the conductor wound around the outer periphery of the support is wound around the outer periphery of the conductive resin. The electrocardiographic signal transmission device according to claim 1 or 2, wherein the conductive wire wound around the outer periphery of the conductive resin is covered with an insulating resin . The connection part of the electrocardiographic induction wire and the multicore wire is
4. The resistor according to claim 1, wherein a resistor that prevents high voltage penetration and a toroidal core for removing electromagnetic waves are connected between the electrocardiographic induction wire and the multicore wire. 5. electrocardiographic signal transmission apparatus according to any. The connection part of the electrocardiographic induction wire and the multicore wire is
The electrocardiographic signal transmission device according to claim 1, wherein the relay unit is housed in a groove portion of a base board provided in the relay unit . The electrocardiographic signal according to claim 3 , wherein the insulating resin covering the core conductor is one of polyethylene (PE), polypropylene (PP), polystyrene (PS), and vinyl chloride resin. Transmission equipment. The electrocardiographic signal transmission device according to claim 3 , wherein the conductive resin is obtained by adding conductive carbon to vinyl carbon resin . The connection portion between the electrocardiographic induction wire and the electrode has a knob-like anchor formed using the core conductor of the electrocardiographic induction wire, and the anchor is integrated with resin. 8. The electrocardiographic signal transmission device according to claim 1, wherein

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