Breathing induction signal generation system and breathing induction plethysmography device

Abstract

The utility model discloses a respiration induction signal generating system and a respiration induction plethysmography device, which belong to the technical field of medical monitoring, and the system comprises a lead coil which is attached to the chest and abdomen of a living body in a surrounding manner and comprises a first interface and a second interface; the input end of the inverting unit is connected with the second interface, and the output end is connected with the first interface; the input end of the counting unit is connected with the output end of the inverting unit; the input end of the filtering and amplifying unit is connected with the output end of the counting unit; when the first interface and the second interface of the wire coil are connected, the wire coil generates an oscillation signal according to inductance periodic change caused by thoracic and abdominal movement, the anti-phase unit generates a high-frequency excitation pulse according to the oscillation signal, and the counting unit counts and encodes the high-frequency excitation pulse to generate a frequency signal. And the filtering and amplifying unit filters and amplifies the frequency signal to obtain a breathing sensing signal. The ultra-low power consumption breathing induction plethysmography system realizes ultra-low power consumption breathing induction plethysmography.

Description

Technical Field

[0001] This utility model relates to the field of medical monitoring technology, and in particular to a respiratory sensing signal generation system and a respiratory sensing volume plethysmography device. Background Technology

[0002] Respiratory plethysmography, a non-invasive respiratory detection technique, is widely used in the detection of chest and abdominal respiratory waveforms. Its detection principle involves stitching a coil bent into a wavy or sinusoidal shape into an elastic element, using the wire as the inductor in a capacitive three-point resonant circuit. When the human body breathes, the periodic fluctuations in the chest and abdomen cause periodic changes in the inductance of the wire. These changes in inductance cause changes in the resonant point. Frequency discrimination or detection is used to detect these changes in the coil's self-inductance, thus enabling the conversion of chest and abdominal respiratory waves. Alternatively, the wire can be used as a purely inductive load, with high-frequency excitation applied to its ends to detect waveform changes at both points.

[0003] In existing technologies, high-frequency excitation current needs to be applied to both ends of the conductor. Previous high-frequency excitation sources required a separate dedicated excitation source circuit, which had a complex circuit structure, high power consumption, and consequently increased manufacturing costs and the overall processing circuit module size.

[0004] Therefore, there is an urgent need for a respiratory sensing signal generation system and a respiratory sensing volume plethysmography device to solve the technical problems of complex circuit structure and high power consumption in the existing technology. Utility Model Content

[0005] In view of this, it is necessary to provide a respiratory sensing signal generation system and a respiratory sensing volume plethysmography device to solve the technical problems of complex circuit structure and high power consumption in the prior art.

[0006] To achieve the above objectives, on the one hand, this utility model provides a respiratory sensing signal generation system, comprising:

[0007] A coil, which is attached to the thorax and abdomen of an organism, includes a first interface and a second interface.

[0008] The inverting unit has its input connected to the second interface and its output connected to the first interface.

[0009] The input terminal of the counting unit is connected to the output terminal of the inverting unit;

[0010] The input terminal of the filter amplification unit is connected to the output terminal of the counting unit;

[0011] When the first interface of the conductor coil is connected to the second interface, the conductor coil generates an oscillation signal based on the periodic change in inductance caused by chest and abdominal movement. The inverting unit generates a high-frequency excitation pulse based on the oscillation signal. The counting unit counts and encodes the high-frequency excitation pulse to generate a frequency signal. The filtering and amplification unit filters and amplifies the frequency signal to obtain a breathing sensing signal.

[0012] In one possible implementation, the inverting unit includes a six-way inverter, a MOSFET, a first resistor, and a first capacitor;

[0013] One end of the first resistor and one end of the first capacitor are both connected to the input pin of the six-way inverter. The other end of the first capacitor is grounded, and the other end of the first resistor is connected to the ground pin of the six-way inverter and then grounded.

[0014] The ground pin of the six-channel inverter is connected to the drain of the MOSFET, the source of the MOSFET is grounded, and the gate of the MOSFET is connected to the input of the filter amplifier unit.

[0015] When the first interface of the conductor coil is connected to the second interface, the conductor coil, the first resistor and the first capacitor form an LRC resonant unit, which inputs the oscillation signal to the input pin of the six-channel inverter.

[0016] One possible implementation also includes a multivibrator unit;

[0017] The multivibrator unit includes a multivibrator, a second resistor, and a second capacitor;

[0018] The input pin of the multivibrator is connected to the output of the counting unit. One end of the second resistor and the second capacitor are both connected to the timing pin of the multivibrator. The other end of the second resistor is connected to the external power supply, and the other end of the second capacitor is grounded. The inverting output pin of the multivibrator is connected to the gate of the MOSFET and then to the input of the filter amplifier unit. The non-inverting output pin of the multivibrator is connected to the binary counter.

[0019] In one possible implementation, the counting unit includes a binary counter;

[0020] The counting pins of the binary counter are connected to the first interface of the coil and the output pins of the six-way inverter. The reset input pin of the binary counter is connected to the positive output pin of the multivibrator, and the output pin of the binary counter is connected to the input pin of the multivibrator.

[0021] In one possible implementation, the filter amplification unit includes a first low-pass filter amplification subunit, a first DC blocking capacitor, and a second low-pass filter subunit.

[0022] The first low-pass filter amplifier subunit, the first DC blocking capacitor, and the second low-pass filter subunit are connected in series in sequence.

[0023] The input of the first low-pass filter amplifier subunit is connected to the output pin of the multivibrator, and the second low-pass filter subunit outputs a breathing induction signal.

[0024] In one possible implementation, the first low-pass filter amplifier subunit includes a third resistor, a fourth resistor, a fifth resistor, a sixth resistor, a first diode, a third capacitor, a fourth capacitor, and a first amplifier;

[0025] The first diode is connected in series with the third resistor and then in parallel with the fourth resistor. One end of the diode is connected to the output pin of the multivibrator, and the other end is connected to the positive input pin of the first amplifier. The negative input pin of the first amplifier is grounded through the sixth resistor.

[0026] The third resistor is grounded through the third capacitor;

[0027] The fifth resistor and the fourth capacitor are connected in parallel. One end of the connection is connected to the negative input pin of the first amplifier, and the other end is connected to the positive output pin of the first amplifier. The negative output pin of the first amplifier is grounded.

[0028] In one possible implementation, the second low-pass filter subunit includes a ninth resistor, a sixth capacitor, and a second amplifier;

[0029] One end of the ninth resistor is connected to the first DC blocking capacitor, and the other end is connected to the positive input pin of the second amplifier;

[0030] One end of the sixth capacitor is connected to the ninth resistor and the positive input pin of the second amplifier, while the other end is grounded.

[0031] The negative input pin of the second amplifier is connected to the negative output pin of the second amplifier, and the positive output pin of the second amplifier is connected to an external power supply.

[0032] In one possible implementation, the second low-pass filter subunit also includes a seventh resistor and an eighth resistor;

[0033] One end of the seventh resistor and the eighth resistor are both connected to the input terminals of the first DC blocking capacitor and the second low-pass filter subunit. The other end of the seventh resistor is connected to an external power supply, and the other end of the eighth resistor is grounded.

[0034] In one possible implementation, a second DC blocking unit is also included;

[0035] The second DC blocking unit includes the tenth resistor, the eleventh resistor, the twelfth resistor, the seventh capacitor, and the eighth capacitor;

[0036] The seventh capacitor, the eleventh resistor, and the eighth capacitor are connected in series in sequence and then connected in parallel with the twelfth resistor.

[0037] One end of the tenth resistor is connected to the negative output pin of the second amplifier, and the other end is connected to one end of the seventh capacitor and the twelfth resistor.

[0038] The seventh capacitor and the eleventh resistor are grounded;

[0039] The eighth capacitor outputs a breathing sensing signal across its two ends.

[0040] Secondly, this utility model also provides a respiratory sensing volume recording device, including: a respiratory sensing signal generation system as described above, and further including an elastic element, a connecting element and a volume recording unit;

[0041] The conductor coil is fixedly mounted on the elastic element in a sinusoidal shape, with the first and second interfaces of the conductor coil located at the two ends of the elastic element, respectively.

[0042] The two ends of the connector are respectively connected to the first and second interfaces of the conductor coil;

[0043] The volume recording unit is connected to the output of the filter amplification unit.

[0044] The beneficial effects of this utility model are as follows: the first and second interfaces of the conductor coil are used as switches for high-frequency excitation. When the first interface of the conductor coil is connected to the second interface of the conductor coil, the conductor coil generates an oscillation signal based on the periodic change in inductance caused by chest and abdominal movement. The inverting unit generates a high-frequency excitation pulse based on the oscillation signal. The counting unit counts and encodes the high-frequency excitation pulse to generate a frequency signal. The filtering and amplification unit filters and amplifies the frequency signal to obtain an oscillation signal for monitoring. In this embodiment, by using the conductor coil as a start switch for the excitation source, when the conductor coil is connected, it provides a high-frequency excitation pulse for the respiratory sensing signal generation system under the action of various logic devices. Since the logic devices have low power consumption characteristics, the entire circuit achieves a simple structure and low power consumption for respiratory sensing volume recording. Attached Figure Description

[0045] To more clearly illustrate the technical solutions in the embodiments of this utility model, the drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this utility model. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0046] Figure 1 A schematic diagram of an embodiment of the respiratory sensing signal generation system provided by this utility model

[0047] Figure 2 A waveform diagram of the process of converting the oscillation signal in one embodiment of the present invention;

[0048] Figure 3 A schematic diagram of an embodiment of the respiratory sensing volume plethysmography device provided by this utility model is shown. Detailed Implementation

[0049] The technical solutions of the present utility model will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present utility model, and not all embodiments. All other embodiments obtained by those skilled in the art based on the embodiments of the present utility model without creative effort are within the scope of protection of the present utility model.

[0050] The terms "first," "second," etc., used in the embodiments of this utility model are for descriptive purposes only and should not be construed as indicating or implying their relative importance or implicitly specifying the number of technical features indicated. Therefore, a technical feature defined with "first" or "second" may explicitly or implicitly include at least one of that feature.

[0051] In this document, the term "embodiment" means that a particular feature, structure, or characteristic described in connection with an embodiment may be included in at least one embodiment of the present invention. The appearance of this phrase in various places throughout the specification does not necessarily refer to the same embodiment, nor is it a mutually exclusive, independent, or alternative embodiment. It will be explicitly and implicitly understood by those skilled in the art that the embodiments described herein can be combined with other embodiments.

[0052] This invention provides a respiratory sensing signal generation system and a respiratory sensing volume recording device, which will be described below.

[0053] In some embodiments of this utility model, such as Figure 1 As shown, Figure 1 A schematic diagram of an embodiment of the respiratory sensing signal generation system provided by this utility model includes:

[0054] A coil (not shown in the figure) is attached to the thorax and abdomen of the organism, and includes a first interface P1 and a second interface P2.

[0055] The inverting unit 10 has its input terminal connected to the second interface P2 and its output terminal connected to the first interface P1.

[0056] The input terminal of the counting unit 20 is connected to the output terminal of the inverting unit 10;

[0057] The input terminal of the filter amplification unit 30 is connected to the output terminal of the counting unit 20;

[0058] When the first interface P1 of the conductor coil is connected to the second interface P2, the conductor coil generates an oscillation signal based on the periodic change in inductance caused by chest and abdominal movement. The inverting unit 10 generates a high-frequency excitation pulse based on the oscillation signal of the conductor coil. The counting unit 20 counts and encodes the high-frequency excitation pulse to generate a frequency signal. The filtering and amplification unit 30 filters and amplifies the frequency signal to obtain a breathing sensing signal.

[0059] It should be noted that the organism is a respiring organism. In this embodiment, the organism is a human body for respiratory sensing monitoring. The coil also includes a grounded interface P0, which is grounded through capacitor C9. The first interface P1 of the coil is grounded through capacitor C10. The coil is used as a variable inductor element. The first and second interfaces of the coil are used as start switches. When the first and second interfaces of the coil are closed, a closed loop is formed. The coil of this closed loop is wrapped around and in close contact with the chest and abdomen of the human body. When the human body breathes, the chest and abdomen will make periodic movements due to breathing, which will cause the coil to also undergo periodic expansion and contraction. The coil, resistor and capacitor in the circuit form an LRC resonant circuit. The coil is stretched due to human breathing, which causes the inductance value of the coil to change, thus changing the frequency of its resonant sinusoidal oscillation waveform and the entire square wave counting time width. The inverting unit generates a high-frequency excitation pulse based on the oscillation signal generated by the frequency change of the resonant sinusoidal oscillation waveform. The counting unit further determines the frequency of the oscillation signal based on the square wave counting time width. Due to the low power consumption characteristics of the logic devices, the entire circuit achieves microamp-level power consumption. In this embodiment, when the first and second interfaces of the conductor coil are not connected, its power consumption is 3.5uA. When the first and second interfaces of the conductor coil are connected, the average power consumption is 15uA. It can work continuously for more than 2 years using a CR2450 button battery with a nominal capacity of 520mAh, which fully demonstrates the extremely low power consumption characteristics of the breathing sensing signal generation circuit system in this embodiment.

[0060] It should be further noted that a monitoring device capable of displaying respiratory sensing signals can be connected to the output of the filter amplification unit 30 to display the respiratory sensing signals and monitor the respiratory motion waveform.

[0061] In this embodiment, the first and second interfaces of the coil are used as switches for high-frequency excitation. When the first interface P1 of the coil is connected to the second interface P2, the coil generates an oscillation signal based on the periodic change in inductance caused by chest and abdominal movement. The inverting unit 10 generates a high-frequency excitation pulse based on the oscillation signal. The counting unit counts and encodes the high-frequency excitation pulse to generate a frequency signal. The filtering and amplification unit 30 filters and amplifies the frequency signal to obtain an oscillation signal for monitoring. The oscillation signal is generated based on the periodic change in the inductance value of the coil caused by chest and abdominal movement during human respiration. In this embodiment, the coil is used as a start switch for the excitation source. When the coil is connected, it provides a high-frequency excitation pulse to the respiratory sensing signal generation system under the action of various logic devices. Since the logic devices have low power consumption characteristics, the entire circuit achieves a simple structure and low power consumption for respiratory sensing volume recording.

[0062] In some embodiments of this utility model, the inverting unit includes a six-way inverter 11, a MOSFET Q1, a first resistor R1, and a first capacitor C1;

[0063] One end of the first resistor R1 and the first capacitor C1 are both connected to the input pin A3 of the six-way inverter 11, the other end of the first capacitor C1 is grounded, and the other end of the first resistor R1 is connected to the ground pin GND of the six-way inverter and then grounded.

[0064] The ground pin GND of the six-way inverter is connected to the drain of MOSFET Q1, the source of MOSFET Q1 is grounded, and the gate of MOSFET Q1 is connected to the input terminal of the filter amplifier unit 30.

[0065] When the first interface P1 of the conductor coil is connected to the second interface P2 of the conductor coil, the conductor coil, the first resistor R1 and the first capacitor C1 form an LRC resonant unit, which inputs the oscillation signal to the input pin A3 of the six-channel inverter 11.

[0066] Specifically, when the first interface P1 of the conductor coil is connected to the second interface P2 of the conductor coil, the conductor coil, the first resistor R1, and the first capacitor C1 form an LRC resonant unit, which inputs an oscillation signal to the input pin A3 of the six-way inverter 11. When the gate of MOSFET Q1 is high, MOSFET Q1 is turned on, and the ground pin of the six-way inverter 11 is grounded. At this time, the voltage of the input pin A3 is inverted, and the output pin Y3 outputs a square wave shaped by a sine oscillation. When the gate of MOSFET Q1 is low, MOSFET Q1 is turned off, the ground pin of the six-way inverter 11 cannot be grounded, and the six-way inverter 11 does not work.

[0067] This embodiment combines the conductor coil as an inductor, resistor, and capacitor in a resonant circuit to provide a resonant oscillation signal for the six inverters, and controls the operation of the six inverters through a MOSFET.

[0068] In some embodiments of this utility model, a multivibrator unit 40 is also included;

[0069] The multivibrator unit 40 includes a multivibrator 41, a second resistor R2, and a second capacitor C2.

[0070] The input pin 1B of the multivibrator 41 is connected to the output of the counting unit. One end of the second resistor R2 and the second capacitor C2 are both connected to the timing pin 1REXT of the multivibrator 41. The other end of the second resistor R2 is connected to the external power supply, and the other end of the second capacitor C2 is grounded. The inverting output pin 1Q# of the multivibrator is connected to the gate of the MOS transistor and then to the input of the filter amplifier unit. The non-inverting output pin 1Q of the multivibrator is connected to the binary counter.

[0071] It should be noted that the second resistor R2 and the second capacitor C2 are connected to the timing pin 1REXT of the multivibrator 41, together forming the timing circuit of the oscillator. The other end of the second resistor R2 is connected to the operating power supply to provide the required DC voltage for the multivibrator 41. The other end of the second capacitor C2 is grounded, and together with the second resistor R2, they determine the oscillation frequency and duty cycle of the oscillator.

[0072] This embodiment uses a multivibrator to adjust the oscillating square wave and output a stable and reliable frequency signal.

[0073] In some embodiments of this utility model, the counting unit 20 includes a binary counter 21;

[0074] The counting pins CP of the binary counter 21 are connected to the first interface P1 of the conductor coil and the output pin of the six-way inverter 11. The reset input pin MP of the binary counter 21 is connected to the positive output pin 1Q of the multivibrator. The output pin Q8 of the binary counter 21 is connected to the input pin 1B of the multivibrator 41.

[0075] Specifically, when the first interface P1 of the conductor coil is connected to the second interface P2 of the conductor coil, the conductor coil, the first resistor R1, and the first capacitor C1 form an LRC resonant unit, which inputs an oscillation signal to the input pin A3 of the six-way inverter 11. The output pin Y3 of the six-way inverter 11 outputs a sinusoidal oscillation waveform. When the gate of the MOSFET Q1 is at a high level, the MOSFET Q1 is turned on, the ground pin GND of the six-way inverter 11 is grounded, and the six-way inverter 11 works normally, inverting the input voltage of the input pin A3, so that the output pin Y3 outputs a sinusoidal oscillation shaped square wave. The technical pin CP of the binary counter 21 receives the square wave from the output pin Y3 of the six-way inverter 11 and counts it. Since the output pin Q8 of the binary counter 21 is connected to the input pin 1B of the multivibrator 41, the binary counter 21... After counting 256 times, counter 21 outputs a high level to multivibrator 41. Input pin 1B of multivibrator 41 receives the high level from output pin Q8 of binary counter and outputs a high level through positive output pin 1Q and a low level through negative output pin. The high level output by positive output pin 1Q is sent to the reset input pin MP of binary counter, resetting binary counter and stopping counting. It waits for the next high level to start counting again. The low level output by negative output pin 1Q# is sent to the gate of MOSFET Q1. When the gate of MOSFET Q1 is low, MOSFET Q1 is turned off, and six-way inverter 11 stops working until the end of one cycle. In the next cycle, positive output pin 1Q outputs a low level, and negative output pin 1Q# outputs a high level, and the above process is repeated.

[0076] Furthermore, such as Figure 2 As shown, Figure 2 The waveform diagrams provided in one embodiment of this utility model illustrate the process of converting the oscillation signal. The first waveform diagram is a periodic change diagram of the sinusoidal oscillation signal generated by the breathing motion of the coil. The second waveform diagram is the input waveform of the input pin A3, i.e., the T2 sinusoidal oscillation signal. The third waveform diagram is the T2 square wave after the sinusoidal oscillation output by the six-channel inverter 11 is shaped. The fourth waveform diagram is the sinusoidal square wave output by the binary counter. The fifth waveform diagram is the positive waveform output by the positive output pin of the multivibrator. The sixth waveform diagram is the waveform received by the gate of the MOS transistor Q1 during the oscillation period.

[0077] In this embodiment, a binary counter is used to count and encode the high-frequency excitation pulse signal output by the six-channel inverter 11 to generate a frequency signal.

[0078] In some embodiments of this utility model, the filtering and amplification unit 30 includes a first low-pass filtering and amplification subunit 31, a first DC blocking capacitor C5, and a second low-pass filtering subunit 32.

[0079] The first low-pass filter amplifier subunit 31, the first DC blocking capacitor C5, and the second low-pass filter subunit 32 are connected in series in sequence.

[0080] The input terminal of the first low-pass filter amplifier subunit 31 is connected to the output pin 1Q# of the multivibrator 41, and the second low-pass filter subunit 32 outputs the breathing sensing signal.

[0081] Specifically, when the frequency square wave signal output by the multivibrator 41 passes through the first low-pass filter amplification subunit 31, only low-frequency signals are allowed to pass through for the first filtering and amplification. Through the DC blocking capacitor C5, only AC signals are allowed to pass through, thus isolating the DC component. The second low-pass filter subunit 32 further performs low-pass filtering and amplification on the AC signal output by the first low-pass filter amplification subunit 31.

[0082] This embodiment uses two low-pass filter subunits and a DC blocking capacitor to perform multi-layer filtering and amplification on the output frequency signal of the multivibrator 41, and isolates its DC component, thereby improving the stability of the circuit and ensuring the integrity of the signal.

[0083] In some embodiments of this utility model, the first low-pass filter amplification subunit 31 includes a third resistor R3, a fourth resistor R4, a fifth resistor R5, a sixth resistor R6, a first diode D1, a third capacitor C3, a fourth capacitor C4, and a first amplifier A.

[0084] After the first diode D1 is connected in series with the third resistor R3, it is connected in parallel with the fourth resistor R4. One end of the diode is connected to the output pin 1Q# of the multivibrator 41, and the other end is connected to the positive input pin of the first amplifier A. The negative input pin of the first amplifier A is grounded through the sixth resistor R6.

[0085] The third resistor R3 is grounded through the third capacitor C3;

[0086] The fifth resistor R5 and the fourth capacitor C4 are connected in parallel. One end of the connection is connected to the negative input pin of the first amplifier A, and the other end is connected to the positive output pin of the first amplifier A. The negative output pin of the first amplifier A is grounded.

[0087] Specifically, the first diode D1 and the third resistor R3, connected in series, prevent the circuit from being damaged by reverse voltage or excessive forward voltage, and limit the diode current to prevent excessive current from impacting the circuit; the fourth resistor R4 is used to change the overall impedance of the circuit. The value of the fourth resistor R4 is set according to specific parameters to control the transmission and attenuation of the signal; the first amplifier A, the fifth resistor R5, the sixth resistor R6 and the fourth capacitor C4, together with the first amplifier A, filter and amplify the output signal of the multivibrator 41, and form a filter feedback network for phase compensation, thereby improving the filtering function of the amplifier and improving the stability and frequency response of the amplifier.

[0088] In this embodiment, multiple resistors and capacitors are combined with a first amplifier to perform signal preprocessing, signal filtering, and amplification on the output signal of the multivibrator 41.

[0089] In some embodiments of this utility model, the second low-pass filter subunit 32 includes a ninth resistor R9, a sixth capacitor C6, and a second amplifier B;

[0090] One end of the ninth resistor R9 is connected to the first DC blocking capacitor C5, and the other end is connected to the positive input pin of the second amplifier B.

[0091] One end of the sixth capacitor C6 is connected to the ninth resistor R9 and the positive input pin of the second amplifier B, and the other end is grounded;

[0092] The negative input pin of the second amplifier B is connected to the negative output pin of the second amplifier B, and the positive output pin of the second amplifier B is connected to an external power supply.

[0093] Specifically, the ninth resistor R9 is connected in series with the second amplifier B to limit the current in the circuit and protect the input terminal of the second amplifier B from damage by excessive current. At the same time, the ninth resistor R9 can also divide or attenuate the signal to adjust the signal amplitude input to the second amplifier B. The grounded sixth capacitor C6 is used to filter out high-frequency noise or interference in the input signal, improve the purity of the signal, and also to decouple it, preventing the output signal of the second amplifier B from being fed back to the input terminal through the power supply line. The negative input pin of the second amplifier B is connected to the negative output pin of the second amplifier B as a negative feedback connection to improve the stability of the amplifier and reduce distortion.

[0094] This embodiment provides a circuit for signal preprocessing, signal filtering and amplification, and signal negative feedback by combining multiple resistors and capacitors with a second amplifier B, and further filters the frequency square wave signal.

[0095] In some embodiments of this utility model, the second low-pass filter subunit 32 further includes a seventh resistor R7 and an eighth resistor R8;

[0096] One end of the seventh resistor R7 and the eighth resistor R8 are both connected to the first DC blocking capacitor C5 and the input terminal of the second low-pass filter subunit 32. The other end of the seventh resistor R7 is connected to an external power supply, and the other end of the eighth resistor R8 is grounded.

[0097] In this embodiment, the virtual ground voltage is provided for the second amplifier B through the seventh resistor R7 and the eighth resistor R8.

[0098] In some embodiments of this utility model, a second DC blocking unit 50 is also included;

[0099] The second DC blocking unit 50 includes a tenth resistor R10, an eleventh resistor R11, a twelfth resistor R12, a seventh capacitor C7, and an eighth capacitor C8.

[0100] The seventh capacitor C7, the eleventh resistor R11 and the eighth capacitor C8 are connected in series and then connected in parallel with the twelfth resistor R12.

[0101] One end of the tenth resistor R10 is connected to the negative output pin of the second amplifier B, and the other end is connected to one end of the seventh capacitor C7 and the twelfth resistor R12.

[0102] The seventh capacitor C7 and the eleventh resistor R11 are grounded;

[0103] The eighth capacitor C8 outputs a breathing sensing signal across its terminals.

[0104] It should be noted that the eighth capacitor C8 has two output ports, namely the positive output terminal P3 and the negative output terminal P4, which are connected to an external chest and abdominal motion monitoring device for displaying frequency square wave signals.

[0105] This embodiment uses a combination of resistors and capacitors to filter out unwanted signal components, thereby further improving the stability and accuracy of the circuit. At the same time, it forms a DC blocking output, so that the two ends of the eighth capacitor C8 output an AC chest and abdominal motion signal.

[0106] Based on the above-described respiratory sensing signal generation system, this embodiment of the invention also provides a respiratory sensing volume plethysmography device, such as... Figure 3 As shown, Figure 3 The present invention provides a schematic diagram of an embodiment of a respiratory sensing volume recording device, which includes the above-mentioned respiratory sensing signal generation system, and also includes an elastic member 1, a connecting member 2, and a volume recording unit (not shown in the figure).

[0107] The conductor coil 4 is fixedly mounted on the elastic element 1 in a sinusoidal shape, and the first interface P1 and the second interface P2 of the conductor coil 4 are respectively located at both ends of the elastic element 1.

[0108] The two ends of connector 2 are respectively connected to the first interface P1 and the second interface P2 of conductor coil 4;

[0109] The volume recording unit is connected to the output of the filter amplification unit.

[0110] It should be noted that the elastic element 1 can be an elastic band or a band made of various elastic materials. The connecting element 2 is the element that connects the elastic elements. It can be a buckle or any other connectable element. In this embodiment, the elastic element is an elastic band and the connecting element is a buckle. At the same time, the length of the elastic band is adjustable. According to the dimensions of the human chest and abdomen, the length of the elastic band can be adjusted by the length adjustment element 3 to ensure the comfort of the wearer. The volumetric recording unit is a device that can display the respiratory sensing signal. It can be a computer screen, mobile phone or other devices. The coil 4 is fixedly set on the elastic band in a sinusoidal shape. The first interface P1 and the second interface P2 of the coil 4 are respectively connected to the two ends of the buckle. When the buckle is engaged, the first interface P1 and the second interface P2 of the coil 4 are connected, the entire respiratory sensing signal generation system is closed, the circuit is connected, and the respiratory sensing volumetric recording device starts to work.

[0111] The respiratory sensing signal generation system provided by this utility model has been described in detail above. Specific examples have been used to illustrate the principle and implementation of this utility model. The description of the above embodiments is only for the purpose of helping to understand the method and core idea of ​​this utility model. At the same time, for those skilled in the art, there will be changes in the specific implementation and application scope based on the idea of ​​this utility model. Therefore, the content of this specification should not be construed as a limitation of this utility model.

Claims

1. A respiratory sensing signal generation system, characterized in that, include: A coil, which is attached to the thorax and abdomen of an organism, includes a first interface and a second interface. The inverting unit has its input connected to the second interface and its output connected to the first interface. The input terminal of the counting unit is connected to the output terminal of the inverting unit; The input terminal of the filter amplification unit is connected to the output terminal of the counting unit; When the first interface of the conductor coil is connected to the second interface, the conductor coil generates an oscillation signal based on the periodic change in inductance caused by chest and abdominal movement. The inverting unit generates a high-frequency excitation pulse based on the oscillation signal. The counting unit counts and encodes the high-frequency excitation pulse to generate a frequency signal. The filtering and amplification unit filters and amplifies the frequency signal to obtain a breathing sensing signal.

2. The respiratory sensing signal generation system according to claim 1, characterized in that, The inverting unit includes six inverters, MOSFETs, a first resistor, and a first capacitor; One end of the first resistor and one end of the first capacitor are both connected to the input pin of the six-way inverter. The other end of the first capacitor is grounded, and the other end of the first resistor is connected to the ground pin of the six-way inverter and then grounded. The ground pin of the six-channel inverter is connected to the drain of the MOSFET, the source of the MOSFET is grounded, and the gate of the MOSFET is connected to the input of the filter amplifier unit. When the first interface of the conductor coil is connected to the second interface, the conductor coil, the first resistor and the first capacitor form an LRC resonant unit, which inputs the oscillation signal to the input pin of the six-channel inverter.

3. The respiratory sensing signal generation system according to claim 2, characterized in that, It also includes a multivibrator unit; The multivibrator unit includes a multivibrator, a second resistor, and a second capacitor; The input pin of the multivibrator is connected to the output of the counting unit. One end of the second resistor and the second capacitor are both connected to the timing pin of the multivibrator. The other end of the second resistor is connected to the external power supply, and the other end of the second capacitor is grounded. The inverting output pin of the multivibrator is connected to the gate of the MOSFET and then to the input of the filter amplifier unit. The non-inverting output pin of the multivibrator is connected to the binary counter.

4. The respiratory sensing signal generation system according to claim 3, characterized in that, The counting unit includes a binary counter; The counting pins of the binary counter are connected to the first interface of the coil and the output pins of the six-way inverter. The reset input pin of the binary counter is connected to the positive output pin of the multivibrator, and the output pin of the binary counter is connected to the input pin of the multivibrator.

5. The respiratory sensing signal generation system according to claim 4, characterized in that, The filtering and amplification unit includes a first low-pass filtering and amplification subunit, a first DC blocking capacitor, and a second low-pass filtering subunit; The first low-pass filter amplifier subunit, the first DC blocking capacitor, and the second low-pass filter subunit are connected in series in sequence. The input of the first low-pass filter amplifier subunit is connected to the output pin of the multivibrator, and the second low-pass filter subunit outputs a breathing induction signal.

6. The respiratory sensing signal generation system according to claim 5, characterized in that, The first low-pass filter amplifier subunit includes a third resistor, a fourth resistor, a fifth resistor, a sixth resistor, a first diode, a third capacitor, a fourth capacitor, and a first amplifier; The first diode is connected in series with the third resistor and then in parallel with the fourth resistor. One end of the diode is connected to the output pin of the multivibrator, and the other end is connected to the positive input pin of the first amplifier. The negative input pin of the first amplifier is grounded through the sixth resistor. The third resistor is grounded through the third capacitor; The fifth resistor and the fourth capacitor are connected in parallel. One end of the connection is connected to the negative input pin of the first amplifier, and the other end is connected to the positive output pin of the first amplifier. The negative output pin of the first amplifier is grounded.

7. The respiratory sensing signal generation system according to claim 6, characterized in that, The second low-pass filter subunit includes a ninth resistor, a sixth capacitor, and a second amplifier; One end of the ninth resistor is connected to the first DC blocking capacitor, and the other end is connected to the positive input pin of the second amplifier; One end of the sixth capacitor is connected to the ninth resistor and the positive input pin of the second amplifier, while the other end is grounded. The negative input pin of the second amplifier is connected to the negative output pin of the second amplifier, and the positive output pin of the second amplifier is connected to an external power supply.

8. The respiratory sensing signal generation system according to claim 7, characterized in that, The second low-pass filter subunit also includes a seventh resistor and an eighth resistor; One end of the seventh resistor and the eighth resistor are both connected to the input terminals of the first DC blocking capacitor and the second low-pass filter subunit. The other end of the seventh resistor is connected to an external power supply, and the other end of the eighth resistor is grounded.

9. The respiratory sensing signal generation system according to claim 8, characterized in that, It also includes a second DC blocking unit; The second DC blocking unit includes the tenth resistor, the eleventh resistor, the twelfth resistor, the seventh capacitor, and the eighth capacitor; The seventh capacitor, the eleventh resistor, and the eighth capacitor are connected in series in sequence and then connected in parallel with the twelfth resistor. One end of the tenth resistor is connected to the negative output pin of the second amplifier, and the other end is connected to one end of the seventh capacitor and the twelfth resistor. The seventh capacitor and the eleventh resistor are grounded; The eighth capacitor outputs a breathing sensing signal across its two ends.

10. A respiratory-sensing volumetric recording device, characterized in that, include: The respiratory sensing signal generation system according to any one of claims 1-9 further includes an elastic element, a connector, and a volumetric recording unit; The conductor coil is fixedly mounted on the elastic element in a sinusoidal shape, with the first and second interfaces of the conductor coil located at the two ends of the elastic element, respectively. The two ends of the connector are respectively connected to the first and second interfaces of the conductor coil; The volume recording unit is connected to the output of the filter amplification unit.

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