Implantable wireless electrocardiogram detection device

Abstract

The invention provides an implantable wireless electrocardio detection device, and relates to the field of in-vivo implantable devices, the implantable wireless electrocardio detection device comprises a shell and a plurality of electrodes, the plurality of electrodes are arranged on the shell, the monitoring ends of the plurality of electrodes are exposed on the surface of the shell, and the plurality of electrodes are used for collecting subcutaneous electrocardio signals; the circuit board is arranged in the shell, a processor and a memory are integrated on the circuit board, and the electrodes are electrically connected with the memory; the induction coil is arranged in the shell and electrically connected with the circuit board, and the induction coil is configured to receive a wireless pressure signal sent by a blood pressure sensor implanted in the heart; the processor is configured to store wireless pressure signals received by the induction coil and electrocardiosignals collected by the electrodes into the storage. According to the technical scheme, a high-synchronism original data basis is provided for follow-up analysis of the relevance between heart electrical activity and hemodynamics, such as evaluation of the influence of arrhythmia on blood pressure, and the capacity of comprehensive monitoring and diagnosis of cardiovascular diseases is remarkably enhanced.

Description

Technical Field

[0001] This invention generally relates to the field of implantable monitoring devices, and more specifically to an implantable wireless electrocardiogram (ECG) monitoring device. Background Technology

[0002] Implantable medical devices are widely used in the long-term monitoring and management of cardiovascular diseases because they can provide continuous and stable physiological signals. Currently, a common type of subcutaneous implantable device uses electrodes mounted on its shell to directly contact surrounding tissues to collect electrocardiogram (ECG) signals. These devices are typically small, can be implanted subcutaneously in the chest wall via minimally invasive surgery, have good biocompatibility and a long service life, and are suitable for long-term observation of symptoms such as arrhythmias and syncope. However, the information they acquire is limited to the electrical activity of the heart and cannot reflect changes in hemodynamic status, thus presenting a significant limitation in assessing overall cardiac function.

[0003] On the other hand, to obtain more comprehensive cardiovascular parameters, existing technologies have implanted miniature sensing units directly into the heart or large blood vessels to monitor key physiological indicators such as blood pressure. These implantable pressure sensors can provide continuous hemodynamic data, demonstrating clinical value in certain high-risk populations. However, because their operation is independent and they typically rely on external devices for data reading, the acquired signals are difficult to correlate effectively with other physiological parameters. Especially when patients require both ECG and blood pressure information simultaneously, current technology lacks an integrated solution capable of coordinating the acquisition of multi-source signals within the body, making it difficult for physicians to make comprehensive judgments based on multi-dimensional data under a unified time reference.

[0004] Despite advancements in various implantable monitoring devices, no subcutaneous implantable device currently possesses the ability to effectively receive and integrate physiological signals from other implanted units. Existing systems are generally single-function oriented, with monitoring modules operating in isolation. This not only increases the burden on patients but also limits the feasibility of multi-parameter joint analysis. Therefore, it is necessary to develop a novel implantable electrocardiogram (ECG) monitoring device that, while maintaining its basic ECG monitoring functions, possesses the fundamental ability to interact with other in vivo sensing units, thus providing a feasible technological path for future multimodal physiological monitoring. Summary of the Invention

[0005] In view of the problems existing in the prior art, the present invention provides an implantable wireless electrocardiogram (ECG) monitoring device, comprising: a housing; a plurality of electrodes disposed on the housing, the monitoring ends of the electrodes being exposed on the surface of the housing for acquiring subcutaneous ECG signals; a circuit board disposed within the housing, the circuit board integrating a processor and a memory, the plurality of electrodes being electrically connected to the memory; and an induction coil disposed within the housing and electrically connected to the circuit board, the induction coil being configured to receive a wireless pressure signal emitted by a blood pressure sensor implanted in the heart; wherein the processor is configured to store the wireless pressure signal received by the induction coil and the ECG signals acquired by the electrodes in the memory.

[0006] By incorporating the aforementioned technical features, this implantable wireless ECG monitoring device integrates multiple electrodes exposed on the shell surface, a built-in circuit board, and an induction coil, achieving simultaneous acquisition and storage of subcutaneous ECG signals and external wireless pressure signals. Multiple electrodes directly contact surrounding tissue, enabling stable acquisition of high-quality subcutaneous ECG data. The processor and memory integrated on the circuit board constitute a local data processing and caching unit, ensuring real-time signal processing and reliable temporary storage. The induction coil serves as a dedicated receiving channel, capturing wireless pressure signals emitted by the implantable blood pressure sensor. The processor times-aligns the ECG signals from the electrodes with the pressure signals from the induction coil and stores them together in the memory, thereby achieving multimodal fusion recording of two key physiological parameters: ECG and blood pressure. This design not only avoids additional leads or external connections, improving implantation safety, but also provides a highly synchronized raw data foundation for subsequent analysis of the correlation between cardiac electrical activity and hemodynamics, such as assessing the impact of arrhythmias on blood pressure, significantly enhancing the ability for comprehensive monitoring and diagnosis of cardiovascular diseases.

[0007] In some embodiments, a fixed frame, which is annular, is provided within the housing, and the circuit board is fixed within the fixed frame. This structural design effectively improves the mechanical stability of the internal components of the device. The annular fixed frame provides circumferential constraint on the circuit board, preventing displacement or warping due to vibration, impact, or tissue deformation during implantation or long-term service within the body. Simultaneously, the fixed frame, acting as a supporting skeleton within the housing, helps maintain the overall rigidity of the housing structure, preventing external pressure from deforming the housing and compressing internal electronic components. Furthermore, this layout provides a clear mounting reference and positioning space for the circuit board, facilitating standardized assembly processes and optimizing the use of space within the housing.

[0008] In some embodiments, the induction coil surrounds the periphery of the fixed frame. This arrangement of the induction coil around the periphery of the fixed frame not only avoids electrical interference with the central circuit board but also maximizes the effective area and magnetic field coupling efficiency of the coil, thereby improving the sensitivity and stability of receiving wireless pressure signals from the implantable blood pressure sensor. Simultaneously, the fixed frame provides a stable support base for the induction coil, preventing deformation or displacement during encapsulation or internal stress, ensuring consistent electromagnetic performance. Furthermore, this surrounding arrangement contributes to a compact and orderly internal structure, facilitating miniaturization of the housing and reducing mutual interference between functional modules, thus improving the overall signal reception reliability, electromagnetic compatibility, and structural durability of the device in long-term implantation environments.

[0009] In some embodiments, a power module is disposed on the circuit board and electrically connected to the processor; a power supply battery is disposed inside the housing and electrically connected to the power module; wherein, the induction coil is configured to receive an alternating magnetic field from an external charging device, and the induced electrical energy is rectified and regulated by the power module to wirelessly charge the power supply battery. Thus, the induction coil not only receives wireless signals from other implantable devices such as blood pressure sensors, but also has an energy receiving function, capable of capturing the alternating magnetic field generated by the external charging device and transmitting the induced AC power to the power module; the power module rectifies, regulates, and controls the electrical energy to safely and efficiently charge the power supply battery, thereby achieving non-invasive wireless power replenishment. The overall power supply solution balances long-term operational reliability and clinical applicability, providing a sustainable energy guarantee for continuous monitoring of implantable ECG and multimodal physiological signals.

[0010] In some embodiments, an emergency battery is disposed within the housing, electrically connected to the power module. The induction coil is configured to receive a low-battery status signal emitted by a blood pressure sensor implanted in the heart. Upon receiving the low-battery status signal, the power module activates the emergency battery and drives the induction coil to generate an alternating magnetic field, wirelessly transmitting energy to the blood pressure sensor to support its emergency operation. Thus, when the induction coil receives a low-battery status signal from the blood pressure sensor in the heart, the power module can respond immediately, automatically activating the emergency battery and driving the induction coil to generate an alternating magnetic field, wirelessly transmitting energy to the blood pressure sensor in the reverse direction. This mechanism effectively solves the risk of sudden failure of critical physiological parameter monitoring devices such as blood pressure sensors due to depletion of power, ensuring that they can maintain basic operation and continuously provide vital sign data in critical situations. By constructing this bidirectional energy and information interaction architecture, this device not only achieves stable acquisition of its own electrocardiogram signals but also becomes an emergency power supply node in an in vivo micro-energy network, significantly improving the overall reliability, safety redundancy, and clinical applicability of multi-device collaborative monitoring systems.

[0011] In some embodiments, the plurality of electrodes are respectively disposed on multiple surfaces of the housing to form electrical contact with surrounding tissue. This arrangement effectively expands the contact coverage between the electrodes and biological tissue, enhancing the spatial diversity and stability of ECG signal acquisition, and contributing to the acquisition of more comprehensive and interference-resistant subcutaneous ECG waveforms. Simultaneously, the multi-faceted electrode design reduces the risk of a sudden drop in signal quality due to slight rotation or displacement of the device within the body, enhancing the robustness of long-term monitoring.

[0012] In some embodiments, the processor is further configured to timestamp the ECG signal and the wireless pressure signal to support subsequent synchronous analysis. This mechanism ensures precise temporal alignment of the two types of physiological signals, allowing for accurate reconstruction of their temporal relationship even if the signals originate from different implanted devices or are transmitted via different paths, in subsequent data playback, remote diagnosis, or clinical analysis. Through timestamp synchronization, physicians or analysis systems can reliably correlate cardiac electrical activity, such as QRS complexes and arrhythmic events, with corresponding hemodynamic changes, such as blood pressure fluctuations, thereby providing a deeper assessment of cardiovascular function and identifying potential risks, such as sudden drops in blood pressure caused by arrhythmias. This synchronization capability significantly enhances the data value and diagnostic accuracy of multimodal physiological monitoring, providing solid technical support for the comprehensive assessment of complex cardiovascular diseases.

[0013] In some embodiments, the periphery of the fixed frame is covered with an electrostatic film. Thus, the electrostatic film has the ability to conduct or dissipate static charge, shielding or dissipating static electricity buildup within the housing caused by circuit operation, wireless power transmission, or tissue friction, preventing electrostatic discharge from interfering with or damaging sensitive electronic components such as processors, memory, and induction coils. Simultaneously, the film can also serve as part of an electromagnetic shielding layer, suppressing external radio frequency noise interference with ECG signal acquisition or reducing the external radiation of internal high-frequency signals, thereby improving the signal-to-noise ratio of signal acquisition and the system's anti-interference capability.

[0014] In some embodiments, the shell is made of a biocompatible material and is elongated and capsule-shaped, suitable for implantation in the subcutaneous tissue of the chest wall. This capsule-like contour has a smooth, non-sharp surface, effectively reducing mechanical irritation and foreign body reactions to surrounding tissues after implantation, and lowering the risk of excessive fibrous capsule encapsulation or local inflammation. Its elongated shape facilitates implantation through minimally invasive incisions and allows for natural conformation along the subcutaneous fascia layer, avoiding skin pressure, abrasion, or patient discomfort caused by abrupt changes in size. Simultaneously, the biocompatible material ensures that the device coexists peacefully with human tissue during long-term implantation, without inducing toxicity, sensitization, or rejection reactions. The overall structure not only improves patient tolerance and comfort but also provides a stable tissue contact environment for the ECG electrodes, thereby ensuring the long-term reliability and clinical applicability of signal acquisition.

[0015] In some embodiments, the housing is provided with an operating hole for grasping or positioning with specialized tools during implantation. Thus, the operating hole can reliably engage with specialized implantation tools such as grasping forceps, push rods, or positioning guides, facilitating precise grasping, directional adjustment, and stable pushing of the device during surgery, effectively preventing slippage, rotation, or positional displacement during implantation. Simultaneously, this hole design eliminates the need for additional protrusions or complex external structures, maintaining the smooth continuity of the housing's outer surface and reducing frictional damage and foreign body sensation to surrounding tissues.

[0016] It should be understood that the description in the Summary of the Invention is not intended to limit the key or essential features of the embodiments of this disclosure, nor is it intended to restrict the scope of this disclosure. Other features of this disclosure will become readily apparent from the following description. Attached Figure Description

[0017] Figure 1 A schematic diagram of the overall structure of an implantable wireless electrocardiogram (ECG) detection device according to an embodiment of the present invention is shown. Figure 2 A schematic diagram of the internal structure of an implantable wireless electrocardiogram (ECG) monitoring device according to an embodiment of the present invention is shown. Figure 3 A circuit diagram of an implantable wireless electrocardiogram (ECG) detection device according to an embodiment of the present invention is shown. Figure 4 A schematic diagram of the structure of a wireless blood pressure monitoring device, the target of an implantable wireless electrocardiogram detection device according to an embodiment of the present invention, is shown.

[0018] Symbol Explanation 1. Housing; 11. Electrode; 12. Operating hole; 13. Processor; 14. Memory; 15. Power module; 2. Circuit board; 3. Induction coil; 4. Fixing frame; 5. Power supply battery; 6. Emergency battery; 7. Electrostatic film; 81. Support shaft; 82. Pressure-sensitive chip; 83. Fixing hook; 84. Inductor; 85. Bracket. Detailed Implementation

[0019] The preferred embodiments (or implementation methods) of the present invention will now be described in detail with reference to the accompanying drawings.

[0020] The following is for reference. Figures 1-4 This invention describes an implantable wireless electrocardiogram (ECG) detection device.

[0021] Figure 1 This diagram illustrates the overall structure of an implantable wireless electrocardiogram (ECG) monitoring device according to an embodiment of the present invention. Figure 2 A schematic diagram of the internal structure of an implantable wireless electrocardiogram (ECG) monitoring device according to an embodiment of the present invention is shown. (Reference) Figure 1 and Figure 2 As shown, an implantable wireless electrocardiogram (ECG) monitoring device includes a housing 1, multiple electrodes 11, a circuit board 2, and an induction coil 3. The multiple electrodes 11 are disposed on the housing 1, with the monitoring ends of the electrodes 11 exposed on the surface of the housing 1 for collecting subcutaneous ECG signals. The circuit board 2 is disposed inside the housing 1 and integrates a processor 13 and a memory 14. The multiple electrodes 11 are electrically connected to the memory 14. The induction coil 3 is disposed inside the housing 1 and electrically connected to the processor 13. The induction coil 3 is configured to receive wireless pressure signals emitted by a blood pressure sensor implanted in the heart. The processor 13 is configured to store the wireless pressure signals received by the induction coil 3 and the ECG signals collected by the electrodes 11 into the memory 14.

[0022] Multiple electrodes 11 are conductive contacts disposed on the outer surface of the housing 1, with their monitoring ends directly exposed on the surface of the housing 1, used to form electrical contact with the surrounding subcutaneous tissue to pick up weak electrical signals generated by myocardial electrical activity; the circuit board 2 is a printed circuit board integrated inside the housing 1, on which a processor 13 and a memory 14 are mounted, used to perform signal processing, control logic and data caching functions respectively; the induction coil 3 is an electromagnetic coupling element made of conductive wire, fixed inside the housing 1 and electrically connected to the circuit board 2, used to receive wireless pressure signals emitted from other implantable devices such as intracardiac blood pressure sensors, and can also serve as an energy receiving unit.

[0023] This implantable wireless ECG monitoring device integrates multiple exposed electrodes 11, an internal circuit board 2, and an induction coil 3 within a sealed housing 1, creating a multifunctional monitoring platform capable of both local ECG acquisition and external physiological signal reception. The electrodes 11 directly contact the subcutaneous tissue, enabling stable acquisition of high-quality ECG signals. The processor 13 and memory 14 on the circuit board 2 work together to process and temporarily store ECG data in real time. The induction coil 3 establishes an information pathway with other implanted devices, receiving wireless pressure signals from an intracardiac blood pressure sensor. The processor 13 stores two key physiological parameters—ECG and blood pressure signals—in the memory 14, providing a highly consistent data foundation for subsequent multimodal synchronous analysis. This design not only avoids additional leads or external connections, improving the safety and reliability of long-term implantation, but also achieves joint monitoring of cardiovascular electrical activity and hemodynamic status, significantly enhancing the comprehensive assessment capabilities for complex arrhythmias, changes in cardiac function, and other clinical events, providing an efficient and integrated technical solution for the precise management of chronic cardiovascular diseases.

[0024] In some embodiments, multiple electrodes 11 are respectively disposed on multiple surfaces of the housing 1 to form electrical contact with surrounding tissue. By arranging multiple electrodes 11 on multiple outer surfaces of the housing 1, the device can form multi-directional and multi-angle electrical contact with surrounding subcutaneous tissue after implantation. This spatial distribution strategy effectively improves the geometric diversity of ECG signal acquisition, making the device more adaptable to changes in local tissue characteristics or small displacements, and avoiding signal quality degradation due to poor contact in a single direction. At the same time, the multi-faceted electrode layout helps to construct multiple differential measurement channels, enhances common-mode noise suppression capability, and thus obtains clearer and more stable ECG waveforms in the complex in vivo electromagnetic environment. In addition, this design allows the device to maintain effective signal pickup performance even when there is a certain degree of freedom in the implantation posture, improving the fault tolerance of surgical operation and the reliability of long-term monitoring, and providing structural protection for continuous and high-quality cardiac rhythm monitoring.

[0025] In some embodiments, the shell 1 is made of a biocompatible material and is generally elongated and capsule-shaped, suitable for implantation in the subcutaneous tissue of the chest wall. The shell 1 refers to the sealed outer shell that constitutes the main body of the device, used to house the internal electronic components and form an outer surface that comes into contact with human tissue; the biocompatible material refers to a medical polymer or composite material that will not cause significant immune rejection, toxic reactions or chronic inflammation after long-term implantation in the body, such as medical silicone, polyether ether ketone (PEEK) or titanium alloy coated polymers; the elongated and capsule-shaped refers to the streamlined shape of the shell 1, which has smooth transitions at both ends and a narrow and elongated main body in the middle, similar to a capsule or elliptical cylinder, without sharp edges or protruding structures.

[0026] The device utilizes a slender, capsule-shaped shell made of biocompatible materials, balancing safety and anatomical compatibility for long-term implantation. Its streamlined contour matches the natural curvature of the subcutaneous tissue of the chest wall, facilitating precise placement via a minimally invasive incision and ensuring good post-operative integration with surrounding soft tissues. This reduces local pressure, friction, or skin bulging caused by the abrupt shape of the foreign body. The smooth, edgeless surface effectively reduces mechanical stimulation to adjacent tissues and inhibits excessive proliferation of the fibrous capsule, thereby maintaining a stable electrode-tissue interface and signal acquisition quality. Simultaneously, the biocompatible materials ensure that the device does not release harmful substances during long-term retention in the body, avoiding chronic inflammation or rejection reactions and improving patient tolerance. The overall design not only optimizes the implantation experience and post-operative comfort but also provides a sound physical and biological basis for the device's stable operation in dynamic physiological environments.

[0027] In some embodiments, a fixing frame 4 is provided inside the housing 1. The fixing frame 4 is annular, and the circuit board 2 is fixed inside the fixing frame 4. The fixing frame 4 is a support structure provided inside the housing 1. It is usually made of rigid or semi-rigid material and is annular in shape, that is, it has a closed annular profile to provide a stable mounting reference.

[0028] This device significantly improves the structural stability and long-term reliability of the internal electronic system. The annular fixing frame 4 provides circumferential constraint on the circuit board 2, effectively preventing displacement or warping during implantation, tissue movement, or external impact. Simultaneously, this frame, acting as the internal mechanical skeleton of the housing 1, helps maintain the overall structural rigidity, preventing deformation of the housing 1 due to external pressure that could compress or damage precision electronic components. The fixing frame 4 provides a precise positioning reference for the circuit board 2, facilitating consistency and automation in the assembly process, and reserving clear layout space for other components such as the induction coil 3 and the battery, thus optimizing the space utilization efficiency within the housing 1. Overall, this structural design not only enhances the device's mechanical durability in complex internal environments but also provides a reliable physical foundation for the continuous and stable operation of ECG signal acquisition and multimodal data processing.

[0029] In some embodiments, the induction coil 3 is arranged around the periphery of the fixed frame 4. This arrangement cleverly utilizes the edge area inside the housing 1, achieving a synergistic optimization of functional integration and space efficiency. This layout keeps the induction coil 3 away from the circuit board 2 and its sensitive electronic components located in the central area of ​​the frame, effectively reducing the impact of electromagnetic interference on ECG signal acquisition and processing. Simultaneously, it provides a larger effective area for the coil to enhance magnetic field coupling, thereby improving the sensitivity and stability of receiving wireless signals from other implanted devices such as blood pressure sensors. Furthermore, the fixed frame 4 provides structural support for the induction coil 3, preventing deformation or displacement during packaging or long-term service, ensuring consistent electromagnetic performance. The ring arrangement itself also facilitates matching with the shape of the housing 1, contributing to a compact and symmetrical overall structure. This spatial configuration not only enhances the electromagnetic compatibility and signal reliability of the device but also lays a robust hardware foundation for the synchronous acquisition of multimodal physiological information.

[0030] In some embodiments, the housing 1 is provided with an operating hole 12 for gripping or positioning with a special tool during implantation. The operating hole 12 refers to one or more through holes or grooves formed on the surface of the housing 1, the shape and size of which match the end of a special implantation tool such as a gripping forceps, a positioning push rod or a clamping instrument, to provide a reliable mechanical interface during surgery.

[0031] This structural design significantly improves the controllability and efficiency of intraoperative procedures without compromising the overall sealing and surface continuity of the shell 1, facilitating accurate placement of the device in the pre-set subcutaneous location. Simultaneously, because the operating port 12 is an embedded or smoothly transitioned structure, it avoids the formation of protruding edges or stress concentration points postoperatively, reducing irritation to surrounding tissues and long-term foreign body sensation. This detailed optimization not only reduces surgical difficulty and operational risks but also provides practical support for the standardized implantation and clinical promotion of the device.

[0032] In some embodiments, the periphery of the fixing frame 4 is covered with an electrostatic film 7. The electrostatic film 7 is a flexible thin film material with conductive or electrostatic dissipation properties, which is covered on the periphery of the fixing frame 4 to suppress or conduct away static charge accumulation. Its composition may include a polymer substrate doped with conductive particles or a metallized polymer layer, and it has good biocompatibility and long-term stability.

[0033] The electrostatic film 7 can promptly dissipate static charges generated by wireless power transmission, circuit switching operations, or tissue friction, preventing local charge accumulation that could lead to electrostatic discharge. This avoids transient interference or permanent damage to the sensitive processor 13, memory 14, and induction coil 3. Simultaneously, the film forms a continuous electrostatic shielding layer around the fixed frame 4, helping to weaken the coupling of external radio frequency noise to the core circuit area and improve the signal-to-noise ratio of ECG signal acquisition. Furthermore, it suppresses the outward radiation of internal high-frequency signals, reducing potential interference to nearby implanted devices. Since the film directly covers the existing structural surface, it does not require additional space within the housing 1, maintaining the device's miniaturization advantage while enhancing overall anti-interference capabilities and long-term operational reliability, providing a cleaner and more stable internal electromagnetic environment for high-precision ECG monitoring.

[0034] Figure 3 A circuit diagram of an implantable wireless electrocardiogram (ECG) monitoring device according to an embodiment of the present invention is shown below. (Refer to...) Figure 3 As shown, in some embodiments, a power module 15 is provided on the circuit board 2, and the power module 15 is electrically connected to the processor 13; a power supply battery 5 is provided inside the housing 1, and the power supply battery 5 is electrically connected to the power module 15; wherein, the induction coil 3 is configured to receive the alternating magnetic field from the external charging device, and after the induced electrical energy is rectified and regulated by the power module 15, it wirelessly charges the power supply battery 5.

[0035] The power module 15 is a power management unit set on the circuit board 2, which has functions such as rectification, voltage regulation and charging control, and is electrically connected to the processor 13 to achieve power supply coordination; the power supply battery 5 refers to a rechargeable micro energy storage unit, which is sealed in the housing 1 to provide operating power for the entire device.

[0036] When the external charging device emits an alternating magnetic field, the induction coil 3 converts it into electrical energy. After rectification and voltage regulation by the power module 15, the energy is safely replenished to the power supply battery 5, thus eliminating the dependence on disposable batteries. This design not only significantly extends the service life of the device and avoids the risk of needing a second surgery to remove or replace the battery due to depletion, but also ensures that core functional modules such as the processor 13, memory 14, and signal receiving unit can obtain a continuous and stable power supply. More importantly, the wireless charging mechanism and signal reception share the induction coil 3, achieving dual-channel multiplexing of energy and information without adding extra structures, improving overall integration and reliability, and providing sustainable energy security for long-term, continuous ECG and multimodal physiological monitoring.

[0037] In some embodiments, an emergency battery 6 is provided within the housing 1, and the emergency battery 6 is electrically connected to the power module 15. The induction coil 3 is configured to receive a low-battery status signal emitted by the blood pressure sensor implanted in the heart. Upon receiving the low-battery status signal, the power module 15 activates the emergency battery 6 and drives the induction coil 3 to generate an alternating magnetic field, wirelessly transmitting energy to the blood pressure sensor to support its emergency operation. The emergency battery 6 refers to an additional independent backup power supply within the housing 1, with a small capacity but rapid activation, specifically designed for emergency power supply scenarios. The induction coil 3 is an electromagnetic coupling element that combines signal reception and energy transmission functions. It can receive wireless signals from other implanted devices and can also actively radiate an alternating magnetic field when driven. The low-battery status signal is a specific wireless command actively emitted by the blood pressure sensor implanted in the heart when its own power is insufficient, used to request external support.

[0038] This device significantly enhances the overall fault tolerance and operational continuity of the in vivo multi-device collaborative system by introducing an emergency battery 6 and a bidirectional energy interaction mechanism. When the induction coil 3 receives a low-battery status signal from the intracardiac blood pressure sensor, the power module 15 immediately recognizes the emergency request and automatically switches to support mode, activating the emergency battery 6. Simultaneously, it reverses the induction coil 3 to generate an alternating magnetic field, transmitting directional wireless energy to the blood pressure sensor. This design makes the device not only a terminal for acquiring ECG signals but also an active power supply node in the in vivo micro-energy network, providing timely power support when critical physiological monitoring equipment faces the risk of power outage, ensuring its maintenance of basic sensing and communication functions. The resulting mutual power supply architecture effectively avoids the loss of important hemodynamic data due to the depletion of power in a single device, enhancing the reliability, safety redundancy, and clinical applicability of the entire implantable monitoring system.

[0039] In some embodiments, the processor 13 is further configured to timestamp the electrocardiogram signal and the wireless stress signal to support subsequent synchronous analysis. Timestamping refers to the processor 13 attaching precise timing information to the signals when receiving or generating them, to record the relative or absolute time of each signal event.

[0040] By configuring the processor 13 to add timestamps to both ECG and wireless pressure signals, this device achieves precise temporal alignment of multi-source physiological data. Since the two types of signals originate from independent sensors at different locations, and their transmission paths and processing delays may differ, the timestamp mechanism ensures accurate reconstruction of their original temporal relationships even in asynchronous sampling or intermittent communication, allowing for accurate playback, remote diagnosis, or clinical analysis. This high-precision temporal correlation capability enables physicians or analysis systems to reliably investigate the causal or response relationships between cardiac electrical activity such as P waves, QRS complexes, arrhythmia episodes, and transient blood pressure changes, thereby providing a more comprehensive assessment of the cardiovascular system's functional status. This design not only enhances the fusion value of multimodal data but also provides a solid data foundation for the mechanistic analysis and early warning of complex cardiac arrhythmias, significantly improving the clinical diagnostic efficacy of implantable monitoring systems.

[0041] Figure 4 A schematic diagram of the structure of a wireless blood pressure monitoring device, the target of an implantable wireless electrocardiogram (ECG) detection device according to an embodiment of the present invention, is shown. (Reference) Figure 4 As shown, an implantable intracardiac blood pressure monitoring sensor includes a support shaft 81, a pressure-sensitive chip 82, a fixing hook 83, an inductor coil 84, and a bracket 85. The pressure-sensitive chip 82 is fixed to one end of the support shaft 81, and the fixing hook 83 is located at the other end of the support shaft 81 for connection with a delivery device. The inductor coil 84 is sleeved on the support shaft 81 and coupled to the pressure-sensitive chip 82. The bracket 85 is composed of multiple high-elasticity shape memory alloy strips arranged around the support shaft 81. The two ends of the bracket 85 are respectively connected to the two ends of the support shaft 81, and the middle part is supported on the inner wall of the left atrium of the heart.

[0042] The support shaft 81 is a slender rod-like structure extending longitudinally along the sensor, serving as a mounting carrier for various functional components and maintaining the overall geometric configuration. The pressure-sensitive chip 82 specifically refers to a capacitive pressure sensor manufactured using microelectromechanical systems (MEMS) technology. Its core is a micron-level variable capacitor structure. When subjected to intracardiac blood pressure, the sensitive diaphragm undergoes a slight deformation, causing a change in capacitance, thereby achieving high-precision and high-sensitivity pressure signal detection. The fixing hook 83 is located at one end of the support shaft 81, used to form a detachable mechanical connection with external delivery devices such as catheter pushing systems or traction mechanisms, facilitating intraoperative manipulation, positioning, and retrieval when necessary. The inductor coil 84 is a helical flexible conductor made of insulated conductive wire wound around the support shaft. The outer periphery of shaft 81 is electrically coupled to pressure-sensitive chip 82 to transmit weak electrical signals. It also has excellent bending compliance and fatigue resistance due to its coil structure, which can adapt to the dynamic environment of continuous heartbeat. It can transmit wireless pressure signals to the wireless ECG detection device and receive energy signals from the induction coil 3 in the wireless ECG detection device to ensure the normal operation of the device itself. The support 85 is composed of multiple high-elasticity memory alloys such as nickel-titanium alloy, which are arranged in a three-dimensional mesh or frame structure around the support shaft 81. Its two ends are respectively connected to the two ends of the support shaft 81. It can automatically restore the preset shape under body temperature. The middle part forms an arched support area to fit the inner wall of the left atrium of the heart, such as the interatrial septum, to provide stable anchoring without penetrating the tissue.

[0043] In the description of this specification, the terms "connection," "installation," and "fixing," etc., should be interpreted broadly. For example, "connection" can be a fixed connection, a detachable connection, or an integral connection; it can be a direct connection or an indirect connection through an intermediate medium. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

[0044] The above are merely preferred embodiments of this application and are not intended to limit this application. Various modifications and variations can be made to this application by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this application should be included within the protection scope of this application.

Claims

1. An implantable wireless electrocardiogram (ECG) monitoring device, characterized in that, include: Shell (1), Multiple electrodes (11) are disposed on the housing (1), with the monitoring ends of the multiple electrodes (11) exposed on the surface of the housing (1) for collecting subcutaneous electrocardiogram signals; Circuit board (2), the circuit board (2) is disposed inside the housing (1), the circuit board (2) integrates a processor (13) and a memory (14), and the plurality of electrodes (11) are electrically connected to the memory (14); An induction coil (3) is disposed inside the housing (1) and electrically connected to the circuit board (2). The induction coil (3) is configured to receive a wireless pressure signal emitted by a blood pressure sensor implanted in the heart. The processor (13) is configured to store the wireless pressure signal received by the induction coil (3) and the electrocardiogram signal collected by the electrode (11) into the memory (14).

2. The implantable wireless ECG detection device according to claim 1, characterized in that, A fixing frame (4) is provided inside the housing (1). The fixing frame (4) is ring-shaped, and the circuit board (2) is fixed inside the fixing frame (4).

3. The implantable wireless ECG detection device according to claim 2, characterized in that, The induction coil (3) is surrounded by the fixed frame (4).

4. The implantable wireless ECG monitoring device according to claim 1, characterized in that, A power module (15) is provided on the circuit board (2), and the power module (15) is electrically connected to the processor (13); A power supply battery (5) is provided inside the housing (1), and the power supply battery (5) is electrically connected to the power module (15); The induction coil (3) is configured to receive the alternating magnetic field from the external charging device and to wirelessly charge the power supply battery (5) after the induced electrical energy is rectified and regulated by the power module (15).

5. An implantable wireless electrocardiogram (ECG) detection device according to claim 4, characterized in that, An emergency battery (6) is provided inside the housing (1), and the emergency battery (6) is electrically connected to the power module (15); The induction coil (3) is configured to receive a low-charge status signal from a blood pressure sensor implanted in the heart; Upon receiving the low battery status signal, the power module (15) activates the emergency battery (6) and drives the induction coil (3) to generate an alternating magnetic field, wirelessly transmitting energy to the blood pressure sensor to support its emergency operation.

6. An implantable wireless electrocardiogram (ECG) detection device according to claim 1, characterized in that, The plurality of electrodes (11) are respectively disposed on a plurality of surfaces of the housing (1) to form electrical contact with the surrounding tissue.

7. An implantable wireless electrocardiogram (ECG) detection device according to claim 1, characterized in that, The processor (13) is also configured to timestamp the ECG signal and the wireless stress signal to support subsequent synchronous analysis.

8. An implantable wireless electrocardiogram (ECG) detection device according to claim 3, characterized in that, The periphery of the fixed frame (4) is covered with an electrostatic film (7).

9. An implantable wireless electrocardiogram (ECG) detection device according to claim 1, characterized in that, The shell (1) is made of biocompatible material and is slender and capsule-shaped, suitable for implantation in the subcutaneous tissue of the chest wall.

10. An implantable wireless electrocardiogram (ECG) detection device according to claim 1, characterized in that, The housing (1) is provided with an operation hole (12) for use in conjunction with special tools for grasping or positioning during implantation.

Images