CN109847160B - Lung breathing assistance control device and breathing machine - Google Patents
Lung breathing assistance control device and breathing machine Download PDFInfo
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- CN109847160B CN109847160B CN201910032784.9A CN201910032784A CN109847160B CN 109847160 B CN109847160 B CN 109847160B CN 201910032784 A CN201910032784 A CN 201910032784A CN 109847160 B CN109847160 B CN 109847160B
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Abstract
The invention discloses a lung breathing assistance control device and a breathing machine, relating to the field of lung breathing, and the lung breathing assistance control device comprises: a memory and a processor and a computer program stored on the memory and executable on the processor, the computer program being a method of pulmonary respiratory assistance control, the processor implementing the steps of: measuring first displacement generated in two processes of expiration and normal inspiration of the thorax of the human body during normal calm breathing; acquiring second displacement generated in two processes of expiration and normal inspiration of the thorax during quiet respiration when a respirator is equipped in real time; calculating a deviation value of the first displacement and the second displacement; and determining the air supply amount of the respirator for inflating the lung according to the deviation value. To solve the problems that the flow control of the breathing machine is complicated due to the difference of the states of the patients and the air leakage detection with higher requirements needs to be carried out.
Description
Technical Field
The invention relates to the field of lung respiration, in particular to a lung respiration assisting control device and a respirator.
Background
The respirator is a device which can replace, control or change the normal physiological respiration of a human, increase the ventilation capacity of the lung, improve the respiratory function, reduce the consumption of the respiratory function and save the reserve capacity of the heart. When the infant is complicated with acute respiratory failure, the infant needs to consider tracheal intubation and a breathing machine due to ineffective active conservative treatment, weakened respiration, excessive and thick phlegm, difficult sputum excretion, airway obstruction or pulmonary atelectasis.
Currently, ventilators are classified into 2 categories according to the type of use or application: 1. controlled Mechanical Ventilation (CMV), which defines: the patient's breathing is generated, controlled and regulated entirely by the mechanical ventilator in the event of a reduction or elimination of spontaneous breathing; the application is applied to disappearance or weakening of spontaneous respiration caused by diseases; spontaneous breathing is inhibited or weakened by artificial methods when the spontaneous breathing is irregular or too frequent and the mechanical ventilation cannot be coordinated with the patient. 2. Assisted Mechanical Ventilation (AMV) in which spontaneous breathing of a patient is assisted or augmented by a ventilator in the presence of Assisted Mechanical Ventilation (AMV) patient breathing. The variety of mechanical ventilation is primarily triggered by the patient's inspiratory negative pressure or inspiratory flow; the method is applied to patients who have spontaneous respiration weakened and are ventilated with relatively regularity although the spontaneous respiration exists.
At present, respirators are classified into 3 types according to the switching mode of inhalation and exhalation phases: 1. pressure setting type: when the pressure in the respiratory tract reaches the expected value, the breathing machine opens the expiratory valve, the thorax and the lung collapse passively or expiration is generated by negative pressure, and when the pressure in the airway continuously drops, the breathing machine generates airflow again by positive pressure and causes inspiration. The constant pressure type respirator is started by the pressure in the respiratory tract, and the detection of the pressure in the respiratory tract is usually detected by an invasive tracheal cannula. 2. Volume fixing type: the predicted tidal volume is sent into the lung through positive pressure, and after the predicted tidal volume is reached, air supply is stopped, and the lung enters an expiratory state. 3, timing type: air is supplied according to preset inspiration and expiration time.
The process and principle of respiratory movement in a calm state of a person are as follows: during inspiration, the external intercostal muscles contract, the ribs are lifted, and the sternum moves upwards and outwards, so that the anteroposterior diameter and the left and right diameters of the thorax are increased; meanwhile, the diaphragm muscle contracts, and the top of the diaphragm descends, so that the upper and lower diameters of the thorax are increased. At the moment, the thorax is enlarged, the volume of the lung is increased along with the expansion of the lung, the air pressure in the lung is reduced, and the outside air enters the lung through the respiratory tract to finish the inspiration action; during expiration, the external intercostal muscles relax, the ribs descend under the action of gravity, the sternum moves downwards and inwards, and the anterior-posterior diameter and the left-right diameter of the thorax are reduced: simultaneously, the diaphragm muscle relaxes, and the top of the compartment rises, so that the upper and lower diameters of the thorax are reduced. At this time, the thorax is contracted, the lung is retracted, the volume of the lung is reduced, the air pressure in the lung is increased, and partial air in the alveoli is forced to be exhausted to the outside of the body through the respiratory tract, so that the exhalation action is completed. Thus, the thorax expands and contracts laterally as a result of the contraction and relaxation of the intercostal and diaphragmatic muscles, but at the end of the moment, whether inspiration or expiration, the air pressure in the lungs is equal to the ambient air pressure. It is often seen that some patients with shallow breathing have hypoventilation and hypoxia. When rescuing patients with sudden cessation of breathing, the thorax of the patient is expanded and contracted by artificial respiration to maintain lung ventilation. But care should be taken not to apply too hard to damage the ribs, but to apply a sufficient amplitude to ventilate the alveoli.
The displacement sensor for acquiring the human thorax data with the application number of 201510894628.5 can be applied to the real-time acquisition of thorax outlines, and provides the displacement sensor for acquiring the human thorax electrical impedance tomography thorax outline data, which is applied to the real-time acquisition of thorax outlines so as to obtain the spatial position information required by updating a field model. So that the metal rod as the inner electrode of the displacement sensor can be driven to do corresponding movement along with the respiration of the human body in the process of breathing the thoracic cavity of the human body. In the reciprocating movement, the facing area of the inner electrode and the outer electrode of the displacement sensor is changed, the capacitance value is correspondingly changed, and the change of the spatial position is finally reflected.
And the micro-displacement sensor, the micro-displacement change frequency and respiratory frequency detection device with application number 201520526583.1, do not need to intervene human body, wherein the first metal plate of the micro-displacement sensor is arranged in front of the chest of the human body, the second metal plate of the micro-displacement sensor is arranged on the back of the human body, when the human body does respiratory motion, the air capacity of the chest is changed periodically, so that the distance between the first metal plate and the second metal plate is changed periodically, namely displacement is generated, and hardware support is provided for the invention.
The study and application of ventilator detection and control algorithm in the university master's academic paper of southeast university in 2015 enhances the accuracy of air leakage detection, but air leakage is often difficult to overcome.
Disclosure of Invention
In view of the above, the present invention provides a lung breathing assistance control device and a ventilator, which determine an air supply amount of a ventilator to inflate a lung according to a physical change of a displacement of a thorax, so as to solve the problems that a flow control of the ventilator is complicated due to a difference of patient states and air leakage detection with high requirements needs to be performed.
In a first aspect, the present invention provides a lung breathing assistance control apparatus comprising:
a memory and a processor and a computer program stored on the memory and executable on the processor, the computer program being a method of controlling lung breathing assistance as described above, the processor implementing the following steps when executing the program:
measuring first displacement generated in two processes of expiration and normal inspiration of the thorax of the human body during normal calm breathing;
acquiring second displacement generated in two processes of expiration and normal inspiration during quiet breathing when a respirator is equipped in real time;
calculating a deviation value of the first displacement and the second displacement;
determining the air supply amount of the respirator for inflating the lung according to the deviation value;
wherein the deviation value and the air supply amount are in a linear positive proportional relation; the normal state of normal calm breathing and normal inspiration is the condition that the human body breathes autonomously and is not provided with a breathing machine.
Preferably, the control device further includes:
measuring the maximum displacement generated in two processes of expiration and normal inspiration of the thorax of the human body during normal deep breathing;
determining the maximum value of the air supply quantity according to the maximum displacement;
the maximum value of the air supply amount is the maximum air supply amount of the respirator for inflating the lung.
Preferably, according to the first displacement and the maximum displacement, determining a displacement measuring range;
dividing the displacement measuring range into a plurality of displacement intervals, wherein each displacement interval corresponds to one air supply gear;
judging the positions of the deviation values in the displacement intervals;
and controlling the air supply amount gear of the respirator for inflating the lung according to the position.
Preferably, recording the current air supply quantity gear;
if the deviation value is within a certain interval in the displacement intervals, counting the certain interval;
if the count reaches a preset number, determining the position and clearing the counts of the displacement intervals except the position;
and adjusting the current air supply quantity gear to the air supply quantity gear corresponding to the position, clearing the current air supply quantity gear, recording the adjusted air supply quantity gear, and repeating the steps.
Preferably, if the deviation value is at a section division point of the plurality of displacement sections, the displacement sections on the right side of the section division point are counted.
Preferably, a K-th moment displacement interval corresponding to the current air supply quantity gear is recorded;
calculating a displacement interval at the K +1 moment corresponding to the deviation value at the K +1 moment;
judging whether the displacement interval at the K +1 moment and the displacement interval at the K moment are adjacent intervals or not;
if yes, controlling the breathing machine to inflate the lungs according to the air supply amount gear corresponding to the displacement interval at the K +1 moment;
if not, determining a middle displacement interval between the K +1 moment displacement interval and the K-th moment displacement interval, and controlling the breathing machine to inflate the lung according to the air supply amount gear corresponding to the middle displacement interval.
Preferably, recording the displacement interval at the K +1 moment or the middle displacement interval;
calculating a displacement interval at the K +2 moment corresponding to the deviation value at the K +2 moment;
judging whether the displacement interval at the K +2 moment is the same as the displacement interval at the K moment or the displacement interval at the K +1 moment;
if yes, controlling the breathing machine to inflate the lungs according to the air supply amount gear corresponding to the displacement interval at the K moment or the displacement interval at the K +1 moment;
if not, controlling the breathing machine to inflate the lungs according to the air supply quantity gear corresponding to the K +2 moment displacement interval.
Preferably, if the deviation value is greater than the alarm displacement value, alarm counting is carried out on the deviation value;
if the next alarm count of the deviation value is larger than the alarm displacement value, adding 1 to the alarm count, otherwise, clearing the alarm count;
when the alarm count reaches the preset alarm count, controlling the respirator to alarm, and clearing the alarm count;
wherein the alarm displacement value is the maximum displacement.
In a second aspect, the present invention provides a ventilator comprising:
a lung breathing assistance control apparatus as described above;
the control device is respectively connected with the displacement acquisition device and the breathing machine;
the displacement acquisition device is used for measuring first displacement generated in two processes of expiration and normal inspiration of the thorax of the human body during normal calm breathing and acquiring second displacement generated in two processes of expiration and normal inspiration during calm breathing when a breathing machine is equipped in real time;
the lung breathing assistance control device calculates a deviation value of the first displacement and the second displacement;
determining the air supply amount of the respirator for inflating the lung according to the deviation value;
wherein the deviation value and the air supply amount are in a linear positive proportional relation; the normal state of normal calm breathing and normal inspiration is the condition that the human body breathes autonomously and is not provided with a breathing machine.
The invention provides a lung breathing assistance control device and a respirator, which are used for determining the air supply quantity of the respirator for inflating a lung by using the physical change of the displacement of a thorax so as to solve the problems that the flow control of the respirator is complex and air leakage detection with higher requirements is required due to the difference of the states of patients.
The foregoing description is only an overview of the technical solutions of the present invention, and the embodiments of the present invention are described below in order to make the technical means of the present invention more clearly understood and to make the above and other objects, features, and advantages of the present invention more clearly understandable.
Drawings
The above and other objects, features and advantages of the present invention will become more apparent from the following description of the embodiments of the present invention with reference to the accompanying drawings, in which:
FIG. 1 is a flow chart of a method of controlling lung breathing assistance in accordance with an embodiment of the present invention;
FIG. 2 is a flow chart of an air supply shift division method of a lung breathing assistance control method according to an embodiment of the present invention;
FIG. 3 is a flow chart of an air supply shift adjustment method of a lung breathing assistance control method according to an embodiment of the present invention;
FIG. 4 is a flow chart of an adjusting method for an excessive abrupt change of an air supply amount gear in a lung breathing assistance control method according to an embodiment of the present invention;
FIG. 5 is a flow chart of a method for adjusting the next moment when the supply air quantity step is suddenly changed too much according to an embodiment of the present invention;
FIG. 6 is a flow chart of an alarm control method of a lung breathing assistance control method according to an embodiment of the present invention;
fig. 7 is a schematic diagram of a lung breathing assistance control device according to an embodiment of the present invention.
Detailed Description
The present invention will be described below based on examples, but it should be noted that the present invention is not limited to these examples. In the following detailed description of the present invention, certain specific details are set forth. However, the present invention may be fully understood by those skilled in the art for those parts not described in detail.
Furthermore, those skilled in the art will appreciate that the drawings are provided solely for the purposes of illustrating the invention, features and advantages thereof, and are not necessarily drawn to scale.
Also, unless the context clearly requires otherwise, throughout the description and the claims, the words "comprise", "comprising", and the like are to be construed in an inclusive sense as opposed to an exclusive or exhaustive sense; that is, the meaning of "includes but is not limited to".
Fig. 1 is a flowchart of a lung breathing assistance control method according to an embodiment of the present invention. As shown in fig. 1, a method for controlling lung breathing assistance includes: step S101, measuring first displacement generated in two processes of expiration and normal inspiration of the human thorax during normal calm breathing; step S102, acquiring second displacement generated in two processes of expiration and normal inspiration of the thorax during quiet respiration when a respirator is equipped in real time; step S103, calculating a deviation value of the first displacement and the second displacement; step S104, determining the air supply amount of the respirator for inflating the lung according to the deviation value; wherein, the deviation value and the air supply amount are in a linear positive proportional relation; normally, the human body breathes autonomously and is not equipped with a breathing machine. The invention only determines the air supply quantity of the respirator for inflating the lung by the physical change of the displacement of the thorax, so as to solve the problems that the flow control of the respirator is complex and the air leakage detection with higher requirement needs is required due to the difference of the states of patients, even if the respirator has the problem of air leakage, the air supply quantity of the respirator for inflating the lung is reduced, the patient himself can actively increase the second displacement, the deviation value of the first displacement and the second displacement is increased, the deviation value is increased, the air supply quantity of the respirator for inflating the lung is correspondingly increased, the adjustment of the air supply quantity of the respirator for inflating the lung is completed in one breathing period, and the adjustment speed is higher according to single variable. Meanwhile, the maximum displacement generated in two processes of expiration and normal inspiration of the human thorax during normal deep breathing is measured; determining the maximum value of the air supply quantity according to the maximum displacement; the maximum value of the air supply amount is the maximum air supply amount of the respirator for inflating the lungs.
Theoretically, whether the deviation value of the first displacement and the second displacement at the first moment is 0 or not is judged; if the deviation value between the first displacement and the second displacement at the time one is 0, the respirator inflates the lungs according to the air supply amount corresponding to the time zero (namely, the air supply amount of the respirator inflating the lungs is unchanged at the time); if the deviation value between the first displacement and the second displacement at the first moment is not 0, the magnitude of the deviation value is determined, and the increment or decrement of the air supply amount of the respirator for inflating the lungs is determined according to the magnitude of the deviation value. The time zero is a time before the time one, and can be understood as a period before the breathing period, and the times in the invention are all a breathing period or a plurality of set periods.
However, since the second displacement is caused by the motion disturbance of the heart or abdominal cavity, or the motion disturbance of the patient or the measurement acquisition error, the deviation value between the first displacement and the second displacement cannot be substantially 0, and even if the micro-displacement sensor of application No. 201520526583.1, the micro-displacement variation frequency and respiratory frequency detection device, or the displacement sensor of application No. 201510894628.5 for acquiring the data of the thoracic cavity of the human body is used, the deviation value between the first displacement and the second displacement cannot be substantially 0. Therefore, the utilization of the deviation value adopts a method of judging displacement intervals, each displacement interval corresponds to one gear, and the description in fig. 2 can be specifically seen.
Fig. 2 is a flowchart of an air supply rate gear division method of a lung breathing assistance control method according to an embodiment of the present invention. As shown in fig. 2, an air supply amount gear division method of a lung breathing assistance control method includes: step S201, determining a displacement range according to the first displacement and the maximum displacement; step S202, dividing a displacement range into a plurality of displacement intervals, wherein each displacement interval corresponds to one air supply quantity gear; step S203, judging the positions of the deviation values in a plurality of displacement intervals; step S204 is used for controlling the air supply quantity gear of the respirator for inflating the lung according to the position. Specifically, the number of the displacement sections can be controlled by the flow of the existing respirator, the air source of the respirator is provided with a valve, and the gear of the air supply gear is adjusted by controlling the opening degree of the valve. Determining the displacement range according to the first displacement and the maximum displacement in step S201; giving a dividing condition, wherein the given dividing condition is an endpoint value of a displacement interval, dividing the displacement range into a plurality of displacement intervals according to the given dividing condition and the step S202, and each displacement interval corresponds to one air supply gear; when the offset value is determined to be at the position of the plurality of displacement sections in step S203, that is, when the offset value is at one of the plurality of displacement sections, the air supply gear for inflating the lung by the ventilator is controlled according to the position in step S204.
The details will be described by taking an example that the plurality of displacement intervals are 3 displacement intervals, and the 3 displacement intervals are a high-gear displacement interval, a middle-gear displacement interval and a low-gear displacement interval. The high-grade displacement interval corresponds to a high air supply quantity gear (for example, the opening degree of a valve is more than 70%), the middle-grade displacement interval corresponds to a middle air supply quantity gear (for example, the opening degree of the valve is 50% -70%), and the low-grade displacement interval corresponds to a low air supply quantity gear (for example, the opening degree of the valve is 40% -50%); and when the deviation value is within the middle shift range, controlling the air supply quantity gear of the respirator for inflating the lung to be a middle gear. However, in practice, when we find that the deviation value occasionally falls at the end point of the displacement interval, we consider that the deviation value falls within the displacement interval to the right of the end point (because it is considered that the patient urgently needs a slightly higher gear), the detailed description of fig. 3 can be seen.
Fig. 3 is a flowchart of an air supply amount gear adjustment method of a lung breathing assistance control method according to an embodiment of the present invention. As shown in fig. 3, step S301 records the current air supply amount gear; step S302, if the deviation value is in a certain interval of a plurality of displacement intervals, counting the certain interval; step S303, if the count reaches a preset number, determining the position and the count of other displacement intervals except the clearing position; step S304, adjusting the current air supply quantity gear to an air supply quantity gear corresponding to the position, clearing the current air supply quantity gear, recording the adjusted air supply quantity gear, and repeating the steps; in step S305, if the deviation value is at a section division point of a plurality of displacement sections, the displacement sections on the right side of the section division point are counted. Specifically, the count number reaching the preset number may be 3, taking a plurality of displacement intervals as 3 displacement intervals as an example, and counting the middle-gear displacement interval plus 1 if the deviation value of the first respiratory cycle is within the middle-gear displacement interval; if the deviation value of the second breathing period is in the high-grade displacement interval, counting the high-grade displacement interval by adding 1, the deviation value of the third breathing period and the fourth breathing period is in the middle-grade displacement interval, the counting value of the middle-grade displacement interval is 3 at the moment, the preset number is reached, the current air supply quantity gear is adjusted to the middle gear of the air supply quantity gear, and meanwhile, counting of the high-grade displacement interval is eliminated; and clearing the current air supply amount gear, recording the middle gear of the adjusted air supply amount, and repeating the steps. If the deviation value is at a division point of a plurality of displacement intervals, counting the displacement intervals at the right side of the division point (namely, the displacement intervals larger than the division point), and if the deviation value is at the division point of the middle-gear displacement interval and the low-gear displacement interval, counting the middle-gear displacement interval and not counting the low-gear displacement interval; and when the count of a certain displacement interval reaches the preset number 3, determining that the position of the deviation value is in the displacement interval reaching the preset number 3 and counting other displacement intervals except the clearing position.
The patient breathes more stably, and the air supply gear can fluctuate between the upper gear and the lower gear; in the actual measurement process, we find that a certain deviation value is particularly large due to the action of the patient or the rapid deterioration of the respiratory function, and the influence cannot be eliminated by the above air supply quantity gear adjustment method, so we consider the adjustment method when the sudden change of the air quantity gear is too large, and see the description of fig. 4 specifically.
Fig. 4 is a flowchart of an adjusting method for an excessive abrupt change of an air supply amount gear in a lung breathing assistance control method according to an embodiment of the present invention. As shown in fig. 4, step S401 records a displacement interval at the K-th time corresponding to the current air supply amount gear; step S402, calculating a K +1 moment displacement interval corresponding to the deviation value of the K +1 moment; step S403, judging whether the displacement interval at the moment K +1 and the displacement interval at the moment K are adjacent intervals; if yes, controlling the breathing machine to inflate the lungs according to the air supply amount gear corresponding to the displacement interval at the K +1 moment; if not, determining a middle displacement interval between the displacement interval at the K +1 moment and the displacement interval at the K-th moment, and controlling the breathing machine to inflate the lungs according to the air supply amount gear corresponding to the middle displacement interval. Specifically, taking a plurality of displacement intervals as 3 displacement intervals as an example, recording a K-th displacement interval corresponding to the current (i.e., K-time) air supply amount gear as a low-gear displacement interval; if the next moment K +1 moment displacement interval of the moment K is a high-grade displacement interval, the moment K +1 displacement interval is a high-grade displacement interval, the moment K displacement interval is a low-grade displacement interval, the moment K +1 displacement interval is not adjacent to the moment K displacement interval, the middle displacement interval between the moment K +1 displacement interval and the moment K displacement interval is a middle-grade displacement interval, and the respirator is controlled to inflate the lungs according to the middle-grade air supply quantity corresponding to the middle-grade displacement interval; if the displacement interval at the next time K +1 of the time K is the middle shift interval, the displacement interval at the time K +1 is the middle shift interval, the displacement interval at the time K is the low shift interval, and the displacement interval at the time K +1 is adjacent to the displacement interval at the time K, then the ventilator is controlled to inflate the lungs according to the middle gear of the air supply amount corresponding to the middle shift interval (i.e., the displacement interval at the time K + 1), i.e., the gear for forcibly reducing the air supply amount is first performed, and the subsequent processing is performed, which is specifically shown in the description of fig. 5, where K is 0, 1, and 2 ….
Fig. 5 is a flowchart of an adjusting method for adjusting the next moment when the supply air quantity step is suddenly changed too much according to an embodiment of the present invention. As shown in fig. 5, step S501 records a displacement interval or a middle displacement interval at the time K + 1; step S502, calculating a K +2 moment displacement interval corresponding to the deviation value of the K +2 moment; step S503, judging whether the displacement interval at the K +2 moment is the same as the displacement interval at the K-th moment or the displacement interval at the K +1 moment; if yes, controlling the breathing machine to inflate the lungs according to the air supply amount gear corresponding to the displacement interval at the K-th moment or the displacement interval at the K +1 moment; if not, the breathing machine is controlled to inflate the lungs according to the air supply amount gear corresponding to the displacement interval at the time K + 2. Specifically, taking a plurality of displacement intervals as 3 displacement intervals as an example, if the air supply shift is too large suddenly changed, controlling the respirator to inflate the lungs according to the air supply shift corresponding to the middle displacement interval, and recording the middle displacement interval at the moment, wherein the displacement interval at the moment of the above K +1 is a high-grade displacement interval; meanwhile, in each expiration cycle, the offset value of 2 expiration cycles needs to be calculated, that is, step S502 is executed to calculate the displacement interval at the K +2 time corresponding to the offset value at the K +2 time (if the count reaches a preset number, which may be 3, and it is determined that the displacement interval at the K +2 time needs at least 3 respiration cycles); in step S401 of fig. 4, a K-th time displacement interval corresponding to the current air supply quantity gear is recorded, where the previous K-th time displacement interval is a low-grade displacement interval, and if the K +2 time displacement interval is a high-grade displacement interval, it indicates that an emergency occurs to the patient, for example, breathing difficulty causes rapid deterioration of the breathing function, and the sudden change of the air supply quantity gear is not generated due to the action of the patient because at least 3 breathing cycles have elapsed; if the displacement interval at the moment K +2 is a low-grade displacement interval, the sudden change of the air supply quantity gear position caused by the action of the patient is indicated; if the displacement interval at the time K +2 is not the low-range displacement interval or the high-range displacement interval, the air supply amount gear corresponding to the middle displacement interval at the time K +1 is recorded to inflate the lungs according to the step S501. Then, according to the method of fig. 3, the displacement interval at the time K +3 corresponding to the offset value at the time K +3 is calculated, and the process proceeds to the flow of fig. 5 until step S405 in fig. 4 occurs.
That is to say, in the invention, the second displacement generated in two processes of expiration and normal inspiration of the thorax during quiet respiration when the respirator is equipped is collected in real time; the first displacement is a given value, and the supply of gas to the lungs by the ventilator is generally determined according to the first displacement, such as: when the deviation value is 0 or within a given error, the air supply level of the respirator for inflating the lung is unchanged. When the second time displacement interval and the first time displacement interval are not adjacent to each other, a middle displacement interval between the second time displacement interval and the first time displacement interval is determined, the ventilator is controlled to inflate the lungs according to the air supply rate gear corresponding to the middle displacement interval, and then adjustment is performed according to the adjustment method of the next time when the sudden change of the air supply rate gear is too large in the embodiment shown in fig. 5.
Fig. 6 is a flowchart of an alarm control method of a lung breathing assistance control method according to an embodiment of the present invention. As shown in fig. 6, if the deviation value is greater than the alarm displacement value in step S601, performing alarm counting on the deviation value; step S602, if the next deviation value alarm count is larger than the alarm displacement value, the alarm count is increased by 1, otherwise, the alarm count is cleared; step S603, when the alarm count reaches the preset alarm count, controlling the respirator to alarm, and clearing the alarm count at the same time; wherein, the alarm displacement value is the maximum displacement.
Fig. 7 is a schematic diagram of a lung breathing assistance control device according to an embodiment of the present invention. As shown in fig. 7, a lung breathing assistance control apparatus includes: a memory 701, a processor 702, and a computer program stored in the memory 701 and executable on the processor 702, where the computer program is the above-mentioned method for controlling lung breathing assistance, and the processor 702 executes the program to implement the following steps: measuring first displacement generated in two processes of expiration and normal inspiration of the thorax of the human body during normal calm breathing; acquiring second displacement generated in two processes of expiration and normal inspiration of the thorax during quiet respiration when a respirator is equipped in real time; calculating a deviation value of the first displacement and the second displacement; determining the air supply amount of the respirator for inflating the lung according to the deviation value; wherein, the deviation value and the air supply amount are in a linear positive proportional relation; normally, the human body breathes autonomously and is not provided with a breathing machine.
In the foregoing embodiments, the descriptions of the respective embodiments have respective emphasis, and for parts that are not described in detail in a certain embodiment, reference may be made to related descriptions of other embodiments.
It will be appreciated that the relevant features of the method and apparatus described above are referred to one another. In addition, "first", "second", and the like in the above embodiments are for distinguishing the embodiments, and do not represent merits of the embodiments.
It is clear to those skilled in the art that, for convenience and brevity of description, the specific working processes of the above-described systems, apparatuses and units may refer to the corresponding processes in the foregoing method embodiments, and are not described herein again.
The algorithms and displays presented herein are not inherently related to any particular computer, virtual machine, or other apparatus. Various general purpose systems may also be used with the teachings herein. The required structure for constructing such a system will be apparent from the description above. Moreover, the present invention is not directed to any particular programming language. It is appreciated that a variety of programming languages may be used to implement the teachings of the present invention as described herein, and any descriptions of specific languages are provided above to disclose the best mode of the invention.
In the description provided herein, numerous specific details are set forth. It is understood, however, that embodiments of the invention may be practiced without these specific details. In some instances, well-known methods, structures and techniques have not been shown in detail in order not to obscure an understanding of this description.
Similarly, it should be appreciated that in the foregoing description of exemplary embodiments of the invention, various features of the invention are sometimes grouped together in a single embodiment, figure, or description thereof for the purpose of streamlining the disclosure and aiding in the understanding of one or more of the various inventive aspects. However, the disclosed method should not be interpreted as reflecting an intention that: that the invention as claimed requires more features than are expressly recited in each claim. Rather, as the following claims reflect, inventive aspects lie in less than all features of a single foregoing disclosed embodiment. Thus, the claims following the detailed description are hereby expressly incorporated into this detailed description, with each claim standing on its own as a separate embodiment of this invention.
Those skilled in the art will appreciate that the modules in the device in an embodiment may be adaptively changed and disposed in one or more devices different from the embodiment. The modules or units or components of the embodiments may be combined into one module or unit or component, and furthermore they may be divided into a plurality of sub-modules or sub-units or sub-components. All of the features disclosed in this specification (including any accompanying claims, abstract and drawings), and all of the processes or elements of any method or apparatus so disclosed, may be combined in any combination, except combinations where at least some of such features and/or processes or elements are mutually exclusive. Each feature disclosed in this specification (including any accompanying claims, abstract and drawings) may be replaced by alternative features serving the same, equivalent or similar purpose, unless expressly stated otherwise.
Furthermore, those skilled in the art will appreciate that while some embodiments described herein include some features included in other embodiments, rather than other features, combinations of features of different embodiments are meant to be within the scope of the invention and form different embodiments. For example, in the following claims, any of the claimed embodiments may be used in any combination.
The various component embodiments of the invention may be implemented in hardware, or in software modules running on one or more processors, or in a combination thereof. It will be appreciated by those skilled in the art that a microprocessor or Digital Signal Processor (DSP) may be used in practice to implement some or all of the functions of some or all of the components of a pulmonary breathing assistance control device according to an embodiment of the present invention. The present invention may also be embodied as apparatus or device programs (e.g., computer programs and computer program products) for performing a portion or all of the methods described herein. Such programs implementing the present invention may be stored on computer-readable media or may be in the form of one or more signals. Such a signal may be downloaded from an internet website or provided on a carrier signal or in any other form.
It should be noted that the above-mentioned embodiments illustrate rather than limit the invention, and that those skilled in the art will be able to design alternative embodiments without departing from the scope of the appended claims. In the claims, any reference signs placed between parentheses shall not be construed as limiting the claim. The word "comprising" does not exclude the presence of elements or steps not listed in a claim. The word "a" or "an" preceding an element does not exclude the presence of a plurality of such elements. The invention may be implemented by means of hardware comprising several distinct elements, and by means of a suitably programmed computer. In the unit claims enumerating several means, several of these means may be embodied by one and the same item of hardware. The usage of the words first, second and third, etcetera do not indicate any ordering. These words may be interpreted as names.
Claims (9)
1. A pulmonary respiratory assistance control apparatus, comprising:
a memory and a processor and a computer program stored on the memory and executable on the processor, the computer program being a method of pulmonary respiratory assistance control, the processor implementing the following steps when executing the computer program:
measuring first displacement generated in two processes of expiration and normal inspiration of the thorax of the human body during normal calm breathing;
acquiring second displacement generated in two processes of expiration and normal inspiration of the thorax during quiet respiration when a respirator is equipped in real time;
calculating a deviation value of the first displacement and the second displacement;
determining the air supply amount of the respirator for inflating the lung according to the deviation value;
wherein the deviation value and the air supply amount are in a linear positive proportional relation; the measurement is carried out on the condition that the thorax of the human body normally breathes autonomously and is not provided with a breathing machine in normal calm breathing and normal inspiration.
2. The control device according to claim 1, characterized by further comprising:
measuring the maximum displacement generated in two processes of expiration and normal inspiration of the thorax of the human body during normal deep breathing;
determining the maximum value of the air supply quantity according to the maximum displacement;
the maximum value of the air supply amount is the maximum air supply amount of the respirator for inflating the lung.
3. The control device according to claim 2, characterized in that:
determining a displacement range according to the first displacement and the maximum displacement;
dividing the displacement measuring range into a plurality of displacement intervals, wherein each displacement interval corresponds to one air supply gear;
judging the positions of the deviation values in the displacement intervals;
and controlling the air supply amount gear of the respirator for inflating the lung according to the position.
4. The control device according to claim 3, characterized in that:
recording the current air supply quantity gear;
if the deviation value is within a certain interval in the displacement intervals, counting the certain interval;
if the count reaches a preset number, determining the position and clearing the counts of the displacement intervals except the position;
and adjusting the current air supply quantity gear to the air supply quantity gear corresponding to the position, clearing the current air supply quantity gear, recording the adjusted air supply quantity gear, and repeating the steps.
5. The control device according to claim 4, characterized in that:
and if the deviation value is at the interval division point of the plurality of displacement intervals, counting the displacement intervals on the right side of the interval division point.
6. The control device according to claim 4, characterized in that:
recording a K-th moment displacement interval corresponding to the current air supply quantity gear;
calculating a displacement interval at the K +1 moment corresponding to the deviation value at the K +1 moment;
judging whether the displacement interval at the K +1 moment and the displacement interval at the K moment are adjacent intervals or not;
if yes, controlling the breathing machine to inflate the lungs according to the air supply amount gear corresponding to the displacement interval at the K +1 moment;
if not, determining a middle displacement interval between the K +1 moment displacement interval and the K-th moment displacement interval, and controlling the breathing machine to inflate the lung according to the air supply amount gear corresponding to the middle displacement interval.
7. The control device according to claim 6, characterized in that:
recording the displacement interval at the K +1 moment or the middle displacement interval;
calculating a displacement interval at the K +2 moment corresponding to the deviation value at the K +2 moment;
judging whether the displacement interval at the K +2 moment is the same as the displacement interval at the K moment or the displacement interval at the K +1 moment;
if yes, controlling the breathing machine to inflate the lungs according to the air supply amount gear corresponding to the displacement interval at the K moment or the displacement interval at the K +1 moment;
if not, controlling the breathing machine to inflate the lungs according to the air supply quantity gear corresponding to the K +2 moment displacement interval.
8. The control device according to any one of claims 1 to 7, characterized in that:
if the deviation value is larger than the alarm displacement value, carrying out alarm counting on the deviation value;
if the next alarm count of the deviation value is larger than the alarm displacement value, adding 1 to the alarm count, otherwise, clearing the alarm count;
and when the alarm count reaches a preset alarm count, controlling the respirator to alarm, and clearing the alarm count.
9. A ventilator, comprising:
a lung breathing assistance control apparatus according to any one of claims 1 to 8;
the lung breathing assistance control device is respectively connected with the displacement acquisition device and the breathing machine;
the displacement acquisition device is used for measuring first displacement generated in two processes of expiration and normal inspiration of the thorax of the human body during normal calm breathing and acquiring second displacement generated in two processes of expiration and normal inspiration of the thorax during calm breathing when a breathing machine is equipped in real time;
the control device calculates a deviation value of the first displacement and the second displacement;
determining the air supply amount of the respirator for inflating the lung according to the deviation value;
wherein the deviation value and the air supply amount are in a linear positive proportional relation; the measurement is carried out on the condition that the thorax of the human body normally breathes autonomously and is not provided with a breathing machine in normal calm breathing and normal inspiration.
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