CN114376559A - Respiration baseline tracking acceleration method - Google Patents

Respiration baseline tracking acceleration method Download PDF

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CN114376559A
CN114376559A CN202210052104.1A CN202210052104A CN114376559A CN 114376559 A CN114376559 A CN 114376559A CN 202210052104 A CN202210052104 A CN 202210052104A CN 114376559 A CN114376559 A CN 114376559A
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breathing
respiratory
reference line
respiration
baseline
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CN114376559B (en
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王聖竣
王建霖
潘能御
尤景良
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Gaochang Shengyi Holding Co ltd
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    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
    • A61B5/087—Measuring breath flow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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    • A—HUMAN NECESSITIES
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    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2230/00—Measuring parameters of the user
    • A61M2230/40—Respiratory characteristics

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Abstract

The invention provides a method for accelerating the tracking of a reference line of a user breathing signal for a breathing assistance system, which accelerates the tracking of the breathing reference line when the state that a user operates or wears a breathing mask changes. The tracking method includes tracking relatively high points of the respiratory signal during an inspiratory period, tracking relatively low points of the respiratory signal during an expiratory period, and calculating respiratory amplitude over a span. According to the invention, the respiratory amplitude is calculated as a basis, and after a reference value is obtained through calculation, the tracking speed of the respiratory reference line is optimized.

Description

Respiration baseline tracking acceleration method
Technical Field
The invention relates to a calculation method of a breathing reference line, in particular to a breathing reference line tracking acceleration method for a positive pressure respirator.
Background
Methods of treating sleep apnea include surgery, mouth occludators, positive pressure ventilators (CPAP), and the like, wherein the positive pressure ventilators may also be used to treat: chronic obstructive pulmonary disease, congestive heart failure, neuromuscular disorders, and the like. The positive pressure respirator can open the upper respiratory tract with air pressure to maintain the respiratory tract smooth, and can be used for treating snoring and apnea. The automatic type positive pressure respirator has an air flow Sensor (air flow Sensor) for sensing whether a user is currently exhaling or inhaling, so that the automatic type positive pressure respirator can automatically change the air pressure in accordance with the breathing state of the user.
In which, the breathing states of the user at each stage of a breathing cycle can be represented by breathing phases, so that the user has a plurality of breathing phases in a breathing cycle, and the ventilator apparatus should perform corresponding control and measurement items at different breathing phases, for example: various pressures and various flow rates of the gas flow output/input; however, the breathing phase is only a general term, and there is no fixed design or number of phases that the specification should have, which is generally determined by the design of the developer, and since the breathing state of the user can be at least distinguished into inspiration and expiration, the breathing phase is often designed to be a number greater than 2, for example: 4 phase, 6 phase …, etc.
The breathing reference line is an important reference basis for judging the breathing phase of the user by the positive pressure respirator. The determination of the breathing phase affects the time point of controlling the output/input of the airflow, and a premature determination increases the probability of erroneous determination, causing discomfort to the user of the respirator; a too slow determination may cause the user to inhale uncomfortably or exhale uncomfortably, and also cause discomfort to the user. Therefore, the signal stability and response speed of the breathing reference line are important issues for controlling the positive pressure respirator.
The method of generating the breathing baseline usually employs an algorithm such as a digital filter or an averaging method, wherein the digital filter includes: finite Impulse Response (FIR) or Infinite Impulse Response (IIR) can respond to the change of the breathing baseline faster, but the design is relatively complex, which not only has high requirement on the computation amount, but also may destroy the integrity of the signal. And the averaging method is, for example: exponential averaging (EMA) or Simple averaging (SMA), although relatively low, often results in a delay in the response of the breathing baseline due to an increase in the number of points or cycles used to calculate the Average. In the prior art US 7,337,778B 2, the long and short mean lines are used together with the threshold setting as the basis for accelerating the adjustment of the respiration baseline, wherein the determination time is set to 6 seconds (i.e. one respiration cycle).
No matter the filter or the averaging method, too high point number or cycle number may cause too slow response of the breathing reference line, which may result in the operation of the positive pressure respirator being unable to meet the requirement, but too low point number or cycle number may also cause the calculation result of the breathing reference line to be easily disturbed by noise, thereby affecting the accuracy of the breathing phase determination of the user. In addition, the breathing rate may vary with the depth of sleep, and other sleep events may cause instantaneous flow changes, so that the design of a fixed number of points or a fixed number of cycles is difficult to be applied. In view of the trend of the number of users of respirators rising continuously in recent years, there is a strong need to achieve "fast adjustment of the breathing reference line" so that the breathing phase of the user can be accurately determined.
Disclosure of Invention
In view of the above problems, the present invention discloses a method for accelerating the tracking of a breathing reference line, which is applied to a breathing assistance system to optimize the tracking speed of the breathing reference line, and the method comprises the following steps:
a method for tracking and accelerating a breathing reference line, which provides a computing module and receives a breathing flow signal, comprises the following steps:
step S1: the calculation module generates a respiration amplitude and a respiration datum line according to the respiration flow signal;
step S2: the calculation module generates a respiratory phase determination signal according to the respiratory flow signal and the respiratory reference line, and when the respiratory phase determination signal stays in a respiratory phase exceeding a time threshold, the process goes to step S3, and when the respiratory phase determination signal stays in a respiratory phase not exceeding the time threshold, the process goes back to step S1;
step S3: judging whether a modulation trigger condition is satisfied, if yes, jumping to step S4, and if not, jumping back to step S1;
step S4: the calculation module generates a respiration datum line reference value according to the product of the respiration amplitude and a proportional parameter and a relative low point in the respiration datum line;
step S5: the calculation module corrects the breathing reference line according to the breathing reference line reference value.
Preferably, the modulation trigger condition is satisfied by any one of the following trigger conditions:
amplitude modulation trigger conditions: the difference between two consecutive breath amplitudes in the breath reference line is greater than a breath amplitude threshold;
high-point modulation trigger conditions: the difference between two continuous relative high points in the breathing datum line is greater than a breathing high point threshold value;
low-point modulation trigger condition: the difference between two consecutive relatively low points in the breathing reference line is greater than a breathing low point threshold;
the reference line modulation triggering condition is as follows: the difference between two consecutive points in the breathing reference line is greater than a breathing reference line threshold; and is
Each of the respiration amplitude threshold, the respiration high point threshold, the respiration low point threshold, and the respiration baseline threshold is a product of the respiration amplitude and a scaling parameter.
Preferably, as mentioned above, the respiratory baseline tracking and accelerating method, wherein the respiratory flow signal may be a real-time measured flow signal, a filtered flow signal, or a patient respiratory signal obtained by processing a measurement signal.
Preferably, the method for tracking and accelerating a breathing reference line as described above, wherein the calculation method of the breathing reference line reference value is as follows:
the reference value Bref of the respiration datum linen＝PoleLn+FlowPPn-1×PrefThe baseline reference value parameter PrefBetween 1% and 99%, PoleLnFlowPP, the current relatively low point in this baseline of breathingn-1Is the amplitude of the previous breath in the breathing reference line, wherein the foot code n represents the current value and the foot code n-1 represents the previous value.
Preferably, the above method for tracking and accelerating a breathing reference line, wherein the formula for calculating the corrected breathing reference line value is as follows:
the corrected baseline value of breathing bnew ═ (Bref)n-Basen-1)×PBL+Basen-1The baseline modulation parameter PBLBetween 1% and 99%, Basen-1Is the previous value of the breathing reference line.
Drawings
FIG. 1 is a block diagram of a computing module of the method for accelerating the tracking of a breathing reference line according to the present invention.
Fig. 2A is a schematic diagram of an exponential smooth moving average line (long-period EMA) of 30 periods of a respiratory airflow signal of a user.
FIG. 2B is a schematic diagram of the average line of exponential smooth movement (abbreviated as short-period EMA) of 10 periods of the respiratory airflow signal of the user.
FIG. 2C is the exponential smooth moving average (long-period EMA) of 30 periods of the respiratory Flow signal Flow in FIG. 2A
Fig. 3A shows the system breathing Flow, the breathing baseline of the long-period EMA, and the breathing Flow signal Flow with respect to the time axis when the air leakage starts without using the breathing baseline tracking acceleration method of the present invention.
FIG. 3B is the breathing phase determined from FIG. 3A.
Fig. 4A shows the system breathing Flow, the breathing baseline of the long-period EMA, and the breathing Flow signal Flow with respect to the time axis when the breathing baseline tracking acceleration method of the present invention is not used and the air leakage is recovered to normal.
Fig. 4B is the breathing phase determined from fig. 4A.
Fig. 5A shows the system respiratory Flow, respiratory Flow signal Flow, respiratory baseline and baseline reference values when the method of the present invention is applied to a long-cycle EMA and there is an air leak.
Fig. 5B is the breathing phase determined from fig. 5A.
Fig. 6A shows the system respiratory Flow, respiratory Flow signal Flow and respiratory baseline of the long-period EMA recovered from air leakage by the method of the present invention.
Fig. 6B is the breathing phase determined from fig. 6A.
FIG. 7 is a flowchart of an algorithm for tracking and accelerating a breathing reference line according to the present invention.
FIG. 8 is a block diagram of a computing module according to another embodiment of the present invention.
Detailed Description
The technical means adopted by the invention to achieve the preset purpose are further described in the following accompanying drawings and the preferred embodiment of the invention.
Referring to fig. 1, fig. 1 is a calculation module 10 for executing the method of tracking and accelerating a breathing reference line according to the present invention, where the calculation module 10 includes a breathing signal unit 11, a high-low point determination unit 12 connected to the breathing signal unit 11, a breathing reference line unit 13 connected to the breathing signal unit 11, an amplitude determination unit 14 connected to the high-low point determination unit 12, a breathing reference line reference value unit 15 respectively connected to the high-low point determination unit 12 and the amplitude determination unit 14, a breathing reference line correction unit 16 respectively connected to the breathing reference line unit 13 and the breathing reference line reference value unit 15, and a phase detection unit 17 respectively connected to the breathing signal unit 11 and the breathing reference line correction unit 16. The computing module 10 is composed of a computer hardware such as a personal computer, a mobile device or a server, and an algorithm operating on the computer hardware.
The respiratory signal unit 11 mainly obtains a system respiratory Flow of the positive pressure respirator and obtains a respiratory Flow signal Flow close to the respiratory Flow of the user after system calibration, wherein the respiratory Flow signal Flow is a time function, and the respiratory Flow signal Flow can be a Flow signal measured in real time, a Flow signal after filtering, or a patient respiratory signal obtained after processing a measurement signal according to different system calibration modes.
The high/low determination unit 12 receives the respiratory Flow signal Flow and determines a relatively high PoleH and a relatively low PoleL in the respiratory Flow signal Flow, where the relatively high PoleH and the relatively low PoleL are Time series (Time series).
During the inspiration process, according to the turning of the respiratory Flow signal Flow, a relatively high point PoleH of the respiratory Flow signal Flow is obtained, wherein the relatively high point PoleH is obtained by a common method: monitoring the maximum value of the respiratory Flow signal Flow within a certain time or the slope of the respiratory Flow signal Flow changing from a positive value to a negative value.
In the exhalation process, the relatively low-point PoleL of the respiratory Flow signal Flow is obtained according to the transition of the respiratory Flow signal Flow, wherein the relatively low-point PoleL is obtained by the following general method: monitoring the minimum value of the respiratory Flow signal Flow within a certain time or the slope of the respiratory Flow signal Flow is changed from a negative value to a positive value.
The respiration baseline unit 13 also receives the respiration Flow signal Flow and generates a respiration baseline accordingly, and the algorithm for calculating the respiration baseline is usually a digital filter or an averaging method as mentioned above.
The amplitude determination unit 14 receives the relatively high point PoleH and the relatively low point PoleL and accordingly generates a respiration amplitude FlowPP, which is a function of time.
The breath baseline reference value unit 15 receives the breath amplitude FlowPP, the relatively high point PoleH and the relatively low point PoleL, and generates a breath baseline reference value as a function of time.
The breathing reference line correcting unit 16 receives the breathing reference line reference value and the breathing reference line, and generates a corrected breathing reference line accordingly. The phase detecting unit 17 receives the modified breathing baseline value and the breathing Flow signal Flow, and generates a breathing phase determination signal accordingly.
Referring to fig. 2A to 2C, fig. 2A is a respiratory Flow signal Flow relative to a time axis, fig. 2B is an exponential smooth moving average line (short period EMA) of 10 periods of the respiratory Flow signal Flow in fig. 2A, and fig. 2C is an exponential smooth moving average line (long period EMA) of 30 periods of the respiratory Flow signal Flow in fig. 2A. Comparing the exponential smooth moving average of fig. 2B and fig. 2C shows that: the variation of the 10 periods of the exponential smooth moving average line (EMA) is larger than that of the 30 periods of the exponential smooth moving average line (EMA), namely, compared with the longer periods of the exponential smooth moving average line, the shorter periods of the exponential smooth moving average line is more easily influenced by the respiratory Flow signal Flow; meanwhile, when the respiratory Flow signal Flow has a large variation, the exponential smooth moving average line of a long period does not immediately reflect the variation of the respiratory Flow signal Flow, but is delayed. Therefore, the exponential smooth moving average line is used as a breathing reference line to determine the breathing phase of the user, although most of noise can be filtered to maintain the stability of the breathing phase determination signal, the longer period exponential smooth moving average line also reflects the real variation of the breathing flow signal in a delayed manner, so that the breathing phase determination signal is distorted, which is particularly obvious when the breathing system leaks air or stops leaking air, for example, when the breathing system is connected with a ventilation pipeline between a respirator and a breathing mask worn by the user.
Referring to fig. 3A and 3B, fig. 3A shows the system breathing Flow (labeled as C11), the breathing Flow signal Flow (labeled as C12), and the breathing baseline of the long-period EMA (labeled as C13) relative to the time axis when the breathing apparatus starts to leak air, wherein the breathing baseline of the long-period EMA (labeled as C13) is not corrected by the breathing baseline reference correction value. Fig. 3B is a respiratory phase decision signal (labeled C14) generated in accordance with fig. 3A with respect to the time axis, wherein the respiratory phase decision signal (labeled C14) has four values (1-4) on the phase axis corresponding to four phases, respectively, such that the respiratory phase of the user has four phases.
In fig. 3A and 3B, 5 intervals (or 5 stages) such as a1-E1 can be distinguished along the time axis:
interval a 1: the respiratory phase decision signal (labeled C14) may be triggered normally.
Interval B1: when the respirator system starts to enter a leakage state, the respiratory Flow (marked as C11) of the system rises sharply, so that the respiratory Flow signal Flow (marked as C12) and the respiratory reference line (marked as C13) of the long-period EMA are completely not intersected, and the respiratory phase determination signal (marked as C14) is deviated.
Interval C1: the respiratory phase decision signal (labeled C14) cannot be triggered, and the respiratory baseline (labeled C13) is tracked, wherein the respiratory phase decision signal (labeled C14) cannot be triggered, that is, the respiratory phase decision signal (labeled C14) stays at a respiratory phase for more than a specified threshold time, as shown in fig. 3B, the respiratory phase decision signal (labeled C14) stays at the respiratory phase 2 from the end of the interval B1 to the interval C1.
Interval D1: after a delay of about 12 respiratory cycles, the respiratory baseline (labeled C13) has caught up with the respiratory Flow signal Flow (labeled C12) and reached a stage sufficient for initial phase determination, but at which the phase may deviate.
Interval E1: at this time, compared to the interval a1, although the value of the respiration Flow signal Flow (labeled as C12) is still high, the respiration phase determination signal (labeled as C14) can be triggered normally.
Referring to fig. 4A and 4B, fig. 4A shows the system breathing Flow (labeled as C21), the breathing Flow signal Flow (labeled as C22), and the breathing baseline of the long-period EMA (labeled as C23) relative to the time axis when the breathing apparatus system starts to change from air-leakage to air-leakage, wherein the breathing baseline of the long-period EMA (labeled as C23) is not corrected by the breathing baseline reference correction value, without using the breathing baseline tracking acceleration method of the present invention in fig. 4A. Fig. 4B shows the generation of a respiratory phase determination signal (labeled C24) with respect to the time axis as determined in fig. 4A.
In fig. 4A and 4B, 5 intervals (or 5 stages) such as a2-E2 can be distinguished:
interval a 2: the respiratory phase decision signal (labeled C24) may be triggered normally.
Interval B2: when the respirator system starts to enter a state of being converted from air leakage to air leakage, the respiratory Flow (marked as C21) of the system is suddenly reduced, so that the respiratory Flow signal Flow (marked as C22) and the respiratory reference line (marked as C23) of the long-period EMA are completely not intersected, and the respiratory phase determination signal (marked as C24) is deviated.
Interval C2: the breathing phase decision signal (labeled C24) cannot be triggered and the breathing baseline (labeled C23) of the long cycle EMA is tracked.
Interval D2: after a delay of about 4.5 breath cycles, the breathing baseline (labeled C23) of the long-cycle EMA has caught up with the breathing Flow signal Flow (labeled C22) and reached a stage sufficient for initial phase determination, but at which the phase may be biased.
Interval E2: the respiratory phase decision signal (labeled C24) has been triggered normally.
Referring to fig. 5A and 5B, fig. 5A shows the system breathing Flow (labeled as C31), the breathing Flow signal Flow (labeled as C32), the breathing baseline of the long-period EMA (labeled as C33), and the breathing baseline reference correction value (labeled as C35) relative to the time axis when the breathing apparatus starts to leak air, wherein the breathing baseline of the long-period EMA (labeled as C33) is corrected in the interval C3 according to the breathing baseline reference correction value (labeled as C35). Fig. 5B shows the generation of a respiratory phase determination signal (labeled C34) with respect to the time axis as determined in fig. 5A.
In fig. 5A and 5B, 5 intervals (or 5 stages) such as a3-E3 can be distinguished:
interval a 3: the respiratory phase decision signal (labeled C34) may be triggered normally.
Interval B3: when the respirator system starts to enter a leakage state, the respiratory Flow (marked as C31) of the system rises suddenly, so that the respiratory Flow signal Flow (marked as C32) and the respiratory reference line (marked as C33) of the long-period EMA are completely not intersected, and the respiratory phase determination signal (marked as C34) generates deviation.
Interval C3: the respiration phase determination signal (labeled as C34) cannot be triggered, and the respiration reference line (labeled as C33) of the long-period EMA performs tracking correction according to the respiration reference correction value (labeled as C35).
Interval D3: after a delay of about 2 breathing cycles, the breathing baseline (labeled C33) of the long-cycle EMA has caught up with the breathing Flow signal Flow (labeled C32) and reached a stage sufficient for initial phase determination, but the phase may be biased.
Interval E3: at this time, compared to the interval a3, although the value of the respiration Flow signal Flow (labeled as C32) is still high, the respiration phase determination signal (labeled as C34) can be triggered normally.
Referring to fig. 6A and 6B, fig. 6A shows the system breathing Flow (labeled as C41), the breathing Flow signal Flow (labeled as C42), and the breathing baseline of the long-period EMA (labeled as C43) relative to the time axis when the ventilator system starts to change from air-leakage to air-leakage by using the breathing baseline tracking acceleration method of the present invention, wherein the breathing baseline of the long-period EMA (labeled as C43) is corrected in the interval C4 according to the breathing baseline reference correction value (not shown). Fig. 4B shows the respiratory phase determination signal (labeled C44) determined from fig. 4A with respect to the time axis.
In fig. 6A and 6B, 5 intervals (or 5 stages) such as a4-E4 can be distinguished:
interval a 4: the respiratory phase decision signal (labeled C44) may be triggered normally.
Interval B4: when the respirator system starts to enter a state of being converted from air leakage to air leakage, the respiratory Flow (marked as C41) of the system is suddenly reduced, so that the respiratory Flow signal Flow (marked as C42) and the respiratory reference line (marked as C43) of the long-period EMA are completely not intersected, and the respiratory phase determination signal (marked as C44) is deviated.
Interval C4: the respiration phase determination signal (labeled C44) cannot be triggered, and the respiration reference line (labeled C43) of the long-period EMA is tracked and corrected according to the respiration reference line reference correction value (not shown).
Interval D4: after a delay of about 2.5 breath cycles, the breathing baseline (labeled C43) of the long-cycle EMA has caught up with the breathing Flow signal Flow (labeled C42) and reached a stage sufficient for initial phase determination, but the phase may be biased.
Interval E4: the respiratory phase decision signal (labeled C44) has been triggered normally.
Referring to fig. 7 and 8, fig. 7 is a flowchart of a method for tracking and accelerating a breathing baseline according to the present invention, which includes steps S1 to S5, corresponding to the flowchart of the method for tracking and accelerating a breathing baseline shown in fig. 7, fig. 8 discloses a computing module 20 of a method for tracking and accelerating a breathing baseline according to another embodiment of the present invention, compared to the computing module 10 disclosed in fig. 1, fig. 8 further includes a modulation trigger condition determining unit 18, a first data switch to a fourth data switch 21-24, wherein an output end of the modulation trigger condition determining unit 18 is connected to control ends SW of the first to fourth data switches 21-24 to control data output of the first to fourth data switches 21-24, and the modulation trigger condition determining unit 18 is connected to the high and low point determining unit 12, the breathing baseline unit 13, and the amplitude determining unit 14, And the phase detection unit 17 for receiving the output data of the high/low point determination unit 12, the respiration reference line unit 13, the amplitude determination unit 14, and the phase detection unit 17.
The first to third data switches 21-23 each have an input terminal, an output terminal and the control terminal SW, the control terminal SW can control whether the data of the input terminal can be outputted through the output terminal; wherein the fourth data switch 24 has a control terminal SW, a first input terminal X, a second input terminal Y and an output terminal O, the control terminal SW can select to output the data of the first input terminal X or the data of the second input terminal Y from the output terminal O, wherein the input terminal and the output terminal of the first data switch 21 are respectively connected to the amplitude determination unit 14 and the respiration reference line reference value unit 15, the input terminal and the output terminal of the second data switch 22 are respectively connected to the high-low point determination unit 12 and the respiration reference line reference value unit 15, the input terminal and the output terminal of the third data switch 23 are respectively connected to the respiration reference line unit 13 and the respiration reference line correction unit 16, the first input terminal X and the second input terminal Y of the fourth data switch 24 are respectively connected to the respiration reference line unit 13 and the respiration reference line correction unit 16, and the output terminal O of the fourth data switch 23 is connected to the phase detection unit 17.
Referring to fig. 7 and 8, the steps S1 to S5 include:
step S1 (calculate relative high/low point): the high/low point determination unit 12 of the calculation module 20 receives the respiratory Flow signal Flow from the respiratory signal unit 11, and generates and outputs the relative high point PoleHnAnd the relatively low point PoleLnWhere the foot code n represents the current value. The respiration baseline unit 13 also receives the respiration Flow signal Flow from the respiration signal unit 11, and generates and outputs a respiration baseline accordingly. The amplitude determination unit 14 receives the relative high point PoleH from the high/low point determination unit 12nAnd the relatively low point PoleLnAnd accordingly generates and outputs a respiratory amplitude FlowPP. The calculation formula of the respiratory amplitude FlowPP is as follows:
·FlowPPn＝PoleHn-PoleLnwhere the foot code n represents the current value.
Step S2 (phase detection time out): when the phase detecting unit 17 of the calculating module 10 calculates the respiratory phase determination signal according to the respiratory Flow signal Flow transmitted from the respiratory signal unit 11 and the respiratory baseline value Base output from the respiratory baseline unit 13 transmitted from the fourth data switch 24 or the modified respiratory baseline value Bnew output from the respiratory baseline correcting unit 16, and determines that the respiratory phase determination signal stays at a respiratory phase exceeding a time threshold (i.e. the respiratory phase determination signal is overdue and not triggered), the phase detecting unit 17 outputs a first correction signal (the value is true) to the modulation trigger condition determining unit 18, and the Flow goes to step S3, when the phase detecting unit 17 determines that the respiratory phase determination signal stays at a respiratory phase not exceeding the time threshold (i.e. the respiratory phase determination signal is triggered and not overdue), the flow proceeds to step S1. Wherein the time threshold may be, for example, a cycle length average of 0.01-0.99 previous 30 breath cycles.
Step S3 (whether the modulation trigger condition is satisfied): the modulation trigger condition determining unit 18 determines the trigger condition according to the signal level from the high level to the low levelThe relative high point PoleH received by the point determination unit 12n、PoleHn-1And the relatively low point PoleLn, PoleLn-1And the breathing reference line values Basen, Basen-1 received from the breathing reference line unit 13 and the breathing amplitude FlowPP received from the amplitude determination unit 14n、FlowPPn-1And the first correction signal received from the phase detection unit 17 to determine whether the modulation triggering condition is satisfied, wherein a respiration amplitude threshold ThppA breath high threshold ThHA breath low threshold ThLAnd a breathing baseline threshold ThBLIt is calculated that the modulation trigger condition is satisfied when any one of the following trigger conditions is satisfied and the value of the first correction signal is true, wherein the foot code n represents the current value, and the foot code n-1 represents the previous value:
amplitude modulation trigger condition: (FlowPP)n-FlowPPn-1)＞Thpp
High point modulation trigger condition: (PoleH)n-PoleHn-1)＞ThH
Low point modulation trigger condition: (PoleL)n-PoleLn-1)＞ThL
Baseline modulation trigger conditions: (Base)n-Basen-1)＞ThBL
Wherein the respiration amplitude threshold ThppThe breath high point threshold ThHThe breath low threshold ThLAnd the respiratory baseline threshold ThBLThe calculation formulas of (A) and (B) are respectively as follows:
·Thpp＝FlowPPn-1×Pthppsaid respiratory amplitude threshold parameter PthppBetween 1% and 200%;
·ThH＝FlowPPn-1×PthHthe high point threshold parameter PthHBetween 1% and 200%;
·ThL＝FlowPPn-1×PthLthe low point threshold parameter PthLBetween 1% and 200%;
·ThBL＝FlowPPn-1×PthBLthe baseline threshold parameter PthBLBetween 1% and 200%.
When the modulation trigger condition determining unit 18 determines that the modulation trigger condition is satisfied, the output terminal of the modulation trigger condition determining unit 18 outputs a control signal to the control terminals SW of the first to fourth data switches 21 to 24 to control the data output of the first to fourth data switches 21 to 24, so that the breathing reference line reference value unit 15 can receive the relatively high point PoleH from the high and low point determining unit 12nAnd the relatively low point PoleLnAnd the respiratory amplitude FlowPP transmitted from the amplitude determining unit 14nAnd makes the respiration reference line correcting unit 16 receive the respiration reference line value Base from the reference line unit 13nMeanwhile, the phase detecting unit 17 receives the corrected breathing reference line value from the breathing reference line correcting unit 16 instead of receiving the breathing reference line value from the breathing reference line unit 15, and the process goes to step S4, and when the modulation triggering condition determining unit 18 determines that the modulation triggering condition is not satisfied, the process goes back to step S1.
Step S4 (calculating breathing baseline reference value): the respiratory baseline reference value unit 15 is based on the relative low point PoleL received by the high-low point determination unit 12nAnd the respiratory amplitude FlowPP received by the amplitude determination unit 14n-1Calculating a reference Bref of a respiration datum linenWherein the foot code n represents the current value, the foot code n-1 represents the previous value, the reference value Bref of the breathing reference linenThe calculation formula of (2) is as follows:
·Brefn＝PoleLn+FlowPPn-1×Prefsaid baseline reference value parameter PrefBetween 1% and 99%.
Step S5 (correction of breathing reference line): the respiration reference line correcting unit 16 corrects the reference value Base according to the respiration reference line received by the respiration reference line unit 13n-1And the breathing reference line reference value Bref received by the breathing reference line reference value unit 15nCalculating a corrected breathing reference line value BnewnThe breathing reference line correcting unit 16 corrects the corrected breathing reference line value BnewnOutput to the phase detection unit 17 via the fourth data switch 24, wherein the foot code n represents the current value, the foot code n-1 represents the previous value, and the modified breathing baseline value BnewnThe calculation formula of (2) is as follows:
·Bnewn＝(Brefn-Basen-1)×PBL+Basen-1the baseline modulation parameter PB，Between 1% and 99%.
The respiratory amplitude threshold parameter Pth in FIGS. 5A, 5B, 6A, 6BppThe high threshold value PthH and the low threshold value PthLAnd the baseline threshold parameter PthBLThe datum line reference value parameter PrefThe baseline modulation parameter PBLAll values of (A) are 50%.
Also labeled in fig. 5A are 3 relatively high PoleH points P2, P4, P6, etc. and 3 relatively low PoleL points P1, P3, P5, etc., wherein point P1 and P2 are normal, the change of point P4 (compared to point P2) makes the modulation trigger condition (i.e., the high modulation trigger condition) true, so that the calculation module 20 starts to track and updates the respiration baseline reference value (as shown by C35) at the next point (point P5) and accordingly corrects the respiration baseline (as shown by C33), the change of point P5 (compared to point P3) makes the modulation trigger condition (i.e., the low modulation trigger condition) true, so that the calculation module 20 updates the respiration baseline reference value (as shown by C35) again and corrects the baseline (as shown by C33), and then the corrected respiration baseline (as indicated by the Flow rate signal C33) is able to track the respiration baseline 36 (as indicated by C32), the respiratory phase decision signal (labeled C34) may then be triggered normally.
As can be seen from the above description of fig. 8: the calculating module 20 of fig. 8 and the calculating module 10 of fig. 1 have similar functions when the modulation triggering condition is satisfied, but the calculating module 20 of fig. 8 and the calculating module 10 of fig. 1 have different functions when the modulation triggering condition is not satisfied. Furthermore, all the components in fig. 8, such as the respiration signal unit 11, the modulation trigger condition determining unit 18 and the first to fourth data switches 21 to 24, can be hardware, software or a combination of hardware and software. Similarly, all the components in fig. 1 may be formed by hardware, software, or a combination of hardware and software.
Comparing fig. 3A and fig. 5A, it can be seen that the method for accelerating the tracking of the breathing reference line can greatly shorten the tracking time of the breathing reference line from 12 breathing cycles to 2 breathing cycles, and similarly, comparing fig. 4A and fig. 6A, it can be seen that the method for accelerating the tracking of the breathing reference line can greatly shorten the tracking time of the breathing reference line from 4.5 breathing cycles to 2.5 breathing cycles. Therefore, the method for tracking and accelerating the breathing reference line can achieve the purpose of rapidly adjusting the breathing reference line.
Although the present invention has been described with reference to the preferred embodiments, it should be understood that various changes, substitutions and alterations can be made herein without departing from the spirit and scope of the invention as defined by the appended claims.

Claims (6)

1. A method for tracking and accelerating a breathing datum line is characterized in that a calculation module is provided and a breathing flow signal is received, and the method for tracking and accelerating the breathing datum line comprises the following steps:
step S1: the calculation module generates a respiration amplitude and a respiration datum line according to the respiration flow signal;
step S2: the calculation module generates a respiratory phase determination signal according to the respiratory flow signal and the respiratory reference line, and when the respiratory phase determination signal stays in a respiratory phase exceeding a time threshold, the process goes to step S3, and when the respiratory phase determination signal stays in a respiratory phase not exceeding the time threshold, the process goes back to step S1;
step S3: judging whether a modulation trigger condition is satisfied, if yes, jumping to step S4, and if not, jumping back to step S1;
step S4: the calculation module generates a respiration datum line reference value according to the product of the respiration amplitude and a proportional parameter and a relative low point in the respiration datum line;
step S5: the calculation module corrects the breathing reference line according to the breathing reference line reference value.
2. The method as claimed in claim 1, wherein the condition for triggering modulation is any one of the following conditions:
amplitude modulation trigger conditions: the difference between two consecutive breath amplitudes in the breath reference line is greater than a breath amplitude threshold;
high-point modulation trigger conditions: the difference between two continuous relative high points in the breathing datum line is greater than a breathing high point threshold value;
low-point modulation trigger condition: the difference between two consecutive relatively low points in the breathing reference line is greater than a breathing low point threshold;
the reference line modulation triggering condition is as follows: the difference between two consecutive points in the breathing reference line is greater than a breathing reference line threshold.
3. The method of claim 2, wherein each of the respiration amplitude threshold, the respiration high threshold, the respiration low threshold, and the respiration baseline threshold is a product of the respiration amplitude and a scaling parameter.
4. The method of claim 1, wherein the respiratory flow signal is a real-time measured flow signal, a filtered flow signal, or a processed patient respiratory signal.
5. The method as claimed in claim 1, wherein the reference value of the breathing reference line is calculated by:
the reference value Bref of the respiration datum linen＝PoleLn+FlowPPn-1×PrefThe baseline reference value parameter PrefBetween 1% and 99%, PoleLnFlowPP, the current relatively low point in this baseline of breathingn-1Is the amplitude of the previous breath in the breathing reference line, wherein the foot code n represents the current value and the foot code n-1 represents the previous value.
6. The method as claimed in claim 5, wherein the modified value of the breathing reference line is calculated by the following formula:
the corrected breathing reference line value Bnewn＝(Brefn-Basen-1)×PBL+Basen-1The baseline modulation parameter PBLBetween 1% and 99%, Basen-1Is the previous value of the breathing reference line.
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