CN113812960B - Sensing unit and implantable heart monitor - Google Patents
Sensing unit and implantable heart monitor Download PDFInfo
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- CN113812960B CN113812960B CN202111130632.6A CN202111130632A CN113812960B CN 113812960 B CN113812960 B CN 113812960B CN 202111130632 A CN202111130632 A CN 202111130632A CN 113812960 B CN113812960 B CN 113812960B
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
- A61B5/283—Invasive
- A61B5/287—Holders for multiple electrodes, e.g. electrode catheters for electrophysiological study [EPS]
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- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
- A61B5/361—Detecting fibrillation
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- A—HUMAN NECESSITIES
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- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
- A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7235—Details of waveform analysis
- A61B5/725—Details of waveform analysis using specific filters therefor, e.g. Kalman or adaptive filters
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- H—ELECTRICITY
- H03—ELECTRONIC CIRCUITRY
- H03H—IMPEDANCE NETWORKS, e.g. RESONANT CIRCUITS; RESONATORS
- H03H11/00—Networks using active elements
- H03H11/02—Multiple-port networks
- H03H11/04—Frequency selective two-port networks
- H03H11/12—Frequency selective two-port networks using amplifiers with feedback
- H03H11/1217—Frequency selective two-port networks using amplifiers with feedback using a plurality of operational amplifiers
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Abstract
The invention relates to a sensing unit which is applied to an implanted heart monitor and is used for carrying out band-pass filtering on output signals of a sensing electrode and filtering low-frequency signals of a left transition band of low-frequency signals and high-frequency signals of a right transition band of high-frequency signals. The technical scheme of the invention has the advantages of high gain, low power consumption, good band-pass performance and adjustable gain.
Description
Technical Field
The invention belongs to the field of heart rhythm management equipment, and particularly relates to improvement of heart rhythm classification and electrocardio data processing methods.
Background
Cardiac rhythm management devices are used to enable monitoring or monitoring and treating abnormal cardiac rhythms.
The heart rhythm monitoring devices include wearable heart monitoring devices (e.g., holter), portable wearable devices such as smart watches, implantable heart monitoring devices (ICMs).
Taking an implanted heart monitor as an example, the implanted heart monitor is implanted under the skin of the chest of a human body, a sensing electrode is arranged on the heart detector, and the sensing electrode senses abnormal events of the heart rhythm of the human body and records electrocardiosignal segments of the abnormal heart rhythm events in a memory.
In order to sense the electrocardiosignals, the sensing circuit of the implantable heart monitor must be capable of providing a band-pass filtering function, so that the sensing circuit can effectively sense the electrocardiosignals and eliminate noise signals except the electrocardiosignals. And should have good frequency amplitude response characteristics, theoretically the better its frequency amplitude response characteristics are, the more beneficial it is for the perceived signal processing.
Therefore, how to ensure the signal processing effects of the sensing circuit, such as filtering, amplitude-frequency characteristics, and the like, while reducing power consumption is very important.
Disclosure of Invention
The invention aims to provide an implanted heart monitor sensing circuit which has excellent frequency amplitude response characteristics and is beneficial to processing signals in subsequent steps.
A sensing unit comprises a first passive low-pass filter, a second passive low-pass filter, a first passive high-pass filter, a second passive high-pass filter, a differential-to-single-ended filter amplifier and a first active second-order low-pass filter amplifier, wherein the first passive low-pass filter receives a first signal input, the output end of the first passive low-pass filter is connected with the first passive high-pass filter, the second passive low-pass filter receives a second signal input, the output end of the second passive low-pass filter is connected with the second passive high-pass filter, the output ends of the first passive high-pass filter and the second passive high-pass filter are connected with the input end of the differential-to-single-ended filter amplifier, and the output end of the differential-to-single-ended filter amplifier is connected with the first active second-order low-pass filter amplifier.
In an embodiment of the present invention, the sensing unit further includes a protection module, and the protection module is connected in parallel between the input ends of the first signal and the second signal.
In an embodiment of the invention, the protection module includes inverse parallel zener diodes.
In an embodiment of the invention, the sensing unit further includes a third passive high-pass filter, and the third passive high-pass filter is connected to the output end of the first active second-order low-pass filter amplifier.
In an embodiment of the invention, the sensing unit further includes a second active second-order low-pass filter amplifier, and the second active second-order low-pass filter amplifier is connected to an output end of the third passive high-pass filter.
In an embodiment of the invention, the sensing unit further includes a fourth passive high-pass filter, and an input end of the fourth passive high-pass filter is connected to an output end of the second active second-order low-pass filter amplifier.
In an embodiment of the invention, the differential-to-single-ended filter amplifier includes two proportional operational amplifiers, and second input ends of the two proportional operational amplifiers are connected through a first resistor.
In an embodiment of the invention, the first resistor is a programmable resistor.
The present invention also provides an implantable heart monitor comprising,
the outer shell is provided with a plurality of grooves,
at least one sensing electrode disposed on the housing for receiving cardiac electrical signals,
a circuit assembly disposed within the housing, the circuit assembly comprising,
a sensing unit receiving an output of the sensing electrode,
an analog-to-digital conversion unit for converting the analog signal output by the sensing unit into a digital signal,
and the processor receives and processes the output signal of the analog-to-digital conversion unit and stores the data in the storage unit.
In an embodiment of the invention, the implantable heart monitor further comprises a wireless communication unit, the wireless communication unit establishing a communication link between the processor and an external device.
In an embodiment of the present invention, the sensing unit includes a first passive low-pass filter, a second passive low-pass filter, a first passive high-pass filter, a second passive high-pass filter, a differential-to-single-ended filter amplifier, and a first active second-order low-pass filter amplifier, where the first passive low-pass filter receives a first signal input, an output end of the first passive low-pass filter is connected to the first passive high-pass filter, the second passive low-pass filter receives a second signal input, an output end of the second passive low-pass filter is connected to the second passive high-pass filter, output ends of the first passive high-pass filter and the second passive high-pass filter are connected to an input end of the differential-to-single-ended filter amplifier, and an output end of the differential-to-single-ended filter amplifier is connected to the first active second-order low-pass filter amplifier.
In an embodiment of the invention, the differential-to-single-ended filter amplifier includes two proportional operational amplifiers, and second input terminals of the two proportional operational amplifiers are connected through a first resistor.
In an embodiment of the present invention, the external device sends a gain parameter to the processor through a wireless communication unit, and the processor adjusts the resistance of the first resistor according to the gain parameter.
In an embodiment of the present invention, the sensing unit further includes a third passive high-pass filter, a second active second-order low-pass filter amplifier, and a fourth passive high-pass filter; the third passive high-pass filter is connected with the output end of the first active second-order low-pass filter amplifier; the second active second-order low-pass filter amplifier is connected with the output end of the third passive high-pass filter; the input end of the fourth passive high-pass filter is connected with the output end of the second active second-order low-pass filter amplifier; an implantable heart monitor further comprising an atrial fibrillation/ventricular fibrillation monitoring module and a bradycardia monitoring module; and the output signal of the fourth passive high-pass filter is connected with the atrial fibrillation/ventricular fibrillation monitoring module, and the output signal of the second active second-order low-pass filter amplifier is connected with the bradycardia monitoring module.
According to the technical scheme, the band-pass filtering is realized and the high gain is effectively realized through the combination of the passive low-pass filtering, the passive high-pass filtering, the differential-to-single-ended amplifier and the active low-pass amplifier according to the scheme of the invention. And a plurality of 1-order passive high-pass filters are combined, so that good high-pass filtering performance is realized, and the power consumption is saved. The combination of the passive 1-order low-pass filter and the active 2-order low-pass filter realizes good low-pass filtering performance. And the circuit gain is adjustable. And outputting the sensing signals through two channels according to different requirements.
Drawings
FIG. 1 is a schematic diagram of an implantable heart monitor implanted in a human body.
Fig. 2 is a schematic structural diagram of a first embodiment of an internal circuit assembly of the implantable heart monitor.
Fig. 3 is a schematic structural diagram of a second embodiment of an internal circuit assembly of the implantable heart monitor.
Fig. 4 is a schematic structural diagram of a third embodiment of an internal circuit assembly of the implantable heart monitor.
Fig. 5 is a structural schematic diagram of a sensing unit of an implanted heart monitor.
Fig. 6 is a schematic view of a first embodiment of the sensing unit shown in fig. 5.
Fig. 7 is a schematic view of a second embodiment of the sensing unit shown in fig. 5.
Fig. 8 is a schematic diagram of a third embodiment of the sensing unit shown in fig. 5.
Fig. 9 is a schematic diagram of a fourth embodiment of the sensing unit shown in fig. 5.
FIG. 10 is a graph of amplitude-frequency characteristics of the sensing unit shown in FIG. 5
Detailed Description
The present invention is described below with reference to the accompanying drawings, in which an implantable heart monitor is schematically illustrated, and the actual mechanical structure and shape thereof may be different from those of the present invention without affecting the understanding of the present invention by those skilled in the art.
Illustratively, referring to FIG. 1, an implantable heart monitor 1 is shown surgically implanted within a human body 100, located subcutaneously in the chest of the body, for collecting cardiac rhythm events. The implantable heart monitor 1 extends in a strip shape, and the extending direction of the implantable heart monitor forms an included angle of 45 degrees with the vertical direction. The implantable heart monitor 1 comprises a housing 11 and a circuit assembly (not shown in the figure) inside the housing, wherein one end of the surface of the housing 11 is provided with a first sensing electrode 12, and the second end of the surface of the housing is provided with a second sensing electrode 13. The first sensing electrode 12 and the second sensing electrode 13 are connected with a circuit component inside the shell to form a loop for sensing electrocardiosignals.
One end of the housing 11 is a head 111, the first electrode 12 is disposed on the head 111, and the head 111 accommodates an antenna for communication in the circuit assembly (not shown), and the head 111 is made of a material capable of passing electromagnetic signals.
Referring to fig. 2, the circuit assembly 14 includes a processor 141, and the processor 141 collects signals from various sensors, and processes the signals to monitor or monitor and treat abnormal heart rhythm. The processor 121 has functional circuitry, logic circuit units or software units for data processing, control of an implantable heart detector (ICM). The processor 121 is preferably a Central Processing Unit (CPU) or an ASIC-specific application integrated circuit or FPGA circuit.
The circuit assembly 14 further includes a sensing unit 142, the sensing unit 142 is connected to the first sensing electrode 12 and the second sensing electrode 13 shown in fig. 1, the first sensing electrode 12 and the second sensing electrode 13 receive the near body surface electrical signal generated by the heart, the sensing unit 142 processes the near body surface electrical signal and outputs the near body surface electrical signal to an analog-to-digital conversion unit 143, the analog-to-digital conversion unit 143 converts the electrocardiographic signal into a digital signal, and provides the digital signal to the processor 141, and the digital signal is a basis for the processor 141 to process electrocardiographic data.
The circuit assembly 14 further includes a memory unit 144, and the processor 141 senses abnormal events of the human heart rhythm and records the cardiac electrical signal segments of the abnormal heart rhythm events in the memory unit 144.
As shown in fig. 3, which is a block diagram of another embodiment of the circuit assembly 14 according to the present invention, different from the embodiment shown in fig. 2, the circuit assembly 14 further includes a wireless communication unit 145, in an embodiment of the present invention, the wireless communication unit 145 is a bluetooth module, the wireless communication unit 145 is connected to the processor 141, and the processor 141 sends or receives data through the wireless communication unit 145. The wireless communication unit 145 includes a communication antenna 1451, the communication antenna 1451 is disposed within the head 111 of fig. 1, and the wireless communication unit 145 establishes a wireless communication link L with an external device by way of wireless communication, as shown in fig. 1, for communicating initialization parameters of the wireless communication unit 145 during an implantation phase, or setting parameters at a patient follow-up visit, or communicating with a patient handheld device to issue timely reminders or warnings to the patient.
As shown in fig. 4, which is a block diagram of another embodiment of the circuit assembly 14 according to the present invention, in this embodiment, the circuit assembly 14 further includes a power supply 146, and the power supply 146 supplies power to a power consumption unit in the circuit assembly 14. The circuit assembly 14 further includes a voltage monitoring unit 147, wherein the voltage monitoring unit 147 detects the voltage of the power supply 146 and transmits a voltage signal of the power supply 146 to the processor 141, and when the voltage monitoring unit 147 monitors that the voltage of the power supply 146 drops to a certain threshold, the processor 141 sends an alarm to an external device when communicating with the external device.
Fig. 5 is a schematic structural diagram of the sensing unit 142, where the sensing unit 142 includes a first passive low-pass filter 1421, a second passive low-pass filter 1422, a first passive high-pass filter 1423, a second passive high-pass filter 1424, a differential-to-single-ended filter 1425, and a first active second-order low-pass filter 1426, an output end of the first sensing electrode 12 is connected to an input end of the first passive low-pass filter 1421, an output end of the first passive low-pass filter 1421 is connected to the first passive high-pass filter 1423, an output end of the second sensing electrode 13 is connected to an input end of the second passive low-pass filter 1422, an output end of the second passive low-pass filter 1422 is connected to the second passive high-pass filter 1424, output ends of the first passive high-pass filter 1423 and the second passive single-ended filter 1424 are connected to an input end of the differential-to-single-ended filter 1425, and an output end of the differential-to-second active second-order low-pass filter 1426 is connected to an input end of the first passive high-pass filter 1426.
The near body surface electrical signals generated by the heart sensed by the first sensing electrode 12 and the second sensing electrode 13 enter the first passive low pass filter 1421 and the second passive low pass filter 1422, respectively, to perform preliminary filtering on high frequency signals, generally the high frequency signals are signals above 100HZ, then enter the first passive high pass filter 1423 and the second passive high pass filter 1424, respectively, to filter low frequency signals below 3HZ, and finally output signals S1 and S2. The signals S1 and S2 enter a differential-to-single-ended amplifier 1425 to convert the signals S1 and S2 into a single signal and amplify the signal. Preferably, the gain of the differential-to-single-ended amplifier 1425 is adjustable. The amplified signal passes through an active second order low pass filter 1426 for eliminating the high frequency signal of the transition band on the right side of the amplified high frequency signal.
Referring to fig. 6, which is a specific embodiment of the sensing unit shown in fig. 5, the first passive low-pass filter 1421 includes a resistor R1, a capacitor C1, and a resistor R2, the resistor R1 and the capacitor C1 are connected to form a low-pass filter, and the level Vref is a signal boosting voltage through the resistor R2. The second passive low pass filter 1422 has the same structure as the first passive low pass filter 1421.
The first passive high-pass filter 1423 includes a capacitor C3 and a resistor R5, one end of the capacitor C3 is connected to the output end of the first passive low-pass filter 1421, the other end of the capacitor C3 is connected to the resistor R5, and the level Vref raises the signal S1 through the resistor R5. The capacitor C3 performs high-pass filtering. The second passive high pass filter 1424 has the same structure and operation principle.
The level Vref is used to pull up the near-body surface electrical signal, so that the pulled-up near-body surface electrical signal is within the working voltage range of the differential-to-single-ended amplifier 1425. Said level Vref being provided by a reference voltage module (not shown in the figures)
The near body surface electric signal is filtered by the filter to generate a signal S1 and a signal S2, the signal S1 and the signal S2 are converted into a signal S3 by a differential-to-single-ended filter amplifier 1425, and the differential-to-single-ended filter amplifier 1425 comprises a first operational amplifier circuit L1 and a second operational amplifier circuit L2; the first operational amplifier circuit L1 amplifies the signal S2, and the input end of the second operational amplifier circuit L2 is connected with the output end of the first operational amplifier circuit L1 and the signal S1.
The first input end of the first operational amplifier circuit L1 is connected with the signal S2, the second input end is connected with the level Vref through a resistor R7, and is connected with the output end in parallel through a resistor R9, and is connected with the second input end of the second operational amplifier circuit L2 through a resistor R10, the output end of the first operational amplifier circuit L1 is connected with the second input end of the second operational amplifier circuit L2 through a resistor R10, the first input end of the second operational amplifier circuit L2 is connected with the signal S1, and the second input end of the second operational amplifier circuit L2 is connected with the output end through a resistor R11. The first operational amplifier circuit L1 and the second operational amplifier circuit L2 are proportional amplifier circuits, and constitute a differential-to-single-ended filter amplifier 1425.
In a preferred embodiment, the resistor R8 is a programmable resistor, the programmable resistance range of R8 is 10K Ω -100K Ω, the resistance ranges of R7, R9, R10, and R11 are 100K Ω -1M Ω, and the processor 141 adjusts the output gain of the differential-to-single-ended amplifier 1425 by programming the resistance of the resistor R8, so that the program control range of the output gain is 50-500 times.
In a preferred embodiment, the implantable heart monitor 1 transmits the signal S4 to the external device 2 through the wireless communication unit 145, and the external device 2 receives the signal S4 and displays the signal on the screen through the display. The external device 2 provides a gain adjustment interface that provides gain value options or adjustment buttons. The external device 2 automatically adjusts the gain value according to the electrocardiosignal amplitude, or adjusts the gain by a doctor. The adjusted gain is fed back to the system interface in real time, the external device 2 sends a gain value to the implantable heart monitor 1 through the wireless communication module, and the processor 141 of the implantable heart monitor 1 writes the received gain value into the resistor R8, so as to achieve the purpose of adjusting the gain of the sensing unit 142.
The differential-to-single-ended filter amplifier 1425 outputs the signal S3 to the input of the first active second-order low-pass filter amplifier 1426. The first active second-order low-pass filter amplifier 1426 includes an operational amplifier L3, and resistors R12R 13R 14R 15, capacitors C5 and C6, and the level Vref is connected to the input terminal of the operational amplifier L3 through the resistor R14. The first active second-order low-pass filter amplifier 1426 outputs the signal S4.
As shown in fig. 7, different from fig. 6, the sensing unit 142 further includes a protection module 1427, where the protection module 1427 includes TVS transistors T1 and T2 connected in parallel in reverse direction, and the TVS transistors are connected between two input terminals of the sensing unit 142 in parallel, and the protection module 1427 prevents the high voltage signal from damaging other devices of the sensing unit 142.
As shown in fig. 8, the sensing unit 142 further includes a third passive high-pass filter 1428, where the third passive high-pass filter 1428 includes a resistor R16 and a capacitor C7, and a resistor R17, where one end of the resistor R17 is connected to the capacitor C7, and the second end is connected to the level Vref.
And a second active second order low pass filter amplifier 1429 input. The second active second-order low-pass filter amplifier 1429 has the same structure as the first active second-order low-pass filter amplifier 1426. The third passive high-pass filter 1428 further filters the low-frequency signal of the low-frequency signal left transition band from the signal S4, and the second active second-order low-pass filter amplifier 1429 further removes the high-frequency signal of the high-frequency signal right transition band from the signal S4.
In the embodiment shown in fig. 9, the signal S4 is further divided into a signal S7 and a signal S8, and the signal S7 is used for monitoring the ecg signal, which has a high frequency enough to reflect the real-time ecg status of the patient. Optionally, the implantable heart monitor comprises an atrial fibrillation/ventricular fibrillation monitoring module for monitoring atrial fibrillation or ventricular fibrillation signals, the signal S7 is connected with the atrial fibrillation/ventricular fibrillation monitoring module of the implantable heart monitor, and the signal S7 only contains high-frequency signals so as to prevent the atrial fibrillation or ventricular fibrillation monitoring from being subjected to undersensing and causing false monitoring.
Further, the signal S4 passes through a fourth passive high-pass filter 14210, the fourth passive high-pass filter 14210 eliminates the high-frequency signal unrelated to the R wave, and the output signal S8 is used for the implantable heart monitor 1 to sense the R wave signal, optionally, the implantable heart monitor includes a bradycardia monitoring module for monitoring bradycardia, and the signal S8 is connected to the implantable heart monitor bradycardia monitoring module. The signal S7 and the signal S8 share the same sensing unit, and the power consumption is lower compared with that of an independent dual channel.
Further, the module for monitoring atrial fibrillation/ventricular fibrillation or bradycardia is a computer instruction executable by the processor or a circuit with corresponding functions.
Referring to fig. 10, the amplitude-frequency characteristic of the sensing unit 142 is shown. The bandpass filter of the sensing unit 142 can well complete the filtering from the aspect of amplitude-frequency characteristics. The sensing unit 142 has a good suppression effect on out-of-band frequency components. The figure shows a good suppression effect on low-frequency signals (about 0-10 HZ) of a transition band on the left side outside the bandwidth B range, and simultaneously has a good suppression effect on high-frequency signals of a transition band on the right side outside the bandwidth B range.
Claims (7)
1. A sensing unit is characterized by comprising a first passive low-pass filter, a second passive low-pass filter, a first passive high-pass filter, a second passive high-pass filter, a differential-to-single-ended filter amplifier and a first active second-order low-pass filter amplifier; the first passive low-pass filter receives a first signal input, and the output end of the first passive low-pass filter is connected with the first passive high-pass filter; the second passive low-pass filter receives a second signal input, and the output end of the second passive low-pass filter is connected with the second passive high-pass filter; the output ends of the first passive high-pass filter and the second passive high-pass filter are connected with the input end of a differential-to-single-ended filter amplifier, the output end of the differential-to-single-ended filter amplifier is connected with a first active second-order low-pass filter amplifier, the differential-to-single-ended filter amplifier comprises two proportional operational amplifiers, the second input ends of the two proportional operational amplifiers are connected through a first resistor, and the first resistor is a programmable resistor; the third passive high-pass filter is connected with the output end of the first active second-order low-pass filter amplifier; the second active second-order low-pass filter amplifier is connected with the output end of the third passive high-pass filter; the electrocardiosignal monitoring device is characterized by further comprising a fourth passive high-pass filter, wherein the input end of the fourth passive high-pass filter is connected with the output end of the second active second-order low-pass filter amplifier, the second active second-order low-pass filter amplifier outputs a first output signal for monitoring electrocardiosignals, and the fourth passive high-pass filter outputs a second output signal for monitoring R waves.
2. The sensing unit of claim 1, further comprising a protection module connected in parallel between the input terminals of the first signal and the second signal.
3. The sensing unit of claim 2, wherein the protection module comprises an anti-parallel zener diode.
4. An implantable heart monitor, comprising,
the outer shell is provided with a plurality of grooves,
at least one sensing electrode disposed on the housing for receiving cardiac electrical signals,
a circuit assembly disposed within the housing, the circuit assembly comprising,
the sensing unit receives the output of the sensing electrode and comprises a first passive low-pass filter, a second passive low-pass filter, a first passive high-pass filter, a second passive high-pass filter, a differential-to-single-ended filter amplifier and a first active second-order low-pass filter amplifier; the first passive low-pass filter receives a first signal input, and the output end of the first passive low-pass filter is connected with the first passive high-pass filter; the second passive low-pass filter receives a second signal input, and the output end of the second passive low-pass filter is connected with the second passive high-pass filter; the output ends of the first passive high-pass filter and the second passive high-pass filter are connected with the input end of a differential-to-single-ended filter amplifier, the output end of the differential-to-single-ended filter amplifier is connected with a first active second-order low-pass filter amplifier, the differential-to-single-ended filter amplifier comprises two proportional operational amplifiers, the second input ends of the two proportional operational amplifiers are connected through a first resistor, and the first resistor is a programmable resistor; the third passive high-pass filter is connected with the output end of the first active second-order low-pass filter amplifier; the second active second-order low-pass filter amplifier is connected with the output end of the third passive high-pass filter; the input end of the fourth passive high-pass filter is connected with the output end of the second active second-order low-pass filter amplifier, the second active second-order low-pass filter amplifier outputs a first output signal for monitoring electrocardiosignals, and the fourth passive high-pass filter outputs a second output signal for monitoring R waves;
an analog-to-digital conversion unit for converting the analog signal output by the sensing unit into a digital signal,
the processor receives and processes the output signal of the analog-to-digital conversion unit, and stores data in the storage unit;
the implantable heart monitor sends the first output signal to an external device, the external device receives the first output signal and then displays the first output signal on a screen through a display, the external device provides a gain adjustment interface, the gain adjustment interface provides gain value options or adjustment buttons, the external device automatically adjusts the gain value according to the amplitude of the electrocardiosignal or adjusts the gain value through a doctor, the adjusted gain value is fed back on a system interface in real time, the external device sends the gain value to the implantable heart monitor, and a processor of the implantable heart monitor writes the received gain value into the first resistor.
5. The implantable heart monitor of claim 4, further comprising a wireless communication unit that establishes a communication link between the processor and an external device.
6. The implantable heart monitor of claim 5, wherein the external device sends a gain parameter to the processor via the wireless communication unit, and the processor adjusts the resistance of the first resistor according to the gain parameter.
7. The implantable heart monitor of claim 4, further comprising an atrial fibrillation/ventricular fibrillation monitoring module and an bradycardia monitoring module; and the output signal of the fourth passive high-pass filter is connected with the atrial fibrillation/ventricular fibrillation monitoring module, and the output signal of the second active second-order low-pass filter amplifier is connected with the bradycardia monitoring module.
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111130632.6A CN113812960B (en) | 2021-09-26 | 2021-09-26 | Sensing unit and implantable heart monitor |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111130632.6A CN113812960B (en) | 2021-09-26 | 2021-09-26 | Sensing unit and implantable heart monitor |
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| Publication Number | Publication Date |
|---|---|
| CN113812960A CN113812960A (en) | 2021-12-21 |
| CN113812960B true CN113812960B (en) | 2022-11-29 |
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Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102512152A (en) * | 2011-10-21 | 2012-06-27 | 南京大学 | Long-distance electrocardio monitoring system |
| CN104622460A (en) * | 2014-12-31 | 2015-05-20 | 北京瀚景锦河科技有限公司 | ECG signal collecting device |
| WO2016044477A1 (en) * | 2014-09-16 | 2016-03-24 | Bardy Diagnostics, Inc. | Ambulatory electrocardiography monitor recorder |
| CN112022146A (en) * | 2020-09-30 | 2020-12-04 | 苏州无双医疗设备有限公司 | Implantable medical device and external defibrillation device combined system |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| US8366628B2 (en) * | 2007-06-07 | 2013-02-05 | Kenergy, Inc. | Signal sensing in an implanted apparatus with an internal reference |
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Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102512152A (en) * | 2011-10-21 | 2012-06-27 | 南京大学 | Long-distance electrocardio monitoring system |
| WO2016044477A1 (en) * | 2014-09-16 | 2016-03-24 | Bardy Diagnostics, Inc. | Ambulatory electrocardiography monitor recorder |
| CN104622460A (en) * | 2014-12-31 | 2015-05-20 | 北京瀚景锦河科技有限公司 | ECG signal collecting device |
| CN112022146A (en) * | 2020-09-30 | 2020-12-04 | 苏州无双医疗设备有限公司 | Implantable medical device and external defibrillation device combined system |
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