Implantable cardioverter defibrillator power supply unit and implantable cardioverter defibrillator

Abstract

The present invention provides an implantable cardioverter defibrillator power supply unit and an implantable cardioverter defibrillator, wherein the power supply unit of the implantable cardioverter defibrillator comprises: a switching power supply, a linear power supply and a controller; the output of the power supply unit comprises VDD and VPP; the controller comprises a custom mode and a plurality of special scene modes; when the controller is in the custom mode, the switching power supply and the linear power supply work based on a set program; the controller is configured to set the custom mode and the special scene mode according to the timing corresponding to the application scene according to the current application scene of the implantable cardioverter defibrillator, so as to control the working state of the switching power supply and the linear power supply, and realize the independent or joint output of VDD and VPP corresponding to the application scene. Such configuration ensures the reliable realization of the priority of each function, reduces the power consumption, and meets the reliability and efficiency requirements of power management.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to an implantable cardioverter defibrillator power supply unit and an implantable cardioverter defibrillator. Background Art

[0002] Implantable cardioverter defibrillators (ICDs) generally use disposable batteries and often need to operate for nearly 10 years after being implanted in the human body, so the power consumption management requirements are very high. ICDs usually need to provide functions such as program control, algorithm identification, high-voltage defibrillation, magnet mode, and magnetic resonance imaging (MRI) compatibility. Different hardware modules of an ICD have different power consumption requirements. Usually, the power supply needs to be managed according to the logic of the system functions to avoid increased power consumption due to concurrent functions, which may cause system instability.

[0003] After defibrillation treatment, radio frequency programming and remote follow-up of implantable cardioverter defibrillators are usually achieved through wireless transmission (such as low-power Bluetooth). Wireless transmission has high instantaneous power consumption when sending and receiving data. In addition, the system functions should be kept running normally even during radio frequency programming and remote follow-up sessions. The increase in instantaneous power consumption caused by wireless transmission may cause the overall instantaneous power consumption of the system to be higher than the output capacity of the battery if effective power management is not performed, affecting the stability of the system. It may also cause excessive discharge of the battery and thus reduce the battery life.

[0004] In addition, implantable cardioverter defibrillators also have to face a variety of complex application scenarios such as high-voltage defibrillation, telemetry, and magnetic field environments (such as magnetic resonance scanning). How to achieve reliable and efficient power supply for each functional module while meeting the priority of each function is an urgent problem to be solved. Summary of the invention

[0005] The object of the present invention is to provide an implantable cardioverter defibrillator power supply unit and an implantable cardioverter defibrillator, so as to solve the problem that it is difficult to achieve both high reliability and high efficiency in the power management of the existing implantable cardioverter defibrillator.

[0006] In order to solve the above technical problems, the present invention provides a power supply unit for an implantable cardioverter defibrillator, which comprises: a switching power supply, a linear power supply and a controller; the output of the power supply unit comprises VDD and VPP; the controller comprises a custom mode and a plurality of special scene modes; when the controller is in the custom mode, the switching power supply and the linear power supply work based on a set program;

[0007] The controller is configured to set the custom mode and the special scenario mode according to the timing corresponding to the application scenario according to the current application scenario of the implantable cardioverter defibrillator, so as to control the working state of the switching power supply and the linear power supply, and realize the independent or joint output of VDD and VPP corresponding to the application scenario;

[0008] The custom mode includes:

[0009] Program 1: The linear power supply is used to output VPP, the switching power supply is used to output VDD, and the linear power supply and the switching power supply are configured to delay starting; the program 1 is used to start or shut down the switching period of the RF program control;

[0010] Program 2: Use the linear power supply to output VPP and VDD; Program 2 is used in the RF program control process;

[0011] Program 3: Using the switching power supply to output VPP and VDD; Program 3 is used for the buffer period before and after charging the defibrillation capacitor.

[0012] Optionally, the linear power supply includes a first module and a second module; the special scene mode includes any of the following modes:

[0013] Magnetic resonance compatible mode: turn off the switch power supply and use the first module to output VPP and VDD;

[0014] High voltage mode: using the switching power supply to output VPP, and using the first module to output VDD;

[0015] High voltage and remote sensing program control mode: using the switching power supply to output VPP, and using the second module to output the portion of VDD used to power the analog circuit;

[0016] RF mode: using the switching power supply to output VPP, and using the first module and the second module to mix and output VDD;

[0017] Telemetry mode: turn off the switch power supply and use the first module to output VPP and VDD;

[0018] The controller further includes a nominal mode, and when the controller is in the nominal mode, the switching power supply and the linear power supply are configured based on normal operating requirements of the implantable cardioverter-defibrillator;

[0019] The priorities of the magnetic resonance compatible mode, the high voltage mode, the high voltage and telemetry program control mode, the radio frequency mode, the telemetry mode and the nominal mode are arranged from high to low.

[0020] Optionally, the application scenario includes starting a radio frequency program control scenario;

[0021] The start-up RF program control scenario includes a telemetry activation phase, a switching phase, a delay phase, and a RF program control phase which are sequentially arranged; wherein the switching phase starts with the RF module being turned on, and the telemetry module is turned off no later than the end of the delay phase;

[0022] In the telemetry activation stage, the controller is configured in the telemetry mode;

[0023] In the switching phase, the controller is configured to the radio frequency mode;

[0024] During the delay phase, the controller is configured as the program 1;

[0025] During the radio frequency programming stage, the controller is configured as program two.

[0026] Optionally, the application scenario includes ending the radio frequency program control scenario;

[0027] The end of the radio frequency program control scenario includes a radio frequency program control phase, a delay phase, and a remote follow-up phase that are arranged in sequence;

[0028] In the radio frequency programming stage, the controller is configured as the second program;

[0029] During the delay phase, the controller is configured as the program 1;

[0030] During the remote follow-up phase, the controller is configured to be in the radio frequency mode;

[0031] After the remote follow-up period ends, the controller is configured to the nominal mode.

[0032] Optionally, the application scenario includes initiating a remote follow-up scenario;

[0033] Before starting the remote follow-up scenario, the controller is configured to the nominal mode;

[0034] In the remote follow-up initiation scenario, the controller is configured to be in the radio frequency mode.

[0035] Optionally, the application scenario includes a magnetic field detection scenario in remote follow-up;

[0036] The magnetic field detection scenario in the remote follow-up includes a radio frequency off stage, a waiting stage and a magnetic resonance stage which are arranged in sequence; wherein the radio frequency off stage ends when the end of the cardiac cycle in which the magnetic field signal is detected is taken as the end;

[0037] During the radio frequency off phase, the controller is configured to the radio frequency mode;

[0038] During the waiting phase, the controller is configured to the nominal mode;

[0039] During the magnetic resonance phase, the controller is configured to the magnetic resonance compatible mode.

[0040] Optionally, the application scenario includes switching to telemetry during radio frequency communication accompanied by a high voltage charging scenario;

[0041] The switching to telemetry during radio frequency communication accompanied by a high voltage charging scenario includes a radio frequency off phase, a delay phase, a telemetry phase, a high voltage charging phase, and a high voltage and telemetry programming phase arranged in sequence in terms of time sequence;

[0042] During the radio frequency off phase, the controller is configured to Program Two;

[0043] During the delay phase, the controller is configured to Program One;

[0044] During the telemetry phase, the controller is configured to the telemetry mode;

[0045] During the high voltage charging phase, the controller is sequentially configured to Program Three, the high voltage mode, and Program Three;

[0046] During the high voltage and telemetry programming phase, when the telemetry module is turned on, the controller is configured to the high voltage and telemetry programming mode, and when the telemetry module is turned off, the controller is configured to the nominal mode.

[0047] Optionally, the application scenario includes ending a high voltage event and detecting a magnetic field scenario;

[0048] The ending a high voltage event and detecting a magnetic field scenario includes a high voltage charging phase, a delay phase, and a magnetic resonance phase arranged in sequence in terms of time sequence; wherein the delay phase ends at the cardiac cycle when a magnetic field signal is detected;

[0049] During the high voltage charging phase, the controller is configured to the high voltage mode;

[0050] During the delay phase, the controller is configured to the nominal mode;

[0051] During the magnetic resonance phase, the controller is configured to the magnetic resonance compatible mode.

[0052] Optionally, VDD is used for the main chip and its peripheral circuits, the bus of the defibrillation chip, and the external RAM; VPP is used for the sensors, the telemetry module, and the radio frequency module.

[0053] In order to solve the above technical problems, the present invention further provides an implantable cardioverter defibrillator, which comprises the power supply unit of the implantable cardioverter defibrillator as described above.

[0054] In summary, in the power supply unit of the implantable cardioverter defibrillator and the implantable cardioverter defibrillator provided by the present invention, the power supply unit of the implantable cardioverter defibrillator includes: a switching power supply, a linear power supply and a controller; the output of the power supply unit includes VDD and VPP; the controller includes a custom mode and a plurality of special scene modes; when the controller is in the custom mode, the switching power supply and the linear power supply work based on a set program; the controller is configured to set the custom mode and the special scene mode according to the timing corresponding to the current application scenario of the implantable cardioverter defibrillator according to the application scenario, To control the working state of the switching power supply and the linear power supply, and realize the independent or joint output of VDD and VPP corresponding to the application scenario; wherein the custom mode includes: program one: adopting the linear power supply to output VPP, adopting the switching power supply to output VDD, and the linear power supply and the switching power supply are configured to delay start; the program one is used to start or shut down the switching period of radio frequency program control; program two: adopting the linear power supply to output VPP and VDD; the program two is used in the radio frequency program control process; program three: adopting the switching power supply to output VPP and VDD; the program three is used for the buffer period before and after charging the defibrillator capacitor.

[0055] With such configuration, through the setting of custom modes and the setting of multiple special scene modes, the multi-scenario requirements of the implantable cardioverter defibrillator can be met. According to different scenarios, the chip and firmware of the implantable cardioverter defibrillator can be used to achieve programmable power management, thereby generating different power timings, ensuring the reliable implementation of the priority of each function, reducing power consumption, and meeting the reliability and efficiency requirements of the implantable cardioverter defibrillator for power management. BRIEF DESCRIPTION OF THE DRAWINGS

[0056] Those skilled in the art will appreciate that the drawings are provided for a better understanding of the present invention, but do not constitute any limitation on the scope of the present invention.

[0057] Figure 1 1 is a schematic diagram of a module of a power supply unit of an implantable cardioverter defibrillator according to an embodiment of the present invention.

[0058] Figure 2 It is a timing diagram of starting a radio frequency program control scenario according to an embodiment of the present invention.

[0059] Figure 3 It is a timing diagram of a radio frequency program control and data transmission scenario in an embodiment of the present invention.

[0060] Figure 4 It is a timing diagram of ending the radio frequency program control scenario according to an embodiment of the present invention.

[0061] Figure 5 It is a timing diagram of starting a remote follow-up scenario according to an embodiment of the present invention.

[0062] Figure 6 It is a timing diagram of a magnetic field detection scenario in a remote follow-up according to an embodiment of the present invention.

[0063] Figure 7 It is a timing diagram of switching to telemetry accompanied by a high-voltage charging scenario in the radio frequency communication of an embodiment of the present invention.

[0064] Figure 8 It is a timing diagram of ending a high voltage event and detecting a magnetic field scene according to an embodiment of the present invention.

[0065] In the attached figure: 1-switching power supply; 2-linear power supply; 21-first module; 22-second module; 3-controller. DETAILED DESCRIPTION

[0066] In order to make the purpose, advantages and features of the present invention clearer, the present invention is further described in detail below in conjunction with the accompanying drawings and specific embodiments. It should be noted that the drawings are all in a very simplified form and are not drawn to scale, and are only used to conveniently and clearly assist in explaining the purpose of the embodiments of the present invention. In addition, the structure shown in the drawings is often a part of the actual structure. In particular, the emphasis of each drawing is different, and sometimes different scales are used.

[0067] As used in the present invention, the singular forms "one", "one", "one" and "the" include plural objects, the term "or" is usually used to include the meaning of "and / or", the term "several" is usually used to include the meaning of "at least one", and the term "at least two" is usually used to include the meaning of "two or more". In addition, the terms "first", "second" and "third" are only used for descriptive purposes and cannot be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, the features defined as "first", "second" and "third" can explicitly or implicitly include one or at least two of the features, and "one end" and "the other end" and "proximal end" and "distal end" generally refer to two corresponding parts, which not only include endpoints. For those of ordinary skill in the art, the specific meanings of the above terms in the present invention can be understood according to the specific circumstances. In addition, directional terms such as above, below, up, down, upward, downward, left, right, etc. are used relative to the exemplary embodiments as shown in the figures, with the upward or upper direction toward the top of the corresponding figure, and the downward or lower direction toward the bottom of the corresponding figure.

[0068] The object of the present invention is to provide a power supply unit of an implantable cardioverter defibrillator and an implantable cardioverter defibrillator, so as to solve the problem that it is difficult to achieve both high reliability and high efficiency in the power supply management of the existing implantable cardioverter defibrillator.

[0069] As described in the background art, an implantable cardioverter defibrillator generally has a built-in battery that can provide a relatively single voltage and a certain current. However, the power supply voltage and current required by the functional modules included in the implantable cardioverter defibrillator are not the same, so it is often necessary to convert the output of the battery through a power conversion module to obtain a suitable voltage and current for use by each functional module.

[0070] Linear regulated power supplies (referred to as linear power supplies) and switching power supplies (SMPS) are two common types of power conversion modules. Compared with linear power supplies, switching power supplies (SMPS) have higher conversion efficiency and are therefore more power-saving. However, the working scenarios of implantable cardioverter defibrillators are relatively complex. For example, they need to be programmed through telemetry (TELEMETRY, referred to as TEL), or they need to be able to perform magnetic resonance scanning. During telemetry programming and magnetic resonance scanning, relatively strong electromagnetic reactions will be generated, which has a relatively large impact on the switching power supply and may cause the switching power supply to fail. Therefore, when applying the switching power supply to an implantable cardioverter defibrillator, it is necessary to make advance judgments on the corresponding power consumption of each functional module of the implantable cardioverter defibrillator and the characteristics of the battery, and to divide the scenarios that the implantable cardioverter defibrillator will face in advance.

[0071] Please refer to Figure 1 Based on the above research, an embodiment of the present invention provides a power supply unit for an implantable cardioverter defibrillator, which includes: a switching power supply 1, a linear power supply 2 and a controller 3; the output of the power supply unit includes VDD and VPP; the controller 3 includes a custom mode and a plurality of special scene modes; when the controller 3 is in the custom mode, the switching power supply 1 and the linear power supply 2 work based on a set program; the controller 3 is configured to set the custom mode and the special scene mode according to the timing corresponding to the current application scenario of the implantable cardioverter defibrillator according to the application scenario, so as to control the working states of the switching power supply 1 and the linear power supply 2, and realize the independent or joint output of VDD and VPP corresponding to the application scenario.

[0072] VDD and VPP are two relatively independent power supply outputs. VDD is mainly used for the main chip and its auxiliary circuits, the bus of the defibrillator chip and the external RAM and other functional modules; VPP is used for sensors, telemetry modules and radio frequency modules and other functional modules. The voltage of VDD can be selected from 0.6V~1.5V, preferably 0.8V~1.2V, and the voltage of VPP can be selected from 1.8V~2.4V, preferably 2.0V~2.2V. VDD can be further subdivided into VDDA and VDDD, where VDDA is mainly used to power analog circuits, such as the analog circuit part attached to the main chip and the analog circuit part attached to the defibrillator chip. The voltage of VDDA can be selected from 1.1V~1.3V, preferably 1.2V. VDDD is mainly used to power digital circuits, such as the CPU of the main chip and the digital circuits on the chip. The voltage of VDDD can be selected from 0.8V~1.2V.

[0073] VDD can be powered by the output of the switching power supply 1 alone, or by the output of the linear power supply 2 alone. In some cases, VDD can also be powered by the combined output of the switching power supply 1 and the linear power supply 2. Similarly, VPP can be powered by the output of the switching power supply 1 alone, or by the output of the linear power supply 2 alone. In some cases, VPP can also be powered by the combined output of the switching power supply 1 and the linear power supply 2. Optionally, the linear power supply 2 can include only one conversion module, or the linear power supply 2 can include two or more conversion modules to provide additional two or more linear conversion outputs to meet the high current requirements of high-power consumption modules. In a preferred embodiment, the linear power supply 2 includes two independent conversion modules, namely a first module 21 and a second module 22. The first module 21 is a permanent module, and the second module 22 is a shunt module.

[0074] Please refer to Figures 2 to 8 , the custom mode (ALTER) of the controller 3 can be configured to be turned on (indicated by a high level) or turned off (indicated by a low level). When the controller 3 is in a special scene mode, the custom mode is in the off state, and the working state of the switching power supply 1 and the linear power supply 2 is uniquely determined based on the selected special scene mode. When the controller 3 is not in a special scene mode, the custom mode is configured to be turned on, and the working state of the switching power supply 1 and the linear power supply 2 is determined based on the program of the custom mode and the normal working requirements of the implantable cardioverter defibrillator, that is, the working state of the switching power supply 1 and the linear power supply 2 is not uniquely determined.

[0075] In one embodiment, the custom mode includes:

[0076] Program 1: The linear power supply 2 is used to output VPP, the switching power supply 1 is used to output VDD, and the linear power supply 2 and the switching power supply 1 are configured to delay start; the program 1 is used to start or shut down the switching period of the RF program control.

[0077] Program 2: The linear power supply 2 is used to output VPP and VDD; the program 2 is used in the RF program control process.

[0078] Program 3: Using the switching power supply 1 to output VPP and VDD; Program 3 is used for the buffer period before and after charging the defibrillation capacitor.

[0079] Taking Formula 2 as an example, it is explained that the working states of the switching power supply 1 and the linear power supply 2 are not uniquely determined. Formula 2 limits the use of the linear power supply 2 to output VPP and VDD, but does not limit the working state of the switching power supply 1. Therefore, the switching power supply 1 can be in the off state or in the working state. The switching power supply 1 can output VPP combined with the VPP output by the linear power supply 2, and can also output VDD combined with the VDD output by the linear power supply 2. The working states of the switching power supply 1 and the linear power supply 2 of other formulas can be understood by reference.

[0080] It should be noted that in each program of the custom mode, the linear power supply 2 can use a single conversion module output (such as only using the first module 21 output), or can use the combined output of more than two conversion modules, which is not limited in this embodiment.

[0081] Optionally, the special scene mode includes any of the following modes:

[0082] Magnetic resonance compatible mode: turn off the switching power supply 1, and use the first module 21 to output VPP and VDD;

[0083] High voltage mode: using the switching power supply 1 to output VPP, and using the first module 21 to output VDD;

[0084] High voltage and remote sensing program control mode: the switching power supply 1 is used to output VPP, and the second module 22 is used to output the part of VDD used to power the analog circuit (referring to VDDA);

[0085] RF mode: the switching power supply 1 is used to output VPP, and the first module 21 and the second module 22 are used to mix and output VDD;

[0086] Telemetry mode: turn off the switching power supply 1 and use the first module 21 to output VPP and VDD.

[0087] It should be noted that in each special scene mode, the status of the switching power supply 1 and the linear power supply 2 is uniquely determined, and the unused power conversion module will be turned off in each special scene mode. In particular, the priorities of the magnetic resonance compatible mode, high voltage mode, high voltage and telemetry program control mode, radio frequency mode and telemetry mode are arranged from high to low, that is, in a certain application scenario, when a high priority event occurs, a low priority event will be interrupted. For example, when the controller 3 is in the radio frequency mode, the implantable cardioverter defibrillator finds that high voltage defibrillation is required, it will switch to a higher priority high voltage mode.

[0088] Optionally, in addition to the custom mode and the special scene mode, the controller 3 also includes a nominal mode. When the controller 3 is in the nominal mode, the switching power supply 1 and the linear power supply 2 are configured based on the normal working requirements of the implantable cardioverter defibrillator. In the nominal mode, no program limitation is imposed on the switching power supply 1 and the linear power supply 2. At this time, the switching power supply 1 and the linear power supply 2 can be configured in different combinations according to the normal working requirements of the implantable cardioverter defibrillator, that is, when the controller 3 is in the nominal mode, the working states of the switching power supply 1 and the linear power supply 2 are not uniquely determined. Their specific working states can be understood by referring to the prior art, and this embodiment does not make any special limitation. Optionally, the priority of the special scene mode is higher than the nominal mode.

[0089] By setting a custom mode combined with the setting of multiple special scene modes, the multi-scenario requirements of the implantable cardioverter defibrillator can be met. According to different scenarios, the chip and firmware of the implantable cardioverter defibrillator can be used to achieve programmable power management, thereby generating different power timings, ensuring the reliable implementation of the priority of each function, reducing power consumption, and meeting the reliability and efficiency requirements of the implantable cardioverter defibrillator for power management.

[0090] The power supply unit of the implantable cardioverter defibrillator provided by the present invention is further described below in conjunction with embodiments of several application scenarios.

[0091] [Example 1] Start the RF program control scenario:

[0092] Please refer to Figure 2, the RF program control startup scenario includes a telemetry activation phase PA1, a switching phase PA2, a delay phase PA3 and a RF program control phase PA4 which are arranged in sequence; wherein the switching phase PA2 starts with the RF module being turned on, and the telemetry module is turned off no later than the end of the delay phase PA3; in the telemetry activation phase PA1, the controller 3 is configured as the telemetry mode; in the switching phase PA2, the controller 3 is configured as the RF mode; in the delay phase PA3, the controller 3 is configured as the program one; in the RF program control phase PA4, the controller 3 is configured as the program two.

[0093] Radio frequency programming is generally carried out in hospitals and other places. When used, the radio frequency module can be activated by bringing the telemetry transmitter close to the implantable cardioverter defibrillator. The telemetry module of the implantable cardioverter defibrillator can detect the electromagnetic signal emitted by the telemetry transmitter. Figure 2 Before the RF module is activated, it is in the telemetry activation phase PA1, at which the controller 3 is configured in telemetry mode, turns off the switch power supply 1 susceptible to electromagnetic interference, and only uses the first module 21 to output VPP and VDD.

[0094] After the RF module is activated, it performs RF wireless transmission with the program-controlled device. Figure 2 In the figure, the RF output is high level. At this time, the telemetry activation stage PA1 enters the switching stage PA2, and the controller 3 switches from the telemetry mode to the RF mode. The switching power supply 1 is used to output VPP, and the first module 21 and the second module 22 are used to mix and output VDD. The RF module is a module with high power consumption. When it is started, if only one module is used to output VPP and VDD, it may not meet its current requirements, which may easily lead to instability. For this reason, when the RF module is turned on, the switching power supply 1 is turned on to output VPP, and the first module 21 is turned on and mixed with the second module 22 to output VDD.

[0095] Then, the switching stage PA2 enters the delay stage PA3, and the controller 3 switches from the RF mode to the program 1, that is, the linear power supply 2 outputs VPP, the switching power supply 1 outputs VDD, and the linear power supply 2 and the switching power supply 1 are configured to delay starting. Here, the linear power supply 2 outputs VDD in the switching stage PA2 and switches to the switching power supply 1 outputs VDD, and the switching power supply 1 outputs VPP and switches to the linear power supply 2 outputs VPP. Since the voltages of VDD and VPP are different, a certain switching time is required. The function of the program 1 here is mainly to increase the delay for switching and improve the switching stability.

[0096] Here, in the delay stage PA3, after switching, linear power supply 2 is used to output VPP, which can be used to provide low-noise power supply to the RF module. Using switching power supply 1 to output VDD can meet the high power consumption requirements of the switching startup phase and improve the stability of the switching process. The duration of the delay stage PA3 is preferably several milliseconds to tens of milliseconds, for example, it can be set to 10 milliseconds. When the delay stage PA3 ends, the telemetry module is turned off and telemetry stops.

[0097] In the RF programming stage PA4, the controller 3 is preferably configured as program 2, that is, the linear power supply 2 is used to output VPP and VDD. The output power of the linear power supply 2 can meet the requirements of the RF module when it is in working state, while ensuring low noise of the power supply. The switching power supply 1 can be set to output according to the normal working requirements of the implantable cardioverter defibrillator, and there is no restriction on its working state here. Please refer to Figure 3 In the RF programming and data transmission scenario, when telemetry is not started (TEL is low level) and high-voltage charging is not started (HV is low level), the controller 3 preferably remains in program two.

[0098] [Example 2] End the RF program control scenario:

[0099] Please refer to Figure 4 , the ending RF programming scenario includes a RF programming stage PB1, a delay stage PB2 and a remote follow-up stage PB3 which are arranged in sequence; in the RF programming stage PB1, the controller 3 is configured as the program two; in the delay stage PB2, the controller 3 is configured as the program one; in the remote follow-up stage PB3, the controller 3 is configured as the RF mode; after the remote follow-up stage PB3 ends, the controller 3 is configured as the nominal mode.

[0100] The RF programming stage PB1 is a continuation of the RF programming stage PA4 of the first embodiment, and the controller 3 is also configured as program 2. After the RF programming is completed, the RF module will switch to the remote follow-up mode (RMS). During this switching process, it is preferred to insert a delay stage PB2 to provide a delay buffer for the switching and improve the stability of the switching process. The delay stage PB2 is similar to the delay stage PA3 of the first embodiment, and the controller 3 is also configured as program 1.

[0101] After the delay phase PB2, the remote follow-up phase PB3 is entered. At this time, the controller 3 is configured in the RF mode, the switch power supply 1 starts to output VPP, the first module 21 is turned on and mixed with the second module 22 to output VDD, and the custom mode is in the off state. The remote follow-up mode (RMS) is a mode in which the remote terminal can interact with each other in the form of timed broadcasts. In order to reduce energy consumption, the RF module will be triggered to start at a fixed time. If data needs to be transmitted, further data transmission will be performed. If no data needs to be transmitted, it will quickly go back to sleep. Figure 4 As shown, after the remote follow-up phase PB3 ends, the controller 3 is configured to the nominal mode, at which time the radio frequency module is turned off and the radio frequency communication ends.

[0102] [Example 3] Start remote follow-up scenario:

[0103] Please refer to Figure 5 Before starting the remote follow-up scenario, the controller 3 is configured to the nominal mode; in the remote follow-up scenario, the controller 3 is configured to the RF mode, the switching power supply 1 turns on the output VPP, the first module 21 turns on and mixes the output VDD with the second module 22, and the custom mode is in the off state.

[0104] [Example 4] Magnetic field detection scenario in remote follow-up:

[0105] Please refer to Figure 6 The magnetic field detection scenario in the remote follow-up includes a radio frequency off stage PC1, a waiting stage PC2 and a magnetic resonance stage PC3 which are arranged in sequence; wherein the radio frequency off stage PC1 ends with the end of the cardiac cycle in which the magnetic field signal is detected; in the radio frequency off stage PC1, the controller 3 is configured as the radio frequency mode; in the waiting stage PC2, the controller 3 is configured as the nominal mode; in the magnetic resonance stage PC3, the controller 3 is configured as the magnetic resonance compatible mode.

[0106] As mentioned above, remote follow-up can be configured to be performed at a scheduled time. In some cases, the patient may need to undergo a magnetic resonance imaging (MRI) while the remote follow-up is being performed. In this case, the timing control of the magnetic field detection scene is based on the magnetic field trigger in the MRI examination room, that is, after the patient enters the MRI examination room, the telemetry module of the implantable cardioverter defibrillator can detect the magnetic field signal and know that the implantable cardioverter defibrillator is currently in the MRI examination room and an MRI scan will be performed later.

[0107] It is understandable that the magnetic field detection scenario of this embodiment is in remote follow-up mode before the mode switching, and the remote follow-up should be stopped first. Considering the safety of the power unit mode switching, in the RF shutdown phase PC1, the controller 3 does not switch immediately after detecting the magnetic field signal, but waits for the current cardiac cycle to end before switching the power mode. Before the RF shutdown phase PC1 ends, the RF module is turned off and the RF communication ends.

[0108] When the RF off phase PC1 ends, the waiting phase PC2 begins, and the controller 3 switches to the nominal mode to serve as a buffer. At this time, the telemetry module can still detect the magnetic field signal. The length of the waiting phase PC2 can be set according to the actual situation. Generally, it may take several minutes for a patient to prepare from entering the MRI examination room to starting the MRI scan, and the length of the waiting phase PC2 should be less than this preparation time.

[0109] In the magnetic resonance phase PC3 , the controller 3 is configured to be in a magnetic resonance compatible mode, the switching power supply 1 is turned off, and the first module 21 is used to output VPP and VDD to avoid the influence of a high-intensity magnetic field on the switching power supply 1 .

[0110] Optionally, after the MRI scan is completed, the magnetic resonance phase PC3 ends through changes in the magnetic field signal detected by the telemetry module, or after a certain time delay, and the controller 3 can be switched from the magnetic resonance compatible mode to the nominal mode and enter a normal working state.

[0111] [Example 5] Switching to telemetry during RF communication and accompanying high-voltage charging scenario:

[0112] Please refer to Figure 7 , the switching to telemetry and high-voltage charging scenario in the RF communication includes the RF shutdown stage PD1, the delay stage PD2, the telemetry stage PD3, the high-voltage charging stage PD4 and the high-voltage and telemetry program control stage PD5 which are arranged in sequence; in the RF shutdown stage PD1, the controller 3 is configured as the program two; in the delay stage PD2, the controller 3 is configured as the program one; in the telemetry stage PD3, the controller 3 is configured as the telemetry mode; in the high-voltage charging stage PD4, the controller 3 is sequentially configured as the program three, the high-voltage mode and the program three; in the high-voltage and telemetry program control stage PD5, the controller 3 is configured as the high-voltage and telemetry program control mode when the telemetry module is turned on, and the controller 3 is configured as the nominal mode when the telemetry module is turned off.

[0113] In some embodiments, the high voltage charging can be activated by sending a telemetry signal by a telemetry transmitter. If the implantable cardioverter defibrillator is in the process of radio frequency programming before the telemetry is activated, the radio frequency communication needs to be turned off first, and this stage is the radio frequency off stage PD1.

[0114] During the RF programming process, as in Embodiment 1 and Embodiment 2, the controller 3 is configured as Program 2. Preferably, the RF off stage PD1 ends at the end of the cardiac cycle when the telemetry signal is detected. In the RF off stage PD1, after the telemetry module detects the telemetry signal, the controller 3 does not immediately switch the mode, and preferably waits for the end of the current cardiac cycle before switching to the delay stage PD2.

[0115] In the delay phase PD2, the controller 3 is configured as program 1, which also serves to increase the delay for switching and improve the switching stability.

[0116] In the telemetry phase PD3, the controller 3 is configured in telemetry mode, the custom mode is turned off, and the HV phase is set to a high level, ready to enter high-voltage charging. The duration of the telemetry phase PD3 can be configured according to actual conditions.

[0117] In the high-voltage charging stage PD4, the controller 3 is sequentially configured as program 3, high-voltage mode, and program 3. Figure 7 The level state of HV in the middle, when HV is at a high level, represents the time period for actually charging the defibrillator capacitor. When switching to the high-voltage charging stage PD4, the defibrillator capacitor is not charged immediately, but first buffered for a short period of time. During the buffering time, the controller 3 is configured as program three, that is, the switch power supply 1 is used to output VPP and VDD, and the custom mode is turned on at this time. When charging the defibrillator capacitor, the battery voltage will be pulled down. At this time, the too low voltage may make it impossible to use the linear power supply 2 to output VPP, so the VPP required by the telemetry module can only be supplied by the switch power supply 1. Therefore, before and after charging the defibrillator capacitor, the controller 3 is first configured as program three, and VPP and VDD are switched to the switch power supply 1 output for buffering, which can effectively ensure the output stability of VPP and VDD when charging the defibrillator capacitor, and ensure the reliable operation of the telemetry module at this stage. In the process of formally charging the defibrillator capacitor, the controller 3 is configured as high-voltage mode, the custom mode is turned off, the switch power supply 1 is used to output VPP, and the first module 21 is used to output VDD.

[0118] After completing a stage of high-voltage charging, the high-voltage and telemetry program control stage PD5 is entered. This stage mainly performs telemetry communication. By judging whether the charging meets the demand, it can be determined whether high-voltage charging needs to be continued in the future. In the high-voltage and telemetry program control stage PD5, the working mode of the controller 3 at this time can be determined according to whether the telemetry module is working or not. When the telemetry module is turned on, the controller 3 is configured to the high-voltage and telemetry program control mode, that is, the switching power supply 1 is used to output VPP, and the second module 22 is used to output the part of VDD used to power the analog circuit, that is, the second module 22 is used to output VDDA. When the telemetry module is turned off, the controller 3 is configured to the nominal mode.

[0119] It can be understood that after the high-voltage and telemetry program control stage PD5, if the charging does not meet the demand, the next high-voltage charging stage PD4 can be entered to repeatedly charge the defibrillation capacitor.

[0120] [Example 6] Ending the high voltage event and detecting the magnetic field scenario:

[0121] Please refer to Figure 8 , ending the high-voltage event and detecting the magnetic field scene includes a high-voltage charging stage PE1, a delay stage PE2 and a magnetic resonance stage PE3 which are arranged in sequence; wherein the delay stage PE2 ends with the end of the cardiac cycle in which the magnetic field signal is detected; in the high-voltage charging stage PE1, the controller 3 is configured as the high-voltage mode; in the delay stage PE2, the controller 3 is configured as the nominal mode; in the magnetic resonance stage PE3, the controller 3 is configured as the magnetic resonance compatible mode.

[0122] During magnetic resonance imaging (MRI), the implantable cardioverter-defibrillator will be exposed to a magnetic field of up to several Tesla. This process is a test for all modules of the implantable cardioverter-defibrillator. Therefore, in terms of control logic, the high field strength required for MRI scanning should be set to the highest priority. At this time, after the high-voltage event (such as high-voltage charging, defibrillation, etc.) is completed, subsequent high-voltage events or other events will not be executed, and the MRI scanning should be responded to instead.

[0123] This sixth embodiment provides a scenario where a high-voltage event ends and a magnetic field signal is detected. First, the implantable cardioverter defibrillator is charging the defibrillation capacitor. This is the high-voltage charging phase PE1, and the controller 3 is configured to be in the high-voltage mode. After this phase ends, the delay phase PE2 is entered, and the controller 3 switches to the nominal mode.

[0124] In the delay phase PE2, the telemetry module detects the magnetic field signal and learns that the implantable cardioverter defibrillator is currently in the MRI examination room and an MRI scan is about to be performed. Preferably, the delay phase PE2 ends with the end of the cardiac cycle in which the magnetic field signal is detected. In the delay phase PE2, after the telemetry module detects the magnetic field signal, the controller 3 does not immediately switch the mode, and preferably waits for the end of the current cardiac cycle before switching to the magnetic resonance phase PE3.

[0125] In the magnetic resonance phase PE3, the controller 3 is configured to be in a magnetic resonance compatible mode.

[0126] An embodiment of the present invention further provides an implantable cardioverter defibrillator, which includes the power supply unit of the implantable cardioverter defibrillator as described above.

[0127] In summary, in the power supply unit of the implantable cardioverter defibrillator and the implantable cardioverter defibrillator provided by the present invention, the power supply unit of the implantable cardioverter defibrillator includes: a switching power supply, a linear power supply and a controller; the output of the power supply unit includes VDD and VPP; the controller includes a custom mode and a plurality of special scene modes; when the controller is in the custom mode, the switching power supply and the linear power supply work based on a set program; the controller is configured to set the custom mode and the special scene mode according to the timing corresponding to the current application scenario of the implantable cardioverter defibrillator according to the application scenario, To control the working state of the switching power supply and the linear power supply, and realize the independent or joint output of VDD and VPP corresponding to the application scenario; wherein the custom mode includes: program one: adopt the linear power supply to output VPP, adopt the switching power supply to output VDD, and the linear power supply and the switching power supply are configured to delay start; the program one is used to start or close the switching period of RF program control; program two: adopt the linear power supply to output VPP and VDD; the program two is used in the RF program control process; program three: adopt the switching power supply to output VPP and VDD; the program three is used for the buffer period before and after charging the defibrillation capacitor. With such configuration, through the setting of the custom mode and the setting of multiple special scene modes, the multi-scenario requirements of the implantable cardioverter defibrillator can be met. According to different scenarios, the chip and firmware of the implantable cardioverter defibrillator can realize programmable management of the power supply, so that different power supply timings can be generated, ensuring the reliable implementation of the priority of each function, and reducing power consumption, meeting the reliability and efficiency requirements of the implantable cardioverter defibrillator for power management.

[0128] It should be noted that the above embodiments can be combined with each other. The above description is only a description of the preferred embodiments of the present invention, and does not limit the scope of the present invention. Any changes and modifications made by ordinary technicians in the field of the present invention based on the above disclosure are within the protection scope of the present invention.

Claims

1. A power supply unit for an implantable cardioverter defibrillator, characterized in that: include: A switching power supply, a linear power supply and a controller; the output of the power supply unit includes VDD and VPP; the controller includes a custom mode and multiple special scene modes; When the controller is in the custom mode, the switching power supply and the linear power supply work based on a set program; The controller is configured to set the custom mode and the special scenario mode according to the timing corresponding to the application scenario according to the current application scenario of the implantable cardioverter defibrillator, so as to control the working state of the switching power supply and the linear power supply, and realize the independent or joint output of VDD and VPP corresponding to the application scenario; The custom mode includes: Program 1: The linear power supply is used to output VPP, the switching power supply is used to output VDD, and the linear power supply and the switching power supply are configured to delay starting; the program 1 is used to start or shut down the switching period of the RF program control; Program 2: Use the linear power supply to output VPP and VDD; Program 2 is used in the RF program control process; Program 3: Using the switching power supply to output VPP and VDD; Program 3 is used for the buffer period before and after charging the defibrillation capacitor.

2. The power supply unit of the implantable cardioverter defibrillator according to claim 1, characterized in that: The linear power supply includes a first module and a second module; the special scene mode includes any of the following modes: Magnetic resonance compatible mode: turn off the switch power supply and use the first module to output VPP and VDD; High voltage mode: using the switching power supply to output VPP, and using the first module to output VDD; High voltage and remote sensing program control mode: using the switching power supply to output VPP, and using the second module to output the portion of VDD used to power the analog circuit; RF mode: using the switching power supply to output VPP, and using the first module and the second module to mix and output VDD; Telemetry mode: turn off the switch power supply and use the first module to output VPP and VDD; The controller further includes a nominal mode, and when the controller is in the nominal mode, the switching power supply and the linear power supply are configured based on normal operating requirements of the implantable cardioverter-defibrillator; The priorities of the magnetic resonance compatible mode, the high voltage mode, the high voltage and telemetry program control mode, the radio frequency mode, the telemetry mode and the nominal mode are arranged from high to low.

3. The power supply unit of the implantable cardioverter defibrillator according to claim 2, characterized in that: The application scenario includes starting a radio frequency program control scenario; The start-up RF program control scenario includes a telemetry activation phase, a switching phase, a delay phase, and a RF program control phase which are sequentially arranged; wherein the switching phase starts with the RF module being turned on, and the telemetry module is turned off no later than the end of the delay phase; In the telemetry activation stage, the controller is configured in the telemetry mode; In the switching phase, the controller is configured to the radio frequency mode; During the delay phase, the controller is configured as the program 1; During the radio frequency programming stage, the controller is configured as program two.

4. The power supply unit of the implantable cardioverter defibrillator according to claim 2, characterized in that: The application scenario includes ending the radio frequency program control scenario; The end of the radio frequency program control scenario includes a radio frequency program control phase, a delay phase, and a remote follow-up phase that are arranged in sequence; In the radio frequency programming stage, the controller is configured as the second program; During the delay phase, the controller is configured as the program 1; During the remote follow-up phase, the controller is configured to be in the radio frequency mode; After the remote follow-up period ends, the controller is configured to the nominal mode.

5. The power supply unit of the implantable cardioverter defibrillator according to claim 2, characterized in that: The application scenario includes starting a remote follow-up scenario; Before starting the remote follow-up scenario, the controller is configured to the nominal mode; In the remote follow-up initiation scenario, the controller is configured to be in the radio frequency mode.

6. The power supply unit of the implantable cardioverter defibrillator according to claim 2, characterized in that: The application scenarios include magnetic field detection scenarios in remote follow-up; The magnetic field detection scenario in the remote follow-up includes a radio frequency off stage, a waiting stage and a magnetic resonance stage which are arranged in sequence; wherein the radio frequency off stage ends when the end of the cardiac cycle in which the magnetic field signal is detected is taken as the end; In the radio frequency off stage, the controller is configured to be in the radio frequency mode; During the waiting phase, the controller is configured in the nominal mode; During the magnetic resonance phase, the controller is configured to be in the magnetic resonance compatible mode.

7. The power supply unit of the implantable cardioverter defibrillator according to claim 2, characterized in that: The application scenarios include switching to telemetry in radio frequency communication accompanied by high-voltage charging scenarios; The switching to telemetry and high-voltage charging scenario in the radio frequency communication includes a radio frequency shutdown phase, a delay phase, a telemetry phase, a high-voltage charging phase, and a high-voltage and telemetry program control phase arranged in sequence; In the radio frequency off stage, the controller is configured as the second program; During the delay phase, the controller is configured as the program 1; In the telemetry stage, the controller is configured to be in the telemetry mode; In the high-voltage charging stage, the controller is sequentially configured as the program three, the high-voltage mode, and the program three; In the high-voltage and telemetry program control stage, the controller is configured to the high-voltage and telemetry program control mode when the telemetry module is turned on, and the controller is configured to the nominal mode when the telemetry module is turned off.

8. The power supply unit of the implantable cardioverter defibrillator according to claim 2, characterized in that: The application scenarios include ending a high voltage event and detecting a magnetic field scenario; The process of ending the high-voltage event and detecting the magnetic field scene includes a high-voltage charging phase, a delay phase, and a magnetic resonance phase that are sequentially arranged; wherein the delay phase ends when the end of the cardiac cycle in which the magnetic field signal is detected is the end; In the high-voltage charging stage, the controller is configured to be in the high-voltage mode; During the delay phase, the controller is configured in the nominal mode; During the magnetic resonance phase, the controller is configured to be in the magnetic resonance compatible mode.

9. The power supply unit of the implantable cardioverter defibrillator according to claim 1, characterized in that: VDD is used for the main chip and its auxiliary circuits, the bus of the defibrillator chip and the external RAM; VPP is used for sensors, telemetry modules and RF modules.

10. An implantable cardioverter defibrillator, characterized in that: A power supply unit comprising an implantable cardioverter defibrillator according to any one of claims 1 to 9.

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