CN220046845U - Heart contractile force regulator capable of removing flutter - Google Patents
Heart contractile force regulator capable of removing flutter Download PDFInfo
- Publication number
- CN220046845U CN220046845U CN202223004572.6U CN202223004572U CN220046845U CN 220046845 U CN220046845 U CN 220046845U CN 202223004572 U CN202223004572 U CN 202223004572U CN 220046845 U CN220046845 U CN 220046845U
- Authority
- CN
- China
- Prior art keywords
- ventricular
- electrode
- heart
- mcu processor
- pulse signal
- 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.)
- Active
Links
- 230000002861 ventricular Effects 0.000 claims abstract description 91
- 230000000638 stimulation Effects 0.000 claims abstract description 30
- 230000001746 atrial effect Effects 0.000 claims abstract description 12
- 238000012544 monitoring process Methods 0.000 claims abstract description 7
- 238000004891 communication Methods 0.000 claims abstract description 5
- 230000005540 biological transmission Effects 0.000 claims description 11
- 210000005241 right ventricle Anatomy 0.000 claims description 9
- 230000000747 cardiac effect Effects 0.000 claims description 8
- WHXSMMKQMYFTQS-UHFFFAOYSA-N Lithium Chemical compound [Li] WHXSMMKQMYFTQS-UHFFFAOYSA-N 0.000 claims description 4
- 238000002001 electrophysiology Methods 0.000 claims description 4
- 230000007831 electrophysiology Effects 0.000 claims description 4
- 229910052744 lithium Inorganic materials 0.000 claims description 4
- 208000003663 ventricular fibrillation Diseases 0.000 abstract description 28
- 206010019280 Heart failures Diseases 0.000 abstract description 17
- 206010044565 Tremor Diseases 0.000 abstract description 3
- 238000000034 method Methods 0.000 description 12
- 206010003119 arrhythmia Diseases 0.000 description 8
- 230000006793 arrhythmia Effects 0.000 description 8
- 206010047302 ventricular tachycardia Diseases 0.000 description 8
- 230000000694 effects Effects 0.000 description 7
- 230000010247 heart contraction Effects 0.000 description 7
- 230000036279 refractory period Effects 0.000 description 7
- 230000001105 regulatory effect Effects 0.000 description 7
- 238000011282 treatment Methods 0.000 description 7
- 230000008602 contraction Effects 0.000 description 5
- 230000005284 excitation Effects 0.000 description 5
- 238000002513 implantation Methods 0.000 description 5
- 230000002107 myocardial effect Effects 0.000 description 5
- 210000000596 ventricular septum Anatomy 0.000 description 5
- 230000004913 activation Effects 0.000 description 4
- 230000033228 biological regulation Effects 0.000 description 4
- 238000011084 recovery Methods 0.000 description 4
- 206010042434 Sudden death Diseases 0.000 description 3
- 206010047281 Ventricular arrhythmia Diseases 0.000 description 3
- 230000034994 death Effects 0.000 description 3
- 231100000517 death Toxicity 0.000 description 3
- 229940079593 drug Drugs 0.000 description 3
- 239000003814 drug Substances 0.000 description 3
- 230000004217 heart function Effects 0.000 description 3
- 230000001976 improved effect Effects 0.000 description 3
- 210000004165 myocardium Anatomy 0.000 description 3
- 238000000306 qrs interval Methods 0.000 description 3
- 230000033764 rhythmic process Effects 0.000 description 3
- 238000012360 testing method Methods 0.000 description 3
- 210000003462 vein Anatomy 0.000 description 3
- 206010008531 Chills Diseases 0.000 description 2
- 206010061592 cardiac fibrillation Diseases 0.000 description 2
- 238000009125 cardiac resynchronization therapy Methods 0.000 description 2
- 230000002964 excitative effect Effects 0.000 description 2
- 230000002600 fibrillogenic effect Effects 0.000 description 2
- 230000006870 function Effects 0.000 description 2
- 238000001727 in vivo Methods 0.000 description 2
- 230000000977 initiatory effect Effects 0.000 description 2
- 230000004936 stimulating effect Effects 0.000 description 2
- 201000006474 Brain Ischemia Diseases 0.000 description 1
- BHPQYMZQTOCNFJ-UHFFFAOYSA-N Calcium cation Chemical compound [Ca+2] BHPQYMZQTOCNFJ-UHFFFAOYSA-N 0.000 description 1
- 206010007558 Cardiac failure chronic Diseases 0.000 description 1
- 241000270722 Crocodylidae Species 0.000 description 1
- 208000033988 Device pacing issue Diseases 0.000 description 1
- 206010061818 Disease progression Diseases 0.000 description 1
- 239000004593 Epoxy Substances 0.000 description 1
- 208000010496 Heart Arrest Diseases 0.000 description 1
- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 description 1
- 230000002159 abnormal effect Effects 0.000 description 1
- 238000000594 atomic force spectroscopy Methods 0.000 description 1
- 210000002048 axillary vein Anatomy 0.000 description 1
- 230000002051 biphasic effect Effects 0.000 description 1
- 230000036770 blood supply Effects 0.000 description 1
- 229910001424 calcium ion Inorganic materials 0.000 description 1
- 210000000748 cardiovascular system Anatomy 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 208000035850 clinical syndrome Diseases 0.000 description 1
- 230000001010 compromised effect Effects 0.000 description 1
- LNNWVNGFPYWNQE-GMIGKAJZSA-N desomorphine Chemical compound C1C2=CC=C(O)C3=C2[C@]24CCN(C)[C@H]1[C@@H]2CCC[C@@H]4O3 LNNWVNGFPYWNQE-GMIGKAJZSA-N 0.000 description 1
- 230000006866 deterioration Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 201000010099 disease Diseases 0.000 description 1
- 230000005750 disease progression Effects 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 238000002565 electrocardiography Methods 0.000 description 1
- 230000002708 enhancing effect Effects 0.000 description 1
- 208000019622 heart disease Diseases 0.000 description 1
- 238000000338 in vitro Methods 0.000 description 1
- 230000006698 induction Effects 0.000 description 1
- 230000001939 inductive effect Effects 0.000 description 1
- 238000003780 insertion Methods 0.000 description 1
- 230000037431 insertion Effects 0.000 description 1
- 231100000518 lethal Toxicity 0.000 description 1
- 230000001665 lethal effect Effects 0.000 description 1
- 230000007774 longterm Effects 0.000 description 1
- 230000003211 malignant effect Effects 0.000 description 1
- 238000002483 medication Methods 0.000 description 1
- 230000035778 pathophysiological process Effects 0.000 description 1
- 230000026731 phosphorylation Effects 0.000 description 1
- 238000006366 phosphorylation reaction Methods 0.000 description 1
- 230000035790 physiological processes and functions Effects 0.000 description 1
- 239000002952 polymeric resin Substances 0.000 description 1
- 238000010837 poor prognosis Methods 0.000 description 1
- 230000000750 progressive effect Effects 0.000 description 1
- 102000004169 proteins and genes Human genes 0.000 description 1
- 108090000623 proteins and genes Proteins 0.000 description 1
- 230000002441 reversible effect Effects 0.000 description 1
- 210000005245 right atrium Anatomy 0.000 description 1
- 230000035939 shock Effects 0.000 description 1
- 230000008054 signal transmission Effects 0.000 description 1
- 210000001321 subclavian vein Anatomy 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 230000004083 survival effect Effects 0.000 description 1
- 229920003002 synthetic resin Polymers 0.000 description 1
- 230000009885 systemic effect Effects 0.000 description 1
- 238000011285 therapeutic regimen Methods 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
- 229910052719 titanium Inorganic materials 0.000 description 1
- 239000010936 titanium Substances 0.000 description 1
Abstract
The utility model provides a heart contractile force adjusting device capable of removing tremors, which comprises: the device comprises a spiral electrode, an MCU processor, a pulse signal generator and a power supply, wherein the spiral electrode comprises a ventricular electrode and an atrial electrode which are implanted in a heart, and the atrial electrode is used for sensing a heart electrophysiological signal, monitoring a ventricular electrocardiosignal by the ventricular electrode and sending an electric stimulation pulse signal to the pulse heart; the MCU processor is in communication connection with the pulse spiral electrode and is used for generating a control signal; the pulse signal generator generates an electric stimulation pulse signal according to a control signal of the pulse MCU processor and sends the electric stimulation pulse signal to the pulse heart through the pulse spiral electrode; the power supply is used for providing electric energy. When the spiral electrode detects ventricular fibrillation signals, the MCU processor controls the pulse signal generator to automatically output defibrillation electric signals to defibrillate the heart in time, so that when serious complications such as ventricular fibrillation and the like of a heart failure patient are prevented, the defibrillation cannot be performed in time, and the optimal rescue time is missed.
Description
Technical Field
The utility model relates to the technical field of medical equipment, in particular to a heart contractile force adjusting device capable of removing tremors.
Background
Chronic heart failure is a pathophysiological process of progressive heart deterioration, affecting clinical syndrome of over 2600 tens of thousands of patients worldwide, one of the most difficult diseases to overcome by the cardiovascular system, and usually drug treatment cannot reverse disease progression.
The total prevalence rate of heart failure in China is about 1.26% at present. Heart failure patients often have a poor prognosis, with 65% of patients dying within 60 months. About 30% of patients with heart failure have wide QRS intervals, and heart function is generally improved by Cardiac Resynchronization Therapy (CRT), but 70% of patients with narrow QRS intervals have no better therapeutic regimen.
About half of deaths in heart disease patients are sudden death (i.e., sudden death). The most common cause of sudden death is severe ventricular arrhythmias, such as ventricular fibrillation and ventricular tachycardia. These severe arrhythmias often are not predicted before they occur, nor are the medications able to completely prevent them. These arrhythmias must be terminated immediately, but even in hospitals, treatment is sometimes not performed because the heart does not actually shoot when ventricular fibrillation occurs, and brain ischemia occurs for more than 6 seconds. If the heart stops shooting for more than 5 minutes, the chance of success of rescue is less than 20%.
Clinically, these severe arrhythmias are terminated at any time by implantation of an in vivo automated defibrillator (ICD), and numerous studies have shown that ICD implantation is much more therapeutically effective than medication. The ICD can detect and judge the type of severe ventricular arrhythmia of the patient at any time and give different treatments, thereby achieving the purposes of stopping arrhythmia and saving the life of the patient.
Since ventricular fibrillation is a serious complication of heart failure, a part of patients with severe heart failure need to regulate the heart contractility and prevent ventricular fibrillation, and a heart contractility regulating device and an in-vivo automatic defibrillator (ICD) need to be implanted clinically respectively, on the one hand, the operation cost of implanting two devices is high, and on the other hand, the two devices are implanted subcutaneously, which also causes inconvenience to the daily activities of the patients.
The following problems exist in the use of existing heart contraction regulators:
the clinically used heart contraction regulator has no defibrillation function, the heart failure patient is relatively easy to generate serious complications of life threatening such as ventricular fibrillation, the occurrence of ventricular fibrillation is generally not predicted, the ventricular fibrillation must be immediately stopped when the ventricular fibrillation occurs, and the defibrillation is not timely and easily causes the death of the patient.
Clinically, the heart contraction force regulator cannot be started at fixed time, and the heart is overloaded due to long-term continuous heart contraction force regulation, so that other complications are caused.
Disclosure of Invention
The utility model aims to solve the technical problem of improving the performance of a heart contraction force regulator, and provides a heart contraction force regulating device capable of removing the chatter.
A decontaminable heart contractility adjusting device according to an embodiment of the present utility model includes:
the spiral electrode comprises a ventricular electrode and an atrial electrode which are implanted in the heart, wherein the atrial electrode is used for sensing cardiac electrophysiology signals, the ventricular electrode is used for monitoring ventricular electrocardiosignals and sending electrical stimulation pulse signals to the heart;
the MCU processor is in communication connection with the spiral electrode and is used for generating a control signal based on the ventricular electrocardiosignal;
the pulse signal generator is in communication connection with the MCU processor and the spiral electrode, and is used for generating an electric stimulation pulse signal according to a control signal of the MCU processor and sending the electric stimulation pulse signal to the heart through the spiral electrode;
and the power supply is used for providing electric energy for the spiral electrode, the MCU processor and the pulse signal generator.
According to the heart contractile force adjusting device capable of removing the tremors, the stimulating electrode is implanted into the right ventricle interval part of the patient, when the ventricular fibrillation signal is detected by the spiral electrode, the MCU processor controls the pulse signal generator to automatically output the defibrillation electric signal, the heart is timely defibrillated, and when serious complications such as ventricular fibrillation and the like of a heart failure patient are prevented, the defibrillation cannot be timely performed, and the optimal rescue time is missed.
According to some embodiments of the utility model, the ventricular electrode comprises: the device comprises a first ventricular electrode and a second ventricular electrode, wherein the first ventricular electrode and the second ventricular electrode are implanted in a right ventricle space and are distributed at preset distance, one of the first ventricular electrode and the second ventricular electrode is used for monitoring ventricular electrocardiosignals, and the other of the first ventricular electrode and the second ventricular electrode is used for sending electrical stimulation pulse signals.
In some embodiments of the present utility model, the first ventricular electrode and the second ventricular electrode are arranged at a predetermined distance interval in the up-down direction at the right ventricular interval, the predetermined distance being not less than 2cm.
According to some embodiments of the utility model, the MCU processor controls the second ventricular electrode to send electrical stimulation to the heart after a preset time of QRS onset when the first ventricular electrode monitors local electrical activity, to regulate the contractile force of the heart.
In some embodiments of the utility model, the MCU processor controls the pulse signal generator to output a stimulus having a frequency greater than a preset value through the second ventricular electrode when the first ventricular electrode monitors ventricular tachycardia.
According to some embodiments of the utility model, the MCU processor controls the pulse signal generator to deliver current for defibrillation if ventricular tachycardia continues to occur or ventricular fibrillation signals are detected by the first ventricular electrode.
In some embodiments of the utility model, the first ventricular electrode continuously monitors ventricular electrocardiographic signals in real-time.
According to some embodiments of the utility model, the MCU processor has a timing device, with setup time control of start-up and run time by the timing device.
In some embodiments of the present utility model, the MCU processor is communicatively connected to a remote configuration system via a data transmission configuration module, and the remote configuration system sets the timing device via the data transmission configuration module.
According to some embodiments of the utility model, the power source is a lithium battery that supports wireless charging.
Drawings
FIG. 1 is a schematic illustration of a combination of a refuelable heart contractile force adjustment device in accordance with an embodiment of the present utility model;
FIG. 2 is a schematic illustration of a spiral electrode implantation in accordance with an embodiment of the present utility model;
fig. 3 is a schematic diagram of the working principle of the spiral electrode according to the embodiment of the utility model.
Reference numerals:
the control device 100 is configured to control the control device,
the spiral electrode 10, the first ventricular electrode 111, the second ventricular electrode 112,
the MCU processor 20, the pulse signal generator 30, the power supply 40,
the data transmission configuration module 50, the remote configuration system 600.
Detailed Description
In order to further describe the technical means and effects adopted by the present utility model for achieving the intended purpose, the following detailed description of the present utility model is given with reference to the accompanying drawings and preferred embodiments.
The steps of the method flow described in the specification and the flow chart shown in the drawings of the specification are not necessarily strictly executed according to step numbers, and the execution order of the steps of the method may be changed. Moreover, some steps may be omitted, multiple steps may be combined into one step to be performed, and/or one step may be decomposed into multiple steps to be performed.
As described in the background section, when heart failure occurs, arrhythmia is likely to occur in a patient due to a change in cardiac structure, including ventricular fibrillation, which is one of the lethal malignant arrhythmias, manifesting as disordered fibrillation, failing to produce effective systole and diastole to ensure systemic blood supply, i.e., functional cardiac arrest, and if defibrillation is not timely performed, life of the patient is compromised. Some existing heart contraction regulators have no defibrillation function, and when heart failure patients have serious complications such as ventricular fibrillation, the heart cannot be defibrillated in time, so that the lives of the patients can be endangered.
Thus, the present utility model proposes a deconstructable heart contractile force adjustment device 100, as shown in fig. 1, the adjustment device 100 comprising: the spiral electrode 10, the MCU processor 20, the pulse signal generator 30 and the power supply 40.
The spiral electrode 10 is implanted in the heart for sensing cardiac electrophysiology signals, monitoring ventricular electrocardiography signals, and delivering electrical stimulation pulse signals to the heart. The MCU processor 20 is communicatively connected to the spiral electrode 10 for generating control signals based on ventricular cardiac electrical signals. The pulse signal generator 30 is communicatively connected to both the MCU processor 20 and the spiral electrode 10 for generating an electrical stimulation pulse signal according to the control signal of the MCU processor 20 and transmitting to the heart through the spiral electrode 10. The power supply 40 is used for supplying power to the spiral electrode 10, the MCU processor 20 and the pulse signal generator 30.
According to the device 100 for regulating heart contractile force capable of removing the heart according to the embodiment of the utility model, by implanting the stimulating electrode into the right ventricular septum of the patient, when the ventricular fibrillation signal is detected by the spiral electrode 10, the MCU processor 20 controls the pulse signal generator 30 to automatically output the defibrillation electric signal, thereby timely removing the heart, and preventing the heart failure patient from being incapable of timely removing the heart when serious complications such as ventricular fibrillation occur, and the optimal rescue time is missed.
According to some embodiments of the utility model, the spiral electrode 10 comprises: a ventricular electrode and an atrial electrode, the ventricular electrode comprising: the first ventricular electrode 111 and the second ventricular electrode 112 are implanted in the right ventricle at intervals, and are arranged at intervals of a preset distance, one of the first ventricular electrode 111 and the second ventricular electrode 112 is used for monitoring ventricular electrocardiosignals, and the other is used for sending an electric stimulation pulse signal. The atrial electrode is used for sensing cardiac electrophysiology signals.
In some embodiments of the present utility model, as shown in fig. 2, the first and second ventricular electrodes 111 and 112 are arranged at a preset distance interval in the up-down direction at the right ventricular interval, the preset distance being not less than 2cm.
According to some embodiments of the present utility model, MCU processor 20 has a timing device by which the start-up and run times are controlled by the set time of the timing device. That is, the MCU processor 20 is integrated with a timing device that allows for free interval time setting, timing of activation of the systolic force modulation, such as activation of one hour every three hours, thereby giving the patient a treatment interval that allows the heart a certain rest recovery period, preventing complications.
In some embodiments of the present utility model, MCU processor 20 is communicatively coupled to remote configuration system 600 via data transmission configuration module 50, and remote configuration system 600 sets the timing device via data transmission configuration module 50.
According to the heart contractile force adjusting method of the embodiment of the present utility model, the adjusting method uses the above-described shivering heart contractile force adjusting device 100 to adjust the heart contractile force.
According to some embodiments of the utility model, the adjusting method comprises:
when the first ventricular electrode 111 monitors local electrical activity, after a preset time from the initiation of the QRS wave, the MCU processor 20 controls the second ventricular electrode 112 to deliver electrical stimulation to the heart to adjust the contractility of the heart. For example, after the first ventricular electrode 111 on the upper side of the right ventricle monitors local electrical activity, the second ventricular electrode 112 on the lower side of the right ventricle sends an electrical stimulation signal 30 milliseconds after the initiation of the QRS wave, by which the contractile force of the heart is regulated.
A defibrillation method according to an embodiment of the present utility model performs defibrillation using the defibrillation-contractile force adjusting apparatus 100 as described above.
According to some embodiments of the utility model, a defibrillation method includes:
when the first ventricular electrode 111 monitors ventricular tachycardia, the MCU processor 20 controls the pulse signal generator 30 to output a stimulus having a frequency greater than a preset value through the second ventricular electrode 112;
if ventricular tachycardia continues to occur or ventricular fibrillation signals are detected by the first ventricular electrode 111, the MCU processor 20 controls the pulse signal generator 30 to deliver current for defibrillation.
When the first ventricular electrode 111 detects a ventricular fibrillation signal, the ventricular fibrillation signal is fed back to the MCU processor 20, and the MCU processor 20 controls the pulse signal generator 30 to output a defibrillation signal from the second ventricular electrode 112, so as to start a defibrillation procedure.
In some embodiments of the utility model, the first ventricular electrode 111 continuously monitors ventricular cardiac signals in real-time. That is, the first ventricular electrode 111 is continuously monitored without interruption, so that the second ventricular electrode 112 can accurately apply pulse stimulation to the cardiac muscle in the absolute refractory period to enhance the myocardial contractility, and the stimulation to the cardiac muscle in the refractory period belongs to non-excitatory stimulation, does not interrupt the normal electric signal transmission sequence of the heart, and does not trigger ventricular arrhythmia.
The following describes in detail a shivering heart contractile force adjustment device 100 and a method of operating the same in accordance with the present utility model in one particular embodiment with reference to the accompanying drawings. It is to be understood that the following description is exemplary only and is not to be construed as limiting the utility model in any way
As shown in fig. 1 and 2, the heart contractile force adjusting device 100 of the present utility model includes a contraction regulator including a power source 40, an MCU processor 20 and a pulse signal generator 30, and a spiral electrode 10 implanted in the heart, the spiral electrode 10 including a right atrial electrode and two right ventricular electrodes, the right atrial electrode being for sensing an electrophysiological signal of the heart.
As shown in fig. 1, two right ventricular electrodes are implanted on the upper and lower sides of the right ventricular septum, respectively, and are clustered at least 2cm. The first ventricular electrode 111 continuously works, as shown in fig. 3, after the first ventricular electrode 111 monitors local electric activity (after QRS wave starts for 30 ms), the MCU processor 20 controls the pulse signal generator 30 to output an electric stimulation signal from the second ventricular electrode 112, and the electric stimulation is performed on the heart in the absolute refractory period of the heart, so that the heart rate of the patient is not changed, and the expression of related proteins is regulated by regulating calcium ion inflow and phosphorylation of myocardial cells, so that the physiological state of the heart muscle is changed, the systole capability of the heart is enhanced, and the heart function of the heart failure patient is improved.
If the first ventricular electrode 111 monitors ventricular tachycardia, the MCU processor 20 controls the pulse signal generator 30 to output a faster frequency stimulus through the second ventricular electrode 112 to suppress the ventricular tachycardia, if the ventricular tachycardia continues to occur, the contraction regulator starts a defibrillation procedure, the MCU processor 20 controls the pulse signal generator 30 to deliver a larger current to defibrillate the heart and then restore the sinus rhythm, and if the first ventricular electrode 111 monitors ventricular fibrillation signals, the MCU processor 20 also controls the pulse signal generator 30 to discharge to perform electric defibrillation. When heart failure patients have arrhythmia, even ventricular fibrillation and other complications, the heart failure patients can be timely defibrillated, death caused by the ventricular fibrillation and other complications of the heart failure patients is avoided, and survival rate of the heart failure patients is improved.
The detailed technical scheme is as follows:
the first ventricular electrode 111 continuously monitors the right ventricular electrocardiograph signal without interruption and transmits the monitored signal back to the pulse signal generator 30, the pulse signal generator 30 feeds back the received waveform to the MCU processor 20, and the MCU processor 20 determines whether and when to initiate contractile force adjustment.
When the first ventricular electrode 111 continuously measures that all five signals are normal sinus excitation and the QRS intervals of all five normal sinus excitation are greater than 60 ms, the MCU processor 20 determines that the heart contractility adjustment can be started, and after the QRS wave of the sixth normal sinus excitation starts for 30 ms, the MCU processor 20 controls the pulse signal generator 30 to send an electrical stimulation pulse signal to the second ventricular electrode 112 so as to enhance the myocardial contractility.
As shown in fig. 3, the pulse signal has a pulse period of 20 ms and an amplitude of 8V, one electrical stimulation comprises two periods of the pulse signal, and one absolute refractory period of normal sinus excitation continuously releases the pulse signal for two periods until the absolute refractory period of the next normal sinus excitation, and the second ventricular electrode 112 releases the electrical stimulation pulse signal again, thereby circulating, regulating and enhancing the systole capability and improving the cardiac function of the heart failure patient.
If continuous sinus activation is interrupted, if an arrhythmia signal, an abnormal pacing activation signal or a QRS wave interval is detected to be less than 60 milliseconds, the electric stimulation pulse signal is immediately stopped, and the regulation of the systole capability is stopped until the precondition for starting the systole capability regulation is met again.
The MCU processor 20 is integrated with a timing device that can be set at random for an interval, for example, every three hours, for an hour, or every four hours, for a treatment interval to allow for a certain rest recovery period for cardiac regulation.
As shown in fig. 1, the data transmission configuration module 50 is electrically connected to the MCU processor 20, the remote configuration system 600 sets the MCU processor 20 through the data transmission configuration module 50, for example, a timing device integrated by the MCU processor 20, the remote configuration system 600 can set the timing device through the data transmission configuration module 50, the working time of the heart contractility adjusting device 100 can be periodically performed throughout the day, and the high-amplitude non-excitatory biphasic electric signal is provided for the myocardial refractory period for 7-12 hours, for example, the operation is started every three hours or every four hours, and a treatment interval can be set according to the age and physical condition of the patient, so that the heart adjustment can have a certain rest recovery period.
The remote configuration system 600 may set the defibrillation threshold of the MCU processor 20, i.e., convert ventricular rate or fibrillation to a minimum energy for sinus rhythm, through the data transmission configuration module 50, acquire the defibrillation threshold through a defibrillation threshold test, and set according to the patient's condition. The patients are anesthetized on the basis of veins before the test, and then ventricular fibrillation is induced, and the current clinical methods for inducing ventricular fibrillation are as follows:
1) T-wave shock, 2) 50HZ DC induction, 3) short burst rapid ventricular stimulation, 4) procedural electrical stimulation. The patient defibrillates after ventricular fibrillation occurs and a defibrillation threshold is recorded. After obtaining the defibrillation threshold, the operator sets the defibrillation threshold for the MCU processor 20 through the remote configuration system 600, so as to prevent the output defibrillation signal from being too large during defibrillation and from damaging the heart.
The power supply 40 adopts a rechargeable lithium battery to support wireless charging, a patient can perform wireless charging by only placing the charging chassis above the implantation position, in-vitro charging can be completed by only taking 1-1.5 hours every week, repeated replacement of the lithium battery in a hospital is not needed, and life-long use is supported.
The housing of the contractile force adjusting device 100 is made of titanium, and the connector is made of epoxy polymer resin, and the connector is provided with 3-4 insertion holes which are respectively connected with leads of an atrial electrode and a ventricular electrode, and the other ends of the atrial electrode and the ventricular electrode are respectively connected with myocardial tissues of a right atrium and a right ventricle.
The surgical procedure of the contractile force adjusting device 100 of the present utility model is as follows:
s1, preparing related consumables before operation, including: tearing the sheath, ventricular septum spiral electrode 10, pacing system analyzer, crocodile clip-on bridge wire, sterile gauze, sterile sheath, pacemaker surgical instrument, and external programmer.
S2, the spiral electrode 10 is implanted into a venous access through tearing a sheath, wherein the left and right side venous access is optional and comprises a head vein, a subclavian vein, an axillary vein and a neck vein, the spiral electrode 10 is connected and implanted into a ventricular septum, and the interval between the spiral electrodes 10 on two right ventricular septum is ensured to be more than 2cm.
S3, testing and recording the pacing threshold (0.4-2V) and pacing impedance (400-800 ohms) of the two ventricular electrodes 10 respectively to determine that the implantation condition of the ventricular electrodes 10 is good.
S4, connecting the defibrillation contraction regulator with the lead of the ventricular electrode 10 and implanting under the collarbone.
S5, setting various parameters of the defibrillation contraction regulator through a program control instrument.
And S6, the defibrillation contraction regulator starts to monitor sinus rhythm, and after capturing the signals, sends pulse electric signals in the absolute refractory period of the heart to strengthen the systole.
In summary, according to the present utility model, two spiral electrodes 10 are respectively implanted on the upper and lower sides of the right ventricle, and are mutually gathered by at least 2cm, after the upper ventricular spiral electrode 10 monitors local electrical activity, after the QRS wave starts for 30 ms, the lower spiral electrode 10 of the right ventricle transmits an electrical stimulation signal, the heart contractility is adjusted by the electrical stimulation, if the upper spiral electrode 10 monitors ventricular fibrillation signals, the ventricular fibrillation signals are fed back to the MCU processor 20, and the MCU processor 20 controls the pulse signal generator 30 to output defibrillation signals from the lower spiral electrode 10, so as to start a defibrillation procedure.
The MCU processor 20 is integrated with a timing device that can freely set the interval time, and periodically initiate the adjustment of the systole force, for example, every three hours, so as to provide a treatment interval to the patient, and allow the heart to have a certain rest recovery period, thus preventing complications.
While the utility model has been described in connection with specific embodiments thereof, it is to be understood that these drawings are included in the spirit and scope of the utility model, it is not to be limited thereto.
Claims (6)
1. A deconstructable heart contractile force adjustment device, comprising:
the spiral electrode comprises a ventricular electrode and an atrial electrode which are implanted in the heart, wherein the atrial electrode is used for sensing cardiac electrophysiology signals, the ventricular electrode is used for monitoring ventricular electrocardiosignals and sending electrical stimulation pulse signals to the heart;
the MCU processor is in communication connection with the spiral electrode and is used for generating a control signal based on the ventricular electrocardiosignal;
the pulse signal generator is in communication connection with the MCU processor and the spiral electrode, and is used for generating an electric stimulation pulse signal according to a control signal of the MCU processor and sending the electric stimulation pulse signal to the heart through the spiral electrode;
and the power supply is used for providing electric energy for the spiral electrode, the MCU processor and the pulse signal generator.
2. The defibrillation heart contractility adjusting device of claim 1, wherein the ventricular electrode comprises: the device comprises a first ventricular electrode and a second ventricular electrode, wherein the first ventricular electrode and the second ventricular electrode are implanted in a right ventricle space and are distributed at preset distance, one of the first ventricular electrode and the second ventricular electrode is used for monitoring ventricular electrocardiosignals, and the other of the first ventricular electrode and the second ventricular electrode is used for sending electrical stimulation pulse signals.
3. The device according to claim 2, wherein the first ventricular electrode and the second ventricular electrode are arranged at intervals of a predetermined distance in the up-down direction at the right ventricular interval, the predetermined distance being not less than 2cm.
4. The device of claim 1, wherein the MCU processor has a timing device, the start-up and run-time being controlled by the set-up time of the timing device.
5. The device of claim 4, wherein the MCU processor is communicatively coupled to a remote configuration system via a data transmission configuration module, the remote configuration system setting the timing device via the data transmission configuration module.
6. The device of any one of claims 1-5, wherein the power source is a lithium battery that supports wireless charging.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202223004572.6U CN220046845U (en) | 2022-11-11 | 2022-11-11 | Heart contractile force regulator capable of removing flutter |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202223004572.6U CN220046845U (en) | 2022-11-11 | 2022-11-11 | Heart contractile force regulator capable of removing flutter |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN220046845U true CN220046845U (en) | 2023-11-21 |
Family
ID=88759771
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202223004572.6U Active CN220046845U (en) | 2022-11-11 | 2022-11-11 | Heart contractile force regulator capable of removing flutter |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN220046845U (en) |
-
2022
- 2022-11-11 CN CN202223004572.6U patent/CN220046845U/en active Active
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| JP6781044B2 (en) | System to detect cardiac arrhythmia | |
| US8983598B2 (en) | System for neurally-mediated anti-arrhythmic therapy | |
| US5782883A (en) | Suboptimal output device to manage cardiac tachyarrhythmias | |
| JP5039151B2 (en) | System for treating supraventricular arrhythmia | |
| US5735876A (en) | Electrical cardiac output forcing method and apparatus for an atrial defibrillator | |
| US7957799B2 (en) | Non-invasive cardiac potentiation therapy | |
| EP2344243B1 (en) | Extravascular arrhythmia induction | |
| US9750941B2 (en) | Criteria for determination of local tissue latency near pacing lead electrodes | |
| JP2004513752A (en) | Apparatus for detecting and treating ventricular arrhythmias | |
| JP2012071206A (en) | Control of electrical stimulation using heart rate variability | |
| DK2603285T3 (en) | Cardioverter for removal of anterior chamber flicker | |
| US20040138713A1 (en) | External defibrillation and transcutaneous pacing device and methods for operating the device | |
| US20050197676A1 (en) | Electrical cardiac output forcer | |
| US20230293890A1 (en) | Medical device and method for generating modulated high frequency electrical stimulation pulses | |
| US6167306A (en) | Method and apparatus for electrically forcing cardiac output in an arrhythmia patient | |
| CN220046845U (en) | Heart contractile force regulator capable of removing flutter | |
| WO2023011641A1 (en) | Pulse stimulation device and method, and medical apparatus | |
| CN110755748B (en) | Artificial atrial flutter heart resuscitation device and system | |
| CN115721859A (en) | Defibrillation heart contractility regulating device and operation method thereof | |
| US20070213774A1 (en) | Defibrillation threshold testing system with automated control of external defibrillator | |
| Uzelac et al. | Personalized low-energy defibrillation through feedback based resynchronization therapy | |
| WO2014071153A1 (en) | Selective autonomic stimulation of the av node fat pad to control rapid post-operative atrial arrhythmias | |
| Batra et al. | Temporary pacing in children | |
| WO2017118933A1 (en) | Heart defibrillation pacing method and system | |
| US20230241391A1 (en) | Integrated sleep apnea and at least one of cardiac monitoring and cardiac therapy |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| GR01 | Patent grant | ||
| GR01 | Patent grant |