CN105597233A - Heart pacemaker with noncontact power supply function - Google Patents

Heart pacemaker with noncontact power supply function Download PDF

Info

Publication number
CN105597233A
CN105597233A CN201610069613.XA CN201610069613A CN105597233A CN 105597233 A CN105597233 A CN 105597233A CN 201610069613 A CN201610069613 A CN 201610069613A CN 105597233 A CN105597233 A CN 105597233A
Authority
CN
China
Prior art keywords
circuit
contact power
pacemaker
heart
external
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
CN201610069613.XA
Other languages
Chinese (zh)
Other versions
CN105597233B (en
Inventor
周成虎
陈朝阳
张秋慧
贾贞贞
张菲菲
许峰宽
周建炜
朱永彪
马楚欣
李柏松
袁勋
邢伟伟
刘磊
贾立冬
吴红波
吴涛
张坤
陈冰洋
王振涛
王京
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Henan Institute of Engineering
Original Assignee
Henan Institute of Engineering
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Henan Institute of Engineering filed Critical Henan Institute of Engineering
Priority to CN201610069613.XA priority Critical patent/CN105597233B/en
Publication of CN105597233A publication Critical patent/CN105597233A/en
Application granted granted Critical
Publication of CN105597233B publication Critical patent/CN105597233B/en
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/3625—External stimulators
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/1116—Determining posture transitions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/346—Analysis of electrocardiograms
    • A61B5/349—Detecting specific parameters of the electrocardiograph cycle
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/48—Other medical applications
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6802—Sensor mounted on worn items
    • A61B5/6804—Garments; Clothes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential
    • A61N1/36592—Heart stimulators controlled by a physiological parameter, e.g. heart potential controlled by the heart rate variability

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Cardiology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Biophysics (AREA)
  • Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Medical Informatics (AREA)
  • Pathology (AREA)
  • Physiology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Dentistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Electrotherapy Devices (AREA)

Abstract

The invention discloses a heart pacemaker with a noncontact power supply function. The pacemaker comprises a storage battery, an external pacemaker circuit and an internal energy receiving apparatus, wherein the storage battery and the external pacemaker circuit are connected, the external end of the external pacemaker circuit is provided with a wireless ECG sensor, the wireless ECG sensor is installed at an external heart, the external energy receiving apparatus is arranged in the skin of a left shoulder, the external pacemaker circuit is connected with the internal energy receiving apparatus through electromagnetic coupling, and the internal energy receiving apparatus is connected with a heart through an electrode. According to the invention, the fatigue degree of the heart is determined through measurement of ECG signals by use of a heart rate variation feature, and amplitude of pulse voltages needing to be provided and conduction stimulation time are controlled; an ECG signal detection filtering circuit, the storage battery and a noncontact power supply primary circuit are installed outside, and only a noncontact power supply secondary circuit is installed in the body of a patient, such that the volume of a built-in circuit is greatly reduced, and regular operation for replacement of the storage battery is unnecessary.

Description

There is the pacemaker of non-contact power function
Technical field
The present invention relates to the technical field of pacemaker, be specifically related to a kind of pacemaker with non-contact power function, the state of beating to heart in vitro of realizing is monitored and pace-making, belongs to the field of medical electronics.
Background technology
Pacemaker is for making secondary stimulus to human heart pace-making, conventionally be arranged on skin in the body under the left shoulder of patient, under the skin of left front chest, insert pacemaker, make skin prop up formation pouch, infraclavicular venipuncture at left front chest passes into electrode, electrode leads to heart by vein and is fixed by the inner side that front end threading hook thrusts heart, as shown in Figure 1. Because traditional pacemaker is conventionally larger, after installing, patient's skin for a long time can not be closed, has a bath, moving is restricted. Patient institute suffer cannot be sayed table, and some patient is even home-confined, and many people cannot go to work, work and the strenuous exercise such as running.
Due to the built-in disposable battery of traditional pacemaker, such pacemaker wants to keep to work for a long time about 10 years, must accomplish enough greatly, and can not take vigorous exercise in order to save electric weight, also wants regular replacing. When skin is just closed after several years, can have a bath, to perspire when also can not immersing in body, operation has next time started again, and patient's life quality only maintains minimum level.
Also have scholar to propose the pacemaker based on wireless power, but these pacemakers still need internal battery and radio communication circuit, testing circuit, the volume of pacemaker cannot narrow down to the degree that hand postoperative skin is completely closed.
Summary of the invention
In order to solve the problems of the technologies described above, the invention provides a kind of pacemaker with non-contact power function, only need in patient body, install energy i (in vivo) receiving system, vitro detection electrocardiosignal and employing reckoning electrode voltage method are carried out non-contact power, do not need the voltage of direct-detection heart electrode both sides, also do not need to install additional and external telecommunication circuit, reduce the overall volume of implanting, extend service life, can forever work and not need to change, made patient avoid the misery of Repeated Operation.
In order to achieve the above object, technical scheme of the present invention is: a kind of pacemaker with non-contact power function, comprise battery, external pacemaker circuits and energy i (in vivo) receiving system, battery is connected with external pacemaker circuits, external pacemaker circuits outer end is provided with wireless EGC sensor, wireless EGC sensor is arranged on external heart place, energy i (in vivo) receiving system is arranged in left shoulder skin, external pacemaker circuits is connected by electromagnetic coupled with energy i (in vivo) receiving system, and energy i (in vivo) receiving system is connected with heart by electrode.
Described energy i (in vivo) receiving system comprises non-contact power secondary coil, rectification circuit, filter circuit and electrode interface, non-contact power secondary coil is connected with non-contact power primary coil by electromagnetic coupled, non-contact power secondary coil is connected with rectification circuit, rectification circuit is connected with filter circuit, filter circuit is connected with electrode interface, and electrode interface is connected with electrode.
Described external pacemaker circuits comprises signal detection filter circuit, control circuit, non-contact power former limit circuit and non-contact power primary coil, wireless EGC sensor is connected with signal detection filter circuit, signal detection filter circuit is connected with control circuit, control circuit is connected with the former limit of non-contact power circuit, and the former limit of non-contact power circuit is connected with non-contact power primary coil.
Described control circuit comprises three-axis gyroscope, A/D change-over circuit, Data Management Analysis circuit, degree of fatigue decision circuitry and output control circuit, A/D change-over circuit is connected with signal detection filter circuit, three-axis gyroscope, A/D change-over circuit are connected with Data Management Analysis circuit respectively, Data Management Analysis circuit is connected with degree of fatigue decision circuitry, degree of fatigue decision circuitry is connected with output control circuit, and output control circuit is connected with the former limit of non-contact power circuit.
Described wireless EGC sensor is arranged near enclosing in chest clothes external heart in wearable mode, non-contact power primary coil and non-contact power secondary coil are installed in parallel under left shoulder, distance between non-contact power primary coil and non-contact power secondary coil is between 0.3 ~ 0.5cm, and non-contact power primary coil and non-contact power secondary coil transmit magnetic field energy with cordless.
Described non-contact power secondary coil is the coil forming with the coiling of thin copper enamel-covered wire, and rectification circuit and filter circuit are surface mount elements.
Its operation principle is: wireless EGC sensor gathers user's electrocardiosignal, and signal detection filter circuit utilizes the operational amplifier in it faint electrocardiosignal amplification, filtering, voltage lifting finally to be generated to the waveform of EGC analog signal; A/D change-over circuit converts EGC analog signal waveform to data signal and delivers to Data Management Analysis circuit and carry out analyzing and processing, judged the state of heart according to the result of electrocardiosignal by degree of fatigue decision circuitry, the former limit of output control circuit control non-contact power circuit the dutycycle of switching devicet on, to non-contact power secondary coil transferring energy, after energy i (in vivo) receiving system rectifying and wave-filtering, implement pacing stimulation by electrode pair heart by non-contact power primary coil.
Described degree of fatigue decision circuitry judges the method for heart fatigue: measure the time difference between electrocardiosignal waveform RR crest, calculate the variation property of heart rate, be judged to be fatigue if the time of RR crest interval is greater than normal time range.
Described output control circuit is by controlling the dutycycle of the former limit of non-contact power contactor devicet onTo change the output voltage of electrodeu o , output control circuit is by judging and controlling the total power-on time of the former limit of non-contact power circuit, to change electrode output voltageu o Duration, the duration is the conducting stimulation time of an electrocardio pulset tot。
Described three-axis gyroscope is measured position, motion track and the acceleration of 6 directions of three reference axis of three dimensions, the signal obtaining is delivered to data processing and analyzing and processing is carried out in analysis circuit processing, in the time detecting that health moves, output control circuit is strengthened cardiac pacing stimulus signal immediately, increases the voltage magnitude stimulating and extends the conducting stimulation time of electrocardio pulset tot。
The present invention is by the measurement to electrocardiosignal, utilize heart rate variability characteristic to judge the degree of fatigue of heart, judge degree of fatigue by degree of fatigue judge module, amplitude size and the stimulation time length of the pulse voltage providing to non-contact power secondary coil by the former limit of output control circuit control non-contact power circuit; Meanwhile, the health of measuring patient by three-axis gyroscope changes, and realizes the initiatively judgement of pace-making. Different from traditional pacemaker, the present invention is installed in former to ECG signal sampling filter circuit, pacemaker, battery and non-contact power limit circuit outside health, only non-contact power secondary circuit is arranged in the subcutaneous pouch of the left front chest of patient, can greatly reduce like this volume of built-in circuit, and no longer need regularly operation to change the battery of pacemaker. The present invention is based on the pacemaker of wireless power technology, without internal battery, radio communication circuit and testing circuit, energy i (in vivo) receiving system does not need direct-detection heart electrode both sides voltage, do not need to install additional the telecommunication circuit matching with external pacemaker circuits yet, compared with built-in dual chamber pacemaker in the past, the volume of energy i (in vivo) receiving system is reduced to original below 1/4, and thickness is reduced to original below 1/3, and energy i (in vivo) receiving system can forever be worked after implanting not to be needed to change.
Brief description of the drawings
In order to be illustrated more clearly in the embodiment of the present invention or technical scheme of the prior art, to the accompanying drawing of required use in embodiment or description of the Prior Art be briefly described below, apparently, accompanying drawing in the following describes is only some embodiments of the present invention, for those of ordinary skill in the art, do not paying under the prerequisite of creative work, can also obtain according to these accompanying drawings other accompanying drawing.
Fig. 1 is traditional pacemaker installation site figure.
Fig. 2 is theory diagram of the present invention.
Fig. 3 is the circuit diagram of signal detection filter circuit of the present invention.
Fig. 4 is electrocardiosignal waveform of the present invention.
Fig. 5 is non-contact power coil relative position figure of the present invention.
Fig. 6 is circuit voltage waveform of the present invention.
Detailed description of the invention
Below in conjunction with the accompanying drawing in the embodiment of the present invention, the technical scheme in the embodiment of the present invention is clearly and completely described, obviously, described embodiment is only the present invention's part embodiment, instead of whole embodiment. Based on the embodiment in the present invention, those of ordinary skill in the art, not paying the every other embodiment obtaining under creative work prerequisite, belong to the scope of protection of the invention.
Have a pacemaker for non-contact power function, theory diagram as shown in Figure 2, comprises battery 9, external pacemaker circuits 27 and energy i (in vivo) receiving system 11. Battery 9 is as the power supply of whole device, for whole device provides electric energy support, battery 9 is connected with external pacemaker circuits 27, external pacemaker circuits 27 outer ends are provided with wireless EGC sensor 25, wireless EGC sensor 25 is arranged on external heart place, energy i (in vivo) receiving system 11 is arranged in left shoulder skin, and external pacemaker circuits 27 is connected by electromagnetic coupled with energy i (in vivo) receiving system 11, and energy i (in vivo) receiving system 11 is connected with heart by electrode.
Wireless EGC sensor 25 is arranged near enclosing in chest clothes external heart in wearable mode, realizes the collection to patient's electrocardiosignal, and wireless EGC sensor 25 is connected with external pacemaker circuits 27. External pacemaker circuits 27 comprises signal detection filter circuit 1, control circuit 12, the former limit of non-contact power circuit 7 and non-contact power primary coil 13, wireless EGC sensor 25 is connected with signal detection filter circuit 1, signal detection filter circuit 1 is connected with control circuit 12, control circuit 12 is connected with the former limit of non-contact power circuit 7, and the former limit of non-contact power circuit 7 is connected with non-contact power primary coil 13.
The electrocardiosignal that signal detection filter circuit 1 gathers wireless EGC sensor 25 is processed, and generates corresponding waveform. Wireless EGC sensor 25 detects the original electrocardiographicdigital signal that obtains human bodyu dec, due to original electrocardiographicdigital signalu decVery faint, only have 0.05～5mV, therefore, signal detection filter circuit 1 need to amplify the original electrocardiographicdigital signal gathering. As shown in Figure 3, operational amplifier A MP1 selects OP07 type operational amplifier to the circuit diagram of signal detection filter circuit 1, utilizes operational amplifier A MP1 form second-order low-pass filter circuit and amplify electrocardiosignal. The major function of low-pass filter circuit is the High-frequency Interference outside filtering electrocardiosignal frequency band, to improve system signal noise ratio. The design upper cut-off frequency of low-pass filter circuit is 45Hz. Operational amplifier A MP2 forms second order high-pass filtering circuit, high-pass filtering circuit can the out-of-band low-frequency noise composition of filtering electrocardiosignal, improve system signal noise ratio, the design lower-cut-off frequency of circuit should be 0.03Hz, arrives the desired diagnosis of AHA standard electrocardio equipment related request. The 50Hz power frequency supply producing when avoiding charge in batteries disturbs, and ensures that other signal has no to pass through damply simultaneously, has designed rejection trap, and operational amplifier A MP3 and AMP4 form notch filter circuit. Electrocardiosignal after filter and amplificationu heart, when original electrocardiographicdigital signalu decWhen input voltage is 1mV, electrocardiosignalu heartOutput voltage can reach about 1V, the multiplication factor of signal detection filter circuit 1 is 1000 times of left and right. The maximum input voltage of A/D change-over circuit 3 is 3.3V, electrocardiosignalu heartOutput voltage within the conversion range of A/D change-over circuit 3.
Control circuit 12 forms its core circuit by ARM9 chip, according to the impulse waveform of electrocardiosignal, patient's degree of fatigue is made to judgement accurately. control circuit 12 comprises three-axis gyroscope 2, A/D change-over circuit 3, Data Management Analysis circuit 4, degree of fatigue decision circuitry 5 and output control circuit 6, A/D change-over circuit 3 is connected with signal detection filter circuit 1, three-axis gyroscope 2, A/D change-over circuit 3 is connected with Data Management Analysis circuit 4 respectively, Data Management Analysis circuit 4 is connected with degree of fatigue decision circuitry 5, degree of fatigue decision circuitry 5 is connected with output control circuit 6, output control circuit 6 is connected with the former limit of non-contact power circuit 7, the former limit of non-contact power circuit 7 is connected with non-contact power primary coil 13.
Energy i (in vivo) receiving system 11 comprises non-contact power secondary coil 14, rectification circuit 8, filter circuit 17 and electrode interface 10, non-contact power secondary coil 14 is connected with non-contact power primary coil 13 by electromagnetic coupled, non-contact power secondary coil 14 is connected with rectification circuit 8, rectification circuit 8 is connected with filter circuit 17, filter circuit 17 is connected with electrode interface 10, and electrode interface 10 is connected with electrode. Electrode comprises positive electrode 15 and negative electrode 16, and the input of positive electrode 15 and negative electrode 16 is connected with motor interface 10 respectively, and the output of positive electrode 15 and negative electrode 16 inserts heart inside through heart arter and is hooked on wall of the heart. Therefore, the resistance at heart internal electrode two ends be the load of noncontact power supply circuitsR eq, can realize the stimulation to heart by energy i (in vivo) receiving system 11 to applying voltage on positive electrode 15, negative electrode 16, the voltage magnitude between two electrodes is 1 ~ 5V.
Non-contact power primary coil 13 and non-contact power secondary coil 14 are installed in parallel under left shoulder, the two phase alternating floor human body skin and wearing clothes, the left scapuloanterior (LScA) parallel beneath that coexists relative position, distance between non-contact power primary coil 13 and non-contact power secondary coil 14 is 0.3 ~ 0.5cm, as shown in Figure 5, non-contact power primary coil 13 and non-contact power secondary coil 14 are with cordless transmission magnetic field energy. Non-contact power secondary coil 14 is the coils that form with the coiling of thin copper enamel-covered wire, and rectification circuit 8, filter circuit 17 are surface mount elements, reduces the volume of energy i (in vivo) receiving system 11. Non-contact power secondary coil 14 is along the outward flange coiling of rectification circuit 8, filter circuit 17 and electrode interface 10, and circuit and coil gross thickness, in 2mm, add that the thickness of shell is not more than 3mm, and length and width are in 25mm × 25mm.
Degree of fatigue can be divided into physical fatigue and mental fatigue, and the present invention only pays close attention to physical fatigue, judges degree of fatigue according to the situation of beating that is heart. In the time of patient strenuous exercise, the frequency of heartbeat increases, but amount of blood supply is not enough to meet the needs of human motion, and the waveform of heartbeat is abnormal, now needs pacemaker cardiac stimulus to strengthen the dynamics of pumping blood flow; If patient does not carry out violent motion, when heartbeat is steady, can think that fatigue state is zero, do not need pacemaker to stimulate.
Electrocardiosignal waveform has certain feature, signal detection filter circuit electrocardiosignal waveform after treatment as shown in Figure 4, wherein, P ripple: represent Atrial depolarization ripple; QRS ripple: represent ventricular depolarization complex; T ripple: represent ventricular bipolar ripple; U ripple: follow-up current potential affect P-R interval, the time before Atrial depolarization starts to start to sequences of ventricular depolarization; QRS interval: represent sequences of ventricular depolarization required time; Q-T interval: represent sequences of ventricular depolarization and ventricular bipolar overall process required time; S-T section: represent that sequences of ventricular depolarization finishes to start previous a period of time to multipole, this section of time ventricular muscles, in depolarising state, can reflect the blood supply state of ventricle.
Interior heart rate HR(HeartRate, HR) in fatigue, there is obvious reaction, the principal element that affects HR is physical load, HRV(HeartRateVariability) and refer to the small fluctuating of successive heartbeat interval (R-R interval), measure fatigue state with HRV. Obtain HRV signal, must obtain heartbeat interval, in order to improve the accurate letter that gathers HRV signal, need to measure for two peak-to-peak time differences of adjacent R wave-wave. While studies have found that driver's driving fatigue, the standard of its RR interval can increase gradually with the increase of driving time, and heart rate variability can increase. Therefore, measure the time difference between RR crest here, calculate heart rate variability situation, if the time of RR crest interval is less than normal time range, be judged to be fatigue. Calculate heart rate variability situation and comprise two contents, one is whether RR interval is at zone of reasonableness; Another is successive heartbeat rate fluctuation (HeartRateVariability, HRV). The variation characteristic (acceleration) that is heart rates must be controlled within the specific limits, and patient's HRV characteristic exceeds characteristic range value, means that cardiac function is abnormal, need to open pacemaker stimulatory function.
In addition, judge arrhythmia cordis (any one such as origin position, frequency, the rhythm and pace of moving things, conduction that refers to heartbeat occurs abnormal) by electrocardiogram, the origin position of normal heart beat should be sinoatrial node, is mainly contained tachycardia, bradycardia, cardiac arrhythmia and is stopped fighting by the arrhythmia cordis of the abnormal exciting generation of sinoatrial node. Judgement draws ARR phenomenon, judges according to phenomenon the stimulation voltage that pacemaker need to provideu o Amplitude size and conducting stimulation timet tot. Wherein stimulation voltageu o Duration be conducting stimulation timet tot。
Operation principle of the present invention is: wireless EGC sensor 25 gathers user's electrocardiosignal, and signal detection filter circuit 1 utilizes the operational amplifier in it faint electrocardiosignal amplification, filtering, voltage lifting finally to be generated to the waveform of EGC analog signal; A/D change-over circuit 3 converts EGC analog signal waveform to data signal and delivers to Data Management Analysis circuit 4 and carry out analyzing and processing, judged the state of heart according to the result of electrocardiosignal by degree of fatigue decision circuitry 5, output control circuit 6 is controlled the former limit of non-contact power circuit 7, to non-contact power secondary coil 14 transferring energies, after energy i (in vivo) receiving system 11 rectifying and wave-filterings, implement pacing stimulation by electrode pair heart by non-contact power primary coil 13.
The present invention can realize by three-axis gyroscope 2 the active pace-making of pacemaker. When under the motion states such as patient stands suddenly, running, heart blood supply amount does not temporarily show not enough state, iff the method that adopts passive detection electrocardiosignal, the stimulus signal intensity of pacemaker is in seconds difficult to reach motion needs, and the even abnormal extreme case of heartbeat of palpitation and short breath may appear in patient. The present invention adopts three-axis gyroscope 2 to measure position, motion track and the acceleration of 6 directions of three reference axis of three dimensions simultaneously, and the signal that three-axis gyroscope 2 is obtained delivers to data processing and analysis circuit 4 is processed. When detecting that health moving state occurs, strengthen immediately cardiac pacing stimulus signal, increase the voltage magnitude stimulating and extend the conducting stimulation time of electrocardio pulset tot. This method that initiatively judges human motion state can be within 1 second rapid cardiac stimulus function, can prevent because the situation that patient gets up suddenly or the cerebral blood supply insufficiency that caused to standing by sitting suddenly is even died suddenly occurs.
Circuit voltage waveform of the present invention as shown in Figure 6. The former limit of non-contact power circuit 7 is powered by battery 9. Detect battery 9 and supply with the terminal voltage of the former limit of non-contact power circuit 7 by external pacemaker circuits 27u i And electric currenti i , obtain powerP i =u i ×i i . Draw the efficiency of transmission approximation of noncontact circuit according to circuit structureη, positive electrode 15 and negative electrode 16 two ends loads are heart resistance, can be equivalent to resistanceR eq, this resistance is directly measured and is obtained in the time that positive electrode 15 and negative electrode 16 are installed,P i =u i ×i i =u o 2 /R eq, can determine thus two voltages between electrodeu o Amplitude size, the voltage between electrodeu o Amplitude is controlled between 1 ~ 5V. Energy i (in vivo) receiving system 11 of the present invention does not need direct-detection heart electrode both sides voltage, do not need to install additional the telecommunication circuit matching with external pacemaker circuits 27 yet, compared with built-in dual chamber pacemaker in the past, the volume of energy i (in vivo) receiving system 11 is reduced to original below 1/4, thickness is reduced to original below 1/3, and energy i (in vivo) receiving system 11 can forever be worked and not need to change after being implanted.
The former limit of non-contact power circuit 7 is selected the DC-DC converter circuit of full-bridge band transformer isolation, converts direct current to high-frequency alternating current (65kHz) by single-phase full bridge circuit.u dr1Withu dr2For driving full-bridge circuit drive signal waveform.u pFor the voltage waveform at non-contact power primary coil 13 two ends. Therefore, drive the pulse width of full-bridge circuit drive signal waveform and the ratio of cycle time to be called dutycyclet on. The conducting stimulation time of an i.e. electrocardio pulse of the duration of electrode output voltaget totRepresent that non-contact power circuit supplies power to the total time of cutting off non-contact power circuit supply from starting,t totBe generally 10ms ~ 100ms. Output control circuit 6 is by the dutycycle of the switching device of the control former limit of non-contact power circuit 7t onTo change the output voltage of electrode, output control circuit 6 is by judging and controlling the total power-on time of the former limit of non-contact power circuit 7, to change conducting stimulation timet tot。
Degree of fatigue decision circuitry 5 judges that the method for heart fatigue is: the time difference of measuring the RR crest (between two peak value R) of electrocardiosignal waveform, the variation property that calculates heart rate, is judged to be fatigue if the time of RR crest interval is greater than normal time range (generally getting 1 second). Judgement state can be divided into two kinds of situations: if human body in heart fatigue state, can judge that amount of blood supply is not enough to meet the needs of body function, start pacemaker; Otherwise fatigue level of human body is less, closes pacemaker or make it to be operated in faint stimulation state.
The fatigue level of human body that degree of fatigue decision circuitry 5 judges is sent to output control circuit 6, and in the time of human-body fatigue, output control circuit 6, to the former limit of non-contact power circuit 7 pipage control voltages, stimulates heart. Degree of fatigue is larger, increases dutycyclet on, the voltage magnitude of stimulation is just larger, increases the conducting stimulation time of electrocardio pulse simultaneouslyt tot. Degree of fatigue is less, reduces dutycyclet on, the voltage magnitude of stimulation just reduces, and shortens the conducting stimulation time of electrocardio pulse simultaneouslyt tot; If human body is in having a rest or sleep state, heartbeat is steady, it is not stimulated.
The above; only for preferably detailed description of the invention of the present invention, but protection scope of the present invention is not limited to this, is anyly familiar with in technical scope that those skilled in the art disclose in the present invention; the variation that can expect easily or replacement, within all should being encompassed in protection scope of the present invention.

Claims (10)

1. one kind has the pacemaker of non-contact power function, it is characterized in that, comprise battery (9), external pacemaker circuits (27) and energy i (in vivo) receiving system (11), battery (9) is connected with external pacemaker circuits (27), external pacemaker circuits (27) outer end is provided with wireless EGC sensor (25), wireless EGC sensor (25) is arranged on external heart place, energy i (in vivo) receiving system (11) is arranged in left shoulder skin, external pacemaker circuits (27) is connected by electromagnetic coupled with energy i (in vivo) receiving system (11), energy i (in vivo) receiving system (11) is connected with heart by electrode.
2. the pacemaker with non-contact power function according to claim 1, it is characterized in that, described energy i (in vivo) receiving system (11) comprises non-contact power secondary coil (14), rectification circuit (8), filter circuit (17) and electrode interface (10), non-contact power secondary coil (14) is connected with non-contact power primary coil (13) by electromagnetic coupled, non-contact power secondary coil (14) is connected with rectification circuit (8), rectification circuit (8) is connected with filter circuit (17), filter circuit (17) is connected with electrode interface (10), electrode interface (10) is connected with electrode.
3. the pacemaker with non-contact power function according to claim 1 and 2, it is characterized in that, described external pacemaker circuits (27) comprises signal detection filter circuit (1), control circuit (12), the former limit of non-contact power circuit (7) and non-contact power primary coil (13), wireless EGC sensor (25) is connected with signal detection filter circuit (1), signal detection filter circuit (1) is connected with control circuit (12), control circuit (12) is connected with the former limit of non-contact power circuit (7), the former limit of non-contact power circuit (7) is connected with non-contact power primary coil (13).
4. the pacemaker with non-contact power function according to claim 3, it is characterized in that, described control circuit (12) comprises three-axis gyroscope (2), A/D change-over circuit (3), Data Management Analysis circuit (4), degree of fatigue decision circuitry (5) and output control circuit (6), A/D change-over circuit (3) is connected with signal detection filter circuit (1), three-axis gyroscope (2), A/D change-over circuit (3) is connected with Data Management Analysis circuit (4) respectively, Data Management Analysis circuit (4) is connected with degree of fatigue decision circuitry (5), degree of fatigue decision circuitry (5) is connected with output control circuit (6), output control circuit (6) is connected with the former limit of non-contact power circuit (7).
5. the pacemaker with non-contact power function according to claim 3, it is characterized in that, described wireless EGC sensor (25) is arranged near enclosing in chest clothes external heart in wearable mode, non-contact power primary coil (13) and non-contact power secondary coil (14) are installed in parallel under left shoulder, distance between non-contact power primary coil (13) and non-contact power secondary coil (14) is between 0.3 ~ 0.5cm, non-contact power primary coil (13) and non-contact power secondary coil (14) are with cordless transmission magnetic field energy.
6. the pacemaker with non-contact power function according to claim 3, it is characterized in that, described non-contact power secondary coil (14) is the coil forming with the coiling of thin copper enamel-covered wire, and rectification circuit (8) and filter circuit (17) are surface mount elements.
7. the pacemaker with non-contact power function according to claim 4, it is characterized in that, its operation principle is: wireless EGC sensor (25) gathers user's electrocardiosignal, and signal detection filter circuit (1) utilizes the operational amplifier in it faint electrocardiosignal amplification, filtering, voltage lifting finally to be generated to the waveform of EGC analog signal; A/D change-over circuit (3) converts EGC analog signal waveform to data signal and delivers to Data Management Analysis circuit (4) and carry out analyzing and processing, judged the state of heart according to the result of electrocardiosignal by degree of fatigue decision circuitry (5), output control circuit (6) is controlled the dutycycle of the switching device of the former limit of non-contact power circuit (7)t on, to non-contact power secondary coil (14) transferring energy, after energy i (in vivo) receiving system (11) rectifying and wave-filtering, implement pacing stimulation by electrode pair heart by non-contact power primary coil (13).
8. the pacemaker with non-contact power function according to claim 7, it is characterized in that, described degree of fatigue decision circuitry (5) judges the method for heart fatigue: measure the time difference between electrocardiosignal waveform RR crest, the variation property that calculates heart rate, is judged to be fatigue if the time of RR crest interval is greater than normal time range.
9. the pacemaker with non-contact power function according to claim 7, is characterized in that, described output control circuit (6) is by controlling the dutycycle of the former limit of non-contact power circuit (7) switching devicet onChange the output voltage of electrodeu o , output control circuit (6) is by judging and controlling the total power-on time of the former limit of non-contact power circuit (7), to change electrode output voltageu o Duration, the duration is the conducting stimulation time of an electrocardio pulset tot。
10. the pacemaker with non-contact power function according to claim 7, it is characterized in that, described three-axis gyroscope (2) is measured position, motion track and the acceleration of 6 directions of three reference axis of three dimensions, the signal obtaining is delivered to data processing and analysis circuit (4) to be processed and carries out analyzing and processing, in the time detecting that health moves, output control circuit (6) is strengthened cardiac pacing stimulus signal immediately, increases the voltage magnitude stimulating and extends the conducting stimulation time of electrocardio pulset tot。
CN201610069613.XA 2016-02-02 2016-02-02 Pacemaker with non-contact power function Active CN105597233B (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
CN201610069613.XA CN105597233B (en) 2016-02-02 2016-02-02 Pacemaker with non-contact power function

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
CN201610069613.XA CN105597233B (en) 2016-02-02 2016-02-02 Pacemaker with non-contact power function

Publications (2)

Publication Number Publication Date
CN105597233A true CN105597233A (en) 2016-05-25
CN105597233B CN105597233B (en) 2017-12-22

Family

ID=55977924

Family Applications (1)

Application Number Title Priority Date Filing Date
CN201610069613.XA Active CN105597233B (en) 2016-02-02 2016-02-02 Pacemaker with non-contact power function

Country Status (1)

Country Link
CN (1) CN105597233B (en)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106073750A (en) * 2016-08-29 2016-11-09 廖晓莉 Ventricle blood supply abnormal detector and the indirect acquiring and processing method of heart pulse wave data
CN114983426A (en) * 2022-04-22 2022-09-02 清华大学 Electrophysiological signal wireless detection method and system based on electromagnetic coupling principle

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN102895734A (en) * 2012-10-30 2013-01-30 河南工程学院 Two-path dual-active non-contact power system for cardiac pacemaker
US20140100622A1 (en) * 2012-10-10 2014-04-10 Physio-Control, Inc. External defibrillation with automatic post-shock anti-tachycardia (apsat) pacing
US20140343349A1 (en) * 2013-05-20 2014-11-20 Mark Klingler Borsody Coordinating emergency treatment of cardiac dysfunction and non-cardiac neural dysfunction
CN205307613U (en) * 2016-02-02 2016-06-15 河南工程学院 Cardiac pacemaker with non -contact power supply function

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20140100622A1 (en) * 2012-10-10 2014-04-10 Physio-Control, Inc. External defibrillation with automatic post-shock anti-tachycardia (apsat) pacing
CN102895734A (en) * 2012-10-30 2013-01-30 河南工程学院 Two-path dual-active non-contact power system for cardiac pacemaker
US20140343349A1 (en) * 2013-05-20 2014-11-20 Mark Klingler Borsody Coordinating emergency treatment of cardiac dysfunction and non-cardiac neural dysfunction
CN205307613U (en) * 2016-02-02 2016-06-15 河南工程学院 Cardiac pacemaker with non -contact power supply function

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106073750A (en) * 2016-08-29 2016-11-09 廖晓莉 Ventricle blood supply abnormal detector and the indirect acquiring and processing method of heart pulse wave data
CN106073750B (en) * 2016-08-29 2023-07-28 廖晓莉 Ventricular blood supply abnormality detection device and indirect collection processing method of heart pulse wave data
CN114983426A (en) * 2022-04-22 2022-09-02 清华大学 Electrophysiological signal wireless detection method and system based on electromagnetic coupling principle

Also Published As

Publication number Publication date
CN105597233B (en) 2017-12-22

Similar Documents

Publication Publication Date Title
US11813470B2 (en) Multi-axis coil for implantable medical device
CN103118741B (en) Wireless heart is beaten sensing
US7200440B2 (en) Cardiac cycle synchronized sampling of impedance signal
US5174286A (en) Sensor for right ventricular and thoracic volumes using the trailing edge value of a generated pulse
US9956414B2 (en) Temporal configuration of a motion sensor in an implantable medical device
US7054686B2 (en) Pulsewidth electrical stimulation
CN109069048A (en) Cardiac electric signals multi-threshold sensing in cardiovascular outer Is implantable cardioverter defibrillator
US20180212451A1 (en) Recharge of implanted medical devices
US8896462B2 (en) Methods for low power communication in an implantable medical device
EP2133117A1 (en) Thoracic or intracardiac impedance selecting vector automatically
US8571641B2 (en) Apparatus and method for processing physiological measurement values
US20080058669A1 (en) Methods for measuring impedances associated with the heart
US20090264783A1 (en) Systems and methods for improved atrial fibrillation (af) monitoring
EP1365836A2 (en) Cardiac rhythm management system using time-domain heart rate variability indicia
US6287263B1 (en) System for processing bursted amplitude modulated signals using an impedance sensor
EP3044880A1 (en) Ultra low power interface using adaptive successive approximation register
CN105597233B (en) Pacemaker with non-contact power function
US8594788B2 (en) Cardiac stimulator for delivery of cardiac contractility modulation therapy
CN205307613U (en) Cardiac pacemaker with non -contact power supply function
CN108092544A (en) A kind of energy resource supply device for collecting organism kinergety
US8798746B2 (en) Automatic mechanical alternans detection
CN201308717Y (en) Discharge energy compensation circuit for external defibrillator
US20130013011A1 (en) Implantable medical device for pulse generation and with means for collecting and storing energy during a recharge phase
Chen et al. Noninvasive ambulatory monitoring of the electric and mechanical function of heart with a multifunction wearable sensor
CN106938121A (en) External defibrillation pacing system

Legal Events

Date Code Title Description
C06 Publication
PB01 Publication
C10 Entry into substantive examination
SE01 Entry into force of request for substantive examination
CB03 Change of inventor or designer information
CB03 Change of inventor or designer information

Inventor after: Zhou Chenghu

Inventor after: Zhu Yongbiao

Inventor after: Ma Chuxin

Inventor after: Li Baisong

Inventor after: Yuan Xun

Inventor after: Xing Weiwei

Inventor after: Liu Lei

Inventor after: Jia Lidong

Inventor after: Wu Hongbo

Inventor after: Wu Tao

Inventor after: Zhang Kun

Inventor after: Li Xiaokui

Inventor after: Chen Bingyang

Inventor after: Wang Zhentao

Inventor after: Wang Jing

Inventor after: Luo Jiming

Inventor after: Chen Chaoyang

Inventor after: Zhang Qiuhui

Inventor after: Jia Zhenzhen

Inventor after: Zhang Feifei

Inventor after: Xu Fengkuan

Inventor after: Zhou Jianwei

Inventor before: Zhou Chenghu

Inventor before: Li Baisong

Inventor before: Yuan Xun

Inventor before: Xing Weiwei

Inventor before: Liu Lei

Inventor before: Jia Lidong

Inventor before: Wu Hongbo

Inventor before: Wu Tao

Inventor before: Zhang Kun

Inventor before: Chen Bingyang

Inventor before: Wang Zhentao

Inventor before: Chen Chaoyang

Inventor before: Wang Jing

Inventor before: Zhang Qiuhui

Inventor before: Jia Zhenzhen

Inventor before: Zhang Feifei

Inventor before: Xu Fengkuan

Inventor before: Zhou Jianwei

Inventor before: Zhu Yongbiao

Inventor before: Ma Chuxin

GR01 Patent grant
GR01 Patent grant