Artificial nose control system

Abstract

The invention relates to the field of auxiliary breathing control systems, in particular to an artificial nose control system which comprises an artificial nose, an airway breathing state judgment module and a wiping driving control module. The artificial nose comprises a main shell, a heat and humidity exchange filter module, an airway opening control module and a differential airflow sensor, the airway breathing state judgment module is in communication connection with the differential airflow sensor; and the wiping driving control module is in communication connection with the air passage opening degree control module. The air passage opening degree control module is connected with the main shell and is used for controlling the opening degree of the air passage; the differential airflow sensor acquires respiration data. According to the artificial nose, the driving module is used for controlling the multiple opening control valves to gather or disperse, so that the opening degree of the airway is accurately controlled. Meanwhile, a differential airflow sensor is further arranged to obtain breathing data, and the opening amount of the airway is determined in combination with other physiological indexes. Automatic self-adaptive adjustment of the resistance of the T pipe is achieved, and the timeliness and the success rate are improved.

Description

Technical Field

[0001] The present invention relates to the field of assisted breathing control systems, and particularly to an artificial nose control system. Background Art

[0002] An artificial airway is an effective connection established between the physiological airway and air or other gas sources to ensure airway patency, providing conditions for effective drainage, patency, mechanical ventilation, and treatment of lung diseases in the respiratory tract. The most common artificial airways are endotracheal intubation (oral, nasal) and tracheotomy, and a ventilator is used to assist the user in breathing.

[0003] When the user's condition improves and they attempt to remove the ventilator and endotracheal tube, the T-tube weaning trial is a commonly used clinical assessment method. By repeatedly adjusting the resistance of the T-tube for a long time and observing changes in the user's respiratory physiological indicators, it is determined whether the user can tolerate weaning and the success rate of extubation is estimated.

[0004] In the prior art, usually this T-tube weaning trial process is completely manually operated by medical staff. Specifically, medical staff use tape to block a part of the opening area of the T-tube according to their clinical experience and the user's reaction to adjust the resistance of the T-tube in real time. This process is very labor-intensive and time-consuming, and at the same time, it is impossible to more accurately determine the size of the blocked opening area of the T-tube, which will increase the failure rate of the T-tube weaning trial. Summary of the Invention

[0005] In view of this, the present invention provides an artificial nose control system, which at least partially solves the problems existing in the prior art.

[0006] According to one aspect of the present invention, there is provided an artificial nose control system, including: an artificial nose, an airway breathing state determination module, and a wiping drive control module; The artificial nose includes: a main housing, a heat and moisture exchange and filtration module, an airway opening degree control module, and a differential air flow sensor; the airway breathing state determination module is communicatively connected to the differential air flow sensor; the wiping drive control module is communicatively connected to the airway opening degree control module; The heat and moisture exchange and filtration module is fixedly arranged inside the inner cavity of the main housing for maintaining the temperature and humidity of the airway; The airway opening degree control module is connected to the main housing for controlling the opening degree of the airway; The differential air flow sensor includes a first air flow probe and a second air flow probe, and the first air flow probe and the second air flow probe are respectively arranged at positions with different heights in the airway passage; Airway through holes are provided on the main housing, the heat and moisture exchange and filtration module, the first holder and the second holder, and the multiple airway through holes are coaxially arranged for forming an airway passage; The airway opening degree control module includes: The first cage, the second cage, a plurality of opening control valves and a driving module; A regular polygon slideway is arranged on the first cage, and a plurality of guiding inclined slideways are evenly arranged on the second cage. The first cage is rotatably connected to the second cage, and each guiding inclined slideway corresponds to one side slideway in the regular polygon slideway; the sliding direction of the side slideway and the sliding direction of the guiding inclined slideway are arranged to cross each other; the number of the opening control valves is the same as the number of sides of the regular polygon slideway; A plurality of opening control valves are all clamped between the first cage and the second cage. On the front and back surfaces of the opening control valve, a first slider and a second slider are respectively fixedly arranged. The first slider is slidably arranged in the regular polygon slideway, and the second slider is slidably arranged in the guiding inclined slideway; The driving module is used to drive the first cage to rotate relative to the second cage; The airway breathing state determination module is used to obtain the breathing airflow data in the airway through the differential airflow sensor and determine the time period at the end of exhalation or the end of inhalation; the breathing airflow data includes airway pressure data and / or gas flow rate data; The wiping driving control module is used to control the movement of the driving module during the time period at the end of exhalation or the end of inhalation, so as to drive the surface of the opening control valve to rub against the moisture-absorbing layer composed of the moisture-absorbing material.

[0007] Furthermore, the artificial nose control system further includes: an airway expectoration state determination module and a sputum guiding driving control module; the airway expectoration state determination module is communicatively connected to the differential airflow sensor; the sputum guiding driving control module is communicatively connected to the airway opening control module; The airway expectoration state determination module is used to obtain the breathing airflow data in the airway through the differential airflow sensor in real time and determine the expectoration time period; The sputum guiding driving control module is used to control the movement of the driving module before the start moment of the expectoration time period, so as to drive the opening control valve to fully open; The sputum guiding driving control module is further used to control the movement of the driving module after the end moment of the expectoration time period, so as to drive the opening control valve to return to the target opening position.

[0008] Furthermore, the airway breathing state determination module is used to obtain the breathing characteristic value of the user; the breathing characteristic value includes the breathing cycle and the airway pressure change curve and / or the airway gas flow rate change curve during breathing; determine the time period at the end of exhalation or the end of inhalation according to the breathing characteristic value; The airway expectoration state determination module is used to obtain the expectoration characteristic value of the user; the expectoration characteristic value includes the expectoration duration, the airway pressure change curve and / or the airway gas flow rate change curve during expectoration; Based on the airway pressure change curve during expectoration and / or the airway gas flow rate change curve during expectoration, an initial expectoration determination curve is determined; Based on the expectoration duration and the initial expectoration determination curve, the expectoration period is determined.

[0009] Furthermore, the first air flow probe and the second air flow probe are fixedly arranged on the main housing and / or the heat and moisture exchange and filtration module, and the detection parts of the first air flow probe and the second air flow probe are located at different heights in the airway passage; Wiping channels are provided on the surfaces of the first retainer and the second retainer close to the opening control flap; The wiping channels are filled with a moisture-absorbing layer composed of a moisture-absorbing material.

[0010] Furthermore, the opening control flap is made of a ceramic composite material.

[0011] Furthermore, a part of the surface of the opening control flap close to the first retainer is set as a diversion inclined surface, and the height of the diversion inclined surface close to the tip of the opening control flap is greater than the height of the diversion inclined surface close to the tail end of the opening control flap.

[0012] Furthermore, a diversion plate is provided on the surface of the opening control flap close to the second retainer; The first air flow probe and the second air flow probe are fixedly arranged on the diversion plate, and the detection parts of the first air flow probe and the second air flow probe are located at different heights in the airway passage; Wiping channels are provided on the surfaces of the first retainer and the second retainer close to the opening control flap; The wiping channels are filled with a moisture-absorbing layer composed of a moisture-absorbing material.

[0013] Furthermore, a liquid collecting groove is provided at the part where the diversion plate is connected to the opening control flap; A liquid guiding flow channel is further provided in the opening control flap. One end of the liquid guiding flow channel communicates with the liquid collecting groove, and one end of the liquid guiding flow channel is opened in the surface area of the opening control flap in contact with the moisture-absorbing layer composed of the moisture-absorbing material on the first retainer.

[0014] Furthermore, it further includes: A temperature and humidity sensor and an oxygen partial pressure sensor, The temperature and humidity sensor and the oxygen partial pressure sensor are both arranged inside the main housing. The temperature and humidity sensor is used to detect the temperature and humidity of the airway passage gas, and the oxygen partial pressure sensor is used to detect the oxygen content of the airway passage gas.

[0015] Furthermore, a plurality of elastic valve sheets are connected in the airway through hole of the main housing; an auxiliary gas channel is provided on the side wall of the main housing.

[0016] The technical solution of the present invention has at least the following beneficial effects: The airway opening degree control module in the intelligent artificial nose of the present invention can drive the first cage to rotate relative to the second cage by a corresponding amplitude through the driving module, thereby driving a plurality of opening degree control valves to gather or disperse. Thus, when the intelligent artificial nose of the present invention is installed on an endotracheal tube, the opening degree of the airway can be accurately controlled through the airway opening degree control module.

[0017] At the same time, a differential airflow sensor is also provided in the present invention to obtain some breathing data of the user, including but not limited to parameters such as inspiratory flow rate, expiratory flow rate, tidal volume, respiratory rhythm, and respiratory frequency. Moreover, the present invention can also combine other physiological indicators of the user monitored by other devices (such as a ventilator) and medical experience, and through an intelligent algorithm, adjust the opening amount of the airway opening degree control module. Furthermore, automatic control of the airway opening degree can be achieved to realize automatic adaptive adjustment of the simulated T-tube resistance, so as to reduce the consumption of manpower and material resources in the traditional T-tube weaning test and improve the timeliness and success rate. BRIEF DESCRIPTION OF THE DRAWINGS

[0018] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings required for the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative efforts.

[0019] Figure 1 It is a schematic diagram of the overall structure of the artificial nose in an embodiment of the present application; Figure 2 It is a schematic diagram of the disassembled structure of the artificial nose in another embodiment of the present application; Figure 3 It is a schematic diagram of the structure of the second cage in another embodiment of the present application; Figure 4 It is a schematic diagram of the structure of the opening degree control valve in another embodiment of the present application; Figure 5 It is a schematic diagram of the structure of the airway opening degree control module (without a deflector) in another embodiment of the present application; Figure 6 It is a schematic diagram of the structure of the airway opening degree control module (when the deflector is completely closed) in another embodiment of the present application; Figure 7 It is a schematic diagram of the structure of the airway opening degree control module (when the deflector is opened) in another embodiment of the present application; Figure 8 It is a schematic diagram of the execution method flow structure of the airway breathing state determination module in another embodiment of the present application; Figure 9 Schematic structural diagram of the execution method flow of the airway expectoration state determination module in another embodiment of the present application; Figure 10 Schematic block diagram of the structure of an artificial nose control system in another embodiment of the present application; Figure 11 Schematic diagram of the Flow waveform (flow waveform) and Paw waveform (airway pressure waveform) under the normal breathing state of the patient; Figure 12 Schematic diagram of the Flow waveform (flow waveform) and Paw waveform (airway pressure waveform) under the expectoration state of the patient (the part boxed by the wireframe in the figure).

[0020] Reference numerals 1, main housing; 10, auxiliary gas channel; 11, elastic valve plate; 2, heat and moisture exchange and filtration module; 31, first holder; 310, regular polygon slideway; 311, wiping channel; 312, gear teeth; 32, second holder; 321, guiding inclined slideway; 33, opening control flap; 331, first slider; 332, second slider; 333, flow deflector; 334, liquid collection tank; 335, liquid guiding flow channel; 34, micro servo motor; 35, driving gear; 4, placement hole; 5, airway through hole. Detailed implementation manners

[0021] The embodiments of the present invention will be described in detail below with reference to the accompanying drawings.

[0022] It should be noted that, without conflict, the following embodiments and the features in the embodiments may be combined with each other; and, based on the embodiments in the present disclosure, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the scope of protection of the present disclosure.

[0023] It should be noted that the following description relates to various aspects of embodiments within the scope of the appended claims. It should be apparent that the aspects described herein may be embodied in a wide variety of forms, and any specific structure and / or function described herein is illustrative only. Based on the present disclosure, those skilled in the art should understand that one aspect described herein may be implemented independently of any other aspect, and two or more of these aspects may be combined in various ways. For example, any number of the aspects described herein may be used to implement the device and / or practice the method. Additionally, this device and / or this method may be implemented using other structures and / or functions in addition to one or more of the aspects described herein.

[0024] As an embodiment of the present invention, as Figure 10As shown in the figure, a control system for an artificial nose is provided, including: an artificial nose, an airway breathing state determination module, and a wiping drive control module; As Figures 1 - 5 shown in the figure, the artificial nose includes: a main housing 1, a heat and moisture exchange and filtration module 2, an airway opening control module, and a differential air flow sensor.

[0025] The differential air flow sensor is used to obtain some respiratory data of the user, such as parameters like respiratory cycle, tidal volume, respiratory rate, etc. The airway breathing state determination module is communicatively connected to the differential air flow sensor. The wiping drive control module is communicatively connected to the airway opening control module.

[0026] The airway breathing state determination module is used to obtain the respiratory air flow data in the airway through the differential air flow sensor and determine the time period at the end of exhalation or the end of inhalation; the respiratory air flow data includes airway pressure data and / or gas flow rate data.

[0027] The wiping drive control module is used to control the movement of the drive module during the time period at the end of exhalation or the end of inhalation, so as to drive the surface of the opening control flap 33 to rub against the moisture-absorbing layer composed of the moisture-absorbing material.

[0028] Through the cooperation of the airway breathing state determination module and the wiping drive control module, the condensed water in the artificial nose can be removed. In this embodiment, accurately determining the time period at the end of exhalation or the end of inhalation is the key to precisely removing the condensed water and minimizing the impact on the user's breathing when wiping the condensed water.

[0029] Specifically, as Figure 8 shown in the figure, the time period at the end of exhalation or the end of inhalation is determined by the airway breathing state determination module, and the airway breathing state determination module is used to perform the following steps: W100: Obtain the respiratory characteristic values of the user; the respiratory characteristic values include the respiratory cycle and the change curve of airway pressure during respiration and / or the change curve of airway gas flow rate during respiration.

[0030] W200: Determine the time period at the end of exhalation or the end of inhalation according to the respiratory characteristic values.

[0031] Generally, a person's breathing has a certain pattern, and correspondingly, the change in the flow rate or pressure of the air flow detected by the differential air flow sensor in the airway also has a certain repetitive pattern.

[0032] Specifically: at the initial stage of inhalation, the pressure in the lungs is lower than the atmospheric pressure, the airway pressure is lower than the atmospheric pressure, and the air flow rapidly enters the lungs; at the end of inhalation, as the pressure in the lungs rises, the air flow gradually slows down until it stops, and the pressure in the airway gradually approaches the atmospheric pressure or even becomes the same as the atmospheric pressure.

[0033] At the beginning of exhalation, the pressure in the lungs is higher than the atmospheric pressure, and the airflow actively and rapidly flows out, with the airway pressure higher than the atmospheric pressure; at the end of exhalation, the pressure in the lungs drops to equal the atmospheric pressure, the airflow gradually slows down until it stops, and the pressure in the airway also gradually approaches the atmospheric pressure or even becomes the same as the atmospheric pressure.

[0034] Based on the above characteristics, the changes in the airway pressure data and / or gas flow rate data obtained by the differential airflow sensor also conform to the above characteristics. And this pattern usually remains stable over a relatively long period of time.

[0035] Therefore, the current breathing characteristics of the user, that is, the airway pressure and / or airway flow rate curve, can be obtained first through the differential airflow sensor. Based on these curves, the breathing cycle can be determined, and the time period corresponding to the part where the airway pressure data or gas flow rate data changes relatively slowly in the breathing cycle can be determined as the end of exhalation or the end of inhalation. During this time period, the breathing action of the human body almost stops. Therefore, at this time, controlling the opening and closing of the opening control flap 33 in a large amplitude will hardly cause resistance to the normal breathing of the human body. So during this time period, the opening control flap 33 can be moved in a large amplitude at least once, so that the moisture absorption layer can quickly dry the condensed water generated by the opening control flap 33.

[0036] During actual use, the curve in each breathing cycle can be used as a comparison feature. As long as the coincidence degree between the currently detected curve before the end of exhalation or the end of inhalation and the corresponding part of the curve in the previously obtained breathing cycle is greater than the threshold (such as 90%), the time period of the end of exhalation or the end of inhalation in the breathing cycle can be used to determine the current time period of the end of exhalation or the end of inhalation.

[0037] In addition, observing the user's sputum expectoration situation can help medical staff evaluate the user's respiratory tract condition and the effectiveness of the cough reflex, which is important information for deciding whether to continue or interrupt the T-tube weaning test and evaluating the user's overall rehabilitation situation. Therefore, users are often encouraged to expectorate sputum during the T-tube weaning experiment. However, if the sputum expectoration is successful, it often causes the sputum to spray and stick to the end of the opening control flap 33. This will cause pollution and is not conducive to subsequent use. So to overcome this problem, the artificial nose control system also includes: an airway sputum expectoration state determination module and a sputum guiding drive control module; the airway sputum expectoration state determination module is communicatively connected to the differential airflow sensor; the sputum guiding drive control module is communicatively connected to the airway opening control module.

[0038] The airway sputum expectoration state determination module is used to obtain the respiratory airflow data in the airway in real time through the differential airflow sensor and determine the sputum expectoration time period; The sputum guiding drive control module is used to control the movement of the drive module before the start time of the sputum expectoration time period to drive the opening control flap to open completely; The phlegm guiding drive control module is further configured to control the movement of the drive module after the end of the phlegm coughing period, so as to drive the opening control flap to return to the target opening position.

[0039] Through the cooperation of the airway phlegm coughing state determination module and the phlegm guiding drive control module, artificial nose can smoothly guide phlegm. In this embodiment, accurately determining the phlegm coughing period is the key to smoothly guiding phlegm.

[0040] Specifically, as Figure 9 shown, the phlegm coughing period is determined by the airway phlegm coughing state determination module, and the airway phlegm coughing state determination module is executed according to the following method: S100: Obtain the phlegm coughing characteristic values of the user; the phlegm coughing characteristic values include the phlegm coughing duration, the airway pressure change curve and / or the airway gas flow rate change curve during phlegm coughing.

[0041] Generally, a person's breathing has a certain pattern, and correspondingly, when coughing phlegm, the airflow in the respiratory tract will also have a certain pattern. Specifically, for patients with T-tube intubation, as Figure 11 and Figure 12 shown. The change rules of the airflow and air pressure in the airway during the phlegm coughing process are as follows: During the whole phlegm coughing process, the airflow experiences a change process from static to accelerating, then to an instant strong jet, and finally returns to calm. The changes of the gas flow rate and air pressure in the airway during this process are quite different from the change rules of the airflow and air pressure in normal ordinary breathing. Specifically, compared with the normal breathing process of the patient, the airflow and air pressure in the airway during phlegm coughing will both quickly rise to the peak value, and the peak value is greater than the peak value in the normal state. For example, the peak pressure of phlegm coughing 49 is greater than the normal peak pressure 25, and the peak flow rate of phlegm coughing 5.98 is greater than the normal peak flow rate 4.2. And after rising to the peak value, it quickly drops to the normal state, that is, the duration of the whole process is shorter than the duration of the normal breathing stage, and the change rate of air pressure and airflow is faster.

[0042] S200: Determine the initial phlegm coughing determination curve according to the airway pressure change curve and / or the airway gas flow rate change curve during phlegm coughing.

[0043] Specifically, since the airway flow rate change and airway pressure change of the same user during phlegm coughing are basically the same, the airway pressure change curve and / or the airway gas flow rate change curve during phlegm coughing of each user can be statistically determined according to the airway pressure change curves and / or the airway gas flow rate change curves during phlegm coughing of the user collected for a long time, as the initial phlegm coughing determination curve. For example, the peak value mean, change period mean and curve change mean of each stage of the curve can be statistically calculated, and the curve can be optimized by these characteristic values, and then an initial phlegm coughing determination curve with higher credibility can be determined.

[0044] S300: Determine the expectoration period according to the expectoration duration and the initial determination curve of expectoration.

[0045] The starting time and the ending time of the expectoration period can be obtained based on the starting time of the change and the time to return to the normal state of the airway pressure change curve and the airway gas flow velocity change curve during expectoration in the initial determination curve, and then the expectoration period can be determined. In actual use, multiple expectoration processes of the patient can be collected in advance, and multiple curve waveforms corresponding to the airway flow velocity and the airway pressure can be obtained. Thus, the starting time and the ending time of each expectoration period can be statistically calculated, and then a more suitable expectoration period can be determined.

[0046] After determining the starting time and the ending time of the expectoration period, the expectoration period of each expectoration can be determined. During this period, the opening control flap 33 is controlled to be fully opened to provide a gas passage with the maximum opening degree, so as to facilitate the smooth ejection of sputum and avoid sticking and contaminating the opening control flap 33. At the same time, the moisture absorption layer can also wipe to remove some foreign matters remaining on the surface of the opening control flap 33 to maintain the cleanliness of the opening control flap 33.

[0047] In actual use, starting from the beginning of each breathing cycle, the coincidence degree between the airway pressure change curve and / or the airway gas flow velocity change curve during expectoration in the currently collected breathing cycle and the initial determination curve of expectoration in this embodiment can be determined. If the coincidence degree is greater than the threshold value (such as 80%), it can be determined that the user is about to expectorate, and the opening control flap of the artificial nose can be moved according to the determined expectoration period.

[0048] Preferably, after S300, the airway expectoration state determination module further executes the following method: S400: If the currently collected airway airflow value is greater than the peak value of the airway flow velocity in the normal breathing stage, obtain the acquisition time t2 of the peak value of the airway flow velocity closest to the current airway flow velocity value in the historical airway flow velocity sequence; S500: If t1 - t2 ≤ T, generate a flap opening instruction to control the opening control flap 33 to be fully opened. T is the duration from the starting time of the expectoration period to the peak of the curve in the initial determination curve of expectoration, as Figure 12 shown; t1 is the current acquisition time.

[0049] In this embodiment, when it is detected that the airway flow velocity value is greater than the peak value of the airway flow velocity in the normal breathing stage, the change duration from the normal airway flow velocity peak value to the current airway flow velocity value is determined. Since the duration of the entire expectoration stage is significantly shorter than the duration of the normal breathing cycle, the current patient's expectoration state can be more accurately determined by further judging the duration.

[0050] In addition, in this embodiment, the sputum expectoration state can be determined before the peak of the initial sputum expectoration determination curve (i.e., the most intense state of sputum expectoration), and thus the opening control valve 33 can be opened earlier. Further, the opening control valve 33 can be arranged above the differential air flow sensor, that is, the differential air flow sensor is arranged on the side closer to the lung, so that the change of the air flow velocity in the airway can be detected earlier to determine the sputum expectoration state earlier.

[0051] The current S400 and S500 are judged based on the characteristic value of the airway flow velocity. Similarly, for the characteristic value of the airway pressure, the judgment methods of S400 and S500 can also be used. The only difference is that the characteristic corresponding to the airway flow velocity is replaced by the characteristic corresponding to the airway air pressure.

[0052] Further, the artificial nose further includes: a temperature and humidity sensor and an oxygen partial pressure sensor.

[0053] Both the temperature and humidity sensor and the oxygen partial pressure sensor are arranged inside the main housing 1. The temperature and humidity sensor is used to detect the temperature and humidity of the gas in the airway passage, and the oxygen partial pressure sensor is used to detect the oxygen content of the gas in the airway passage. Detecting the oxygen partial pressure (Oxygen Partial Pressure, pO2) in the respiratory airflow is an important physiological monitoring index, which can provide information about gas exchange efficiency, respiratory function and systemic oxygenation status.

[0054] The above-mentioned sensors are all used to monitor the user's respiratory function or respiratory state to determine certain relevant real-time physiological indexes of the user for guiding subsequent treatment and operations, such as determining the opening size of the airway opening control module.

[0055] In addition, in order to reduce the influence of the mechanical probes of these sensors on the respiratory resistance of the user, when setting the corresponding probes, it is necessary to try to avoid the probes being located in the airway passage. For example, these sensors can be fixed on the inner cavity wall of the main housing 1, and corresponding accommodation holes are opened on the heat and moisture exchange and filtration module 2 to place the corresponding sensor probes. And on the premise of ensuring the normal operation of the sensors, it is necessary to try to avoid the probes protruding into the gas passage. Correspondingly, the data collected by these sensors can be sent to the corresponding signal processing system for subsequent use through wired or wireless signal transmission methods.

[0056] The heat and moisture exchange and filtration module 2 is fixedly arranged inside the inner chamber of the main housing 1 and is used to maintain the temperature and humidity of the airway.

[0057] The heat and moisture exchange filtration module 2 can be HMEs (Heat and Moisture Exchanger), which is mainly used to assist the function of the respiratory system, especially in cases where external respiratory support is required or after tracheotomy. The basic working principle of HMEs is to recover the heat and moisture in the user's exhaled gas, and then supply the recovered warm and humidified gas to the user during inhalation, so as to achieve the effects of keeping the respiratory tract moist, maintaining an appropriate gas temperature, reducing the risk of infection, and simplifying respiratory management.

[0058] The airway opening control module is connected to the main housing 1 and is used to control the opening degree of the airway.

[0059] The differential airflow sensor includes a first airflow probe and a second airflow probe, and the first airflow probe and the second airflow probe are respectively arranged at different heights in the airway passage.

[0060] The differential airflow sensor in this application can use the differential airflow sensor used in existing ventilators. The differential airflow sensor usually works based on the measurement principle of pressure or flow rate, and monitors the dynamic changes of the airflow by comparing the gas pressure or flow rate at two different points (the detection points corresponding to the first airflow probe and the second airflow probe) in the breathing circuit.

[0061] Specifically, as Figures 1 to 2 shown, the main housing 1 is generally a cylindrical open cavity, and a plurality of elastic valve sheets 11 are connected in the airway through hole 5 at the top end position. The elastic valve sheets 11 can be made of rubber or silica gel, etc. A plurality of elastic valve sheets 11 can be jointly spliced into an operable window that can be opened and closed. When it is necessary to insert other instruments into the airway for inspection, it can enter through this operable window. At this time, the tip of the elastic valve sheet 11 generates a bending deformation, thereby opening the window. When no instrument is inserted, the tip of the elastic valve sheet 11 returns to a straight state to close the operable window. The through hole at the bottom end position of the main housing 1 can be used to connect a tracheal intubation.

[0062] As Figure 2 shown, an auxiliary gas channel 10 is provided on the side wall of the main housing 1, and the auxiliary gas channel 10 communicates with the inner cavity of the main housing 1. The auxiliary gas channel 10 can also be filled with HMEs. The auxiliary gas channel 10 can be used to input oxygen in a T-tube experiment or as an inlet and outlet for respiratory gas.

[0063] Airway through holes 5 are provided on the main housing 1, the heat and moisture exchange filtration module 2, the first holder 31 and the second holder 32, and the plurality of airway through holes 5 are arranged coaxially to form an airway passage. The extending direction of this gas passage can generally be kept basically the same as the extending direction of the user's own airway, so as to facilitate the smooth discharge of sputum when the user expectorates.

[0064] As shown Figures 2 to 5 in the figure, the airway opening degree control module includes: a first cage 31, a second cage 32, a plurality of opening degree control flaps 33 and a driving module.

[0065] A regular polygon slideway 310 is arranged on the first cage 31. As shown Figure 3 in the figure, a plurality of guiding inclined slideways 321 are evenly arranged on the second cage 32. The first cage 31 is rotationally connected to the second cage 32, and each guiding inclined slideway 321 corresponds to one side slideway of the regular polygon slideway 310. The sliding direction of the side slideway is arranged to intersect with the sliding direction of the guiding inclined slideway 321. The number of the opening degree control flaps 33 is the same as the number of sides of the regular polygon slideway 310.

[0066] Generally, as the number of sides of the regular polygon slideway 310 increases, the number of the opening degree control flaps 33 also keeps increasing. Correspondingly, the number of sides of the airway opening formed when the opening degree control flap 33 moves will also increase, making the airway opening closer to a circle with a smooth edge, and the increase amplitude of the opening is more delicate. Thus, the resistance effect of the airway opening edge on the breathing gas can be reduced. However, as the number of sides of the regular polygon slideway 310 increases, the size of the opening degree control flap 33 will gradually decrease, and the slidable stroke of the opening degree control flap 33 will also decrease, which may ultimately affect the size of the airway opening and is also not conducive to the setting of the deflector 333. Therefore, the number of sides of the regular polygon slideway 310 cannot be increased indefinitely. Specifically, the number of sides of the regular polygon slideway 310 can be determined according to the actual usage scenario. Preferably, the regular polygon slideway 310 can be a regular pentagon slideway, a regular hexagon slideway, a regular heptagon slideway or a regular octagon slideway.

[0067] A plurality of opening degree control flaps 33 are all clamped between the first cage 31 and the second cage 32. A first slider 331 and a second slider 332 are respectively and fixedly arranged on the front and back surfaces of the opening degree control flap 33. The first slider 331 is slidably arranged in the side slideway of the regular polygon slideway 310, and the second slider 332 is slidably arranged in the guiding inclined slideway 321.

[0068] As shown Figures 6 to 7 in the figure, since the side slideway and the corresponding guiding inclined slideway 321 are arranged to intersect with each other, when the side slideway and the corresponding guiding inclined slideway 321 move relative to each other, the first slider 331 will reciprocate in the corresponding side slideway, thereby controlling the opening degree of the airway.

[0069] The driving module is used to drive the first cage 31 to rotate relative to the second cage 32.

[0070] As shown Figure 2As shown in the figure, the drive module in this embodiment includes a servo control system, a micro servo motor 34, and a drive gear 35. The drive gear 35 is fixedly connected to the moving end of the micro servo motor 34, and the servo control system is used to control the rotation of the servo motor. At the same time, in order to drive the first cage 31 to rotate relative to the second cage 32, in this embodiment, the first cage 31 is rotatably disposed within the second cage 32, the micro servo motor 34 is fixed on the second cage 32, and at the same time, gear teeth 312 are provided on a part of the edge of the first cage 31, and the gear teeth 312 mesh with the drive gear 35. Thus, driven by the drive gear 35, the first cage 31 can rotate relative to the second cage 32 by a specified amplitude.

[0071] The airway opening degree control module in the artificial nose of this embodiment can drive the first cage 31 to rotate relative to the second cage 32 by a corresponding amplitude through the drive module, thereby driving a plurality of opening degree control valves 33 to gather or disperse. Thus, when the intelligent artificial nose of the present invention is installed on a T-tube or an endotracheal tube, the opening degree of the airway can be accurately controlled through the airway opening degree control module.

[0072] At the same time, a differential airflow sensor is also provided in this embodiment to obtain some respiratory data of the user, such as parameters such as respiratory cycle, tidal volume, and respiratory rate. Moreover, the present invention can also automatically determine the opening amount of the airway opening degree control module in combination with other physiological indicators of the user monitored by other devices (such as a ventilator) and medical experience. Furthermore, the automatic control of the airway opening degree can be realized to realize the automatic adaptive adjustment of the resistance in the breathing passage of the artificial nose, so as to reduce the consumption of manpower and material resources in the weaning trial and improve the timeliness and success rate.

[0073] As another embodiment of the present invention, as Figure 2 shown, the first airflow probe and the second airflow probe are fixedly disposed on the main housing 1 and / or the heat and moisture exchange filter module 2, and the detection parts of the first airflow probe and the second airflow probe are located at different heights in the airway passage.

[0074] Specifically, the first airflow probe and the second airflow probe can be fixed on the inner side wall of the main housing 1 or inserted into the placement holes 4 opened in the heat and moisture exchange filter module 2.

[0075] Wiping channels 311 are provided on the surfaces of the first cage 31 and the second cage 32 close to the side of the opening degree control valve 33.

[0076] The wiping channel 311 is filled with a moisture-absorbing layer made of a moisture-absorbing material. The moisture-absorbing material can be an existing moisture-absorbing material, which can quickly absorb and wipe the condensed water on the surface of the opening control flap 33. Specifically, the moisture-absorbing material can be non-woven fabric with low fiber shedding, super absorbent polymer (SAP), silica gel (the moisture absorption capacity can reach more than 40% of its own weight), activated carbon and other materials.

[0077] In addition, the moisture-absorbing layer can be prepared from a single moisture-absorbing material or a composite layer composed of multiple moisture-absorbing materials. For example, the moisture-absorbing layer can be a silica gel or activated carbon layer and a non-woven fabric layer in sequence from the bottom layer to the top layer. Thus, after the upper non-woven fabric becomes wet by wiping and absorbing moisture, the water will be absorbed by the activated carbon or silica gel in the lower layer, thereby ensuring the dryness of the upper non-woven fabric.

[0078] Since the entire T-tube weaning test usually lasts for a long time and there is no unified standard in the literature, it usually needs to be determined according to the judgment of clinicians and the specific situation of users. Generally speaking, the T-tube weaning test will last for 24 to 48 hours, during which the symptoms and signs of the user are closely monitored. During this process, with the breathing of the user, water vapor is likely to condense on the surface of the opening control flap 33. In order to avoid the formation of condensed water flowing back into the airway and causing discomfort to the user, it is necessary to minimize the generation of condensed water on the surface of the opening control flap 33.

[0079] In this embodiment, by providing wiping channels 311 on the first holder 31 and the second holder 32 and filling them with a moisture-absorbing layer. Thus, driven by the driving module, the opening control flap 33 can be rubbed between the moisture-absorbing layers to wipe the moisture on the surface of the opening control flap 33 in time, thereby reducing the generation of condensed water.

[0080] Preferably, the opening control flap 33 is made of a ceramic composite material. The ceramic composite material contains specially designed composite ceramic components, such as containing alumina, magnesia, silica, fibers (such as carbon fibers, glass fibers), whiskers, particles or other reinforcing phases. After they are combined, they can provide good heat insulation and hydrophobicity, thereby reducing the condensation phenomenon. At the same time, it can also improve the toughness of the ceramic and overcome the brittleness problem of traditional ceramic materials. By using the ceramic composite material to prepare the opening control flap 33, the problem of condensed water condensation on the surface of the opening control flap 33 can be reduced.

[0081] Preferably, a part of the surface of the opening control flap 33 close to the first holder 31 is set as a diversion inclined surface, and the height of the diversion inclined surface close to the tip of the opening control flap 33 is greater than the height of the diversion inclined surface close to the tail end of the opening control flap 33.

[0082] Generally, an included angle of 1-5° can be set between the diversion inclined plane and the tail plane of the opening control flap 33. Thus, even if some condensed water is generated, it will flow to the tail of the opening control flap 33 under the action of the diversion inclined plane. This tail position generally contacts the moisture absorption layer, so that the generated condensed water can be diverted to the moisture absorption layer and absorbed more timely.

[0083] In addition, in order to further prevent the formation of condensed water, an anti-fog spray specially designed for medical equipment can also be sprayed on the surface of the opening control flap 33.

[0084] As another embodiment of the present invention, as Figures 4 to 7 shown, a diversion plate 333 is provided on the surface of the opening control flap 33 close to the second cage 32.

[0085] The first air flow probe and the second air flow probe are fixedly arranged on the diversion plate 333. Specifically, they can be arranged in the placement holes 4 on the diversion plate 333. And the detection parts of the first air flow probe and the second air flow probe are located at different heights in the airway passage.

[0086] Wiping grooves 311 are opened on the surfaces of the first cage 31 and the second cage 32 close to the opening control flap 33. Moisture absorption layers made of moisture absorption materials are filled in the wiping grooves 311.

[0087] Furthermore, a liquid collecting groove 334 is opened at the part where the diversion plate 333 is connected to the opening control flap 33. A liquid guiding flow channel 335 is also arranged in the opening control flap 33. One end of the liquid guiding flow channel 335 communicates with the liquid collecting groove 334, and one end of the liquid guiding flow channel 335 is opened in the surface area of the opening control flap 33 that contacts the moisture absorption layer made of moisture absorption material on the first cage 31.

[0088] Generally, the size of the airway opening enclosed by the opening control flap 33 is smaller than the size of the airway through hole 5 provided by the main housing 1 and the heat and moisture exchange filter module 2. Thus, when the user's breathing gas reaches spaces of different sizes, the air flow itself will change. In this embodiment, when the gas reaches the airway through hole 5 provided by the main housing 1 and the heat and moisture exchange filter module 2, the air flow velocity will decrease due to the sudden increase in space. Moreover, due to the influence of the disease, the air flow velocity of the user's spontaneous breathing may not be strong. Therefore, if the first air flow probe and the second air flow probe are arranged in the main housing 1 and / or the heat and moisture exchange filter module 2, the detection progress will be reduced. In order to be able to detect the user's breathing data more accurately and sensitively, in this embodiment, the first air flow probe and the second air flow probe are fixedly arranged on the diversion plate 333. Since the size of the channel enclosed by multiple diversion plates 333 is basically the same as the size of the airway opening enclosed by the opening control flap 33. Therefore, the detection accuracy of the sensor can be improved.

[0089] In addition, in this embodiment, a liquid collecting tank 334 and a liquid guiding channel 335 are also provided to timely guide the condensed water generated on the deflector 333 to the moisture absorption layer. Thus, the problem of the deflector 333 generating condensed water can be better solved.

[0090] The above is only the specific implementation manner of the present invention, but the protection scope of the present invention is not limited thereto. Any changes or substitutions that can be easily thought of by those skilled in the art within the technical scope disclosed by the present invention should be covered by the protection scope of the present invention. Therefore, the protection scope of the present invention shall be subject to the protection scope of the claims.

Claims

1. An artificial nose control system, characterized in that: include: Artificial nose, airway breathing state determination module and wiping drive control module; The artificial nose comprises: a main shell, a heat and moisture exchange filter module, an airway opening control module and a differential airflow sensor; the airway breathing state determination module is communicatively connected with the differential airflow sensor; the wiping drive control module is communicatively connected with the airway opening control module; The heat and moisture exchange filter module is fixedly disposed in the internal chamber of the main housing to maintain the temperature and humidity of the airway; The airway opening control module is connected to the main housing and is used to control the opening degree of the airway; The differential airflow sensor comprises a first airflow probe and a second airflow probe, wherein the first airflow probe and the second airflow probe are respectively arranged at positions of different heights in the airway passage; The main housing, the heat and moisture exchange filter module, the first holder and the second holder are all provided with airway through holes, and a plurality of the airway through holes are coaxially arranged to form the airway passage; The airway opening control module comprises: A first retaining frame, a second retaining frame, a plurality of opening control valves and a driving module; The first retaining frame is provided with a regular polygonal slideway, and the second retaining frame is evenly provided with a plurality of guide inclined slideways, the first retaining frame is rotatably connected with the second retaining frame, and each of the guide inclined slideways corresponds to a side slideway in the regular polygonal slideway; the sliding direction of the side slideway and the sliding direction of the guide inclined slideway are arranged to intersect with each other; the number of the opening control valves is the same as the number of sides of the regular polygonal slideway; The plurality of opening control valves are all sandwiched between the first retaining frame and the second retaining frame, and a first slider and a second slider are fixedly arranged on the front and back surfaces of the opening control valve, respectively, the first slider is slidably arranged in the regular polygonal slideway, and the second slider is slidably arranged in the guide inclined slideway; The driving module is used to drive the first holding frame to rotate relative to the second holding frame; The airway breathing state determination module is used to obtain the breathing airflow data in the airway through the differential airflow sensor to determine the time period at the end of exhalation or end of inspiration; the breathing airflow data includes airway pressure data and / or gas flow rate data; The wiping drive control module is used to control the movement of the drive module during the period at the end of exhalation or inhalation, so as to drive the surface of the opening control valve to rub against the hygroscopic layer composed of hygroscopic material.

2. An artificial nose control system according to claim 1, characterized in that: Also includes: An airway expectoration state determination module and an expectoration drive control module; the airway expectoration state determination module is communicatively connected to the differential airflow sensor; the expectoration drive control module is communicatively connected to the airway opening control module; The airway expectoration state determination module is used to obtain the respiratory airflow data in the airway in real time through the differential airflow sensor to determine the expectoration period; The sputum guiding drive control module is used to control the movement of the drive module before the start time of the sputum coughing period to drive the opening control valve to fully open; The sputum guiding drive control module is also used to control the movement of the drive module after the sputum coughing period ends, so as to drive the opening control valve to return to the target opening position.

3. An artificial nose control system according to claim 2, characterized in that: The airway breathing state determination module is used to Acquire a user's breathing characteristic value; the breathing characteristic value includes a breathing cycle and a breath-to-breath airway pressure change curve and / or a breath-to-breath airway gas flow rate change curve; Determining the time period at the end of exhalation or inhalation according to the respiratory characteristic value; The airway expectoration state determination module is used to Acquire a cough characteristic value of the user; the cough characteristic value includes a duration of coughing, an airway pressure change curve between coughs, and / or an airway gas flow rate change curve between coughs; Determine an initial sputum determination curve according to a sputum airway pressure change curve and / or a sputum airway gas flow rate change curve; Determining the expectoration period according to the expectoration duration and the expectoration initial determination curve; If the currently acquired airway flow velocity value is greater than the peak airway flow velocity value in the normal breathing stage, then the acquisition time t2 of the peak airway flow velocity value closest to the current airway flow velocity value in the historical airway flow velocity sequence is obtained; If t1-t2≤T, a valve opening instruction is generated to control the opening degree so that the valve is fully opened; T is the time from the start of the sputum period to the peak of the curve in the initial sputum determination curve; t1 is the current acquisition time.

4. An artificial nose control system according to claim 1, characterized in that: The first airflow probe and the second airflow probe are fixedly arranged on the main housing and / or the heat and moisture exchange filter module, and the detection parts of the first airflow probe and the second airflow probe are located at different heights in the airway passage; The first retainer and the second retainer are provided with wiping grooves on their surfaces close to the opening control valve; The wiping channel is filled with a moisture absorbing layer made of a moisture absorbing material.

5. An artificial nose control system according to claim 4, characterized in that: The opening control valve is made of ceramic composite material.

6. An artificial nose control system according to claim 4, characterized in that: A partial surface of the opening control flap close to the first retaining frame is set as a guide slope, and the height of the guide slope close to the tip of the opening control flap is greater than the height of the guide slope close to the tail end of the opening control flap.

7. An artificial nose control system according to claim 1, characterized in that: A guide plate is provided on the surface of the opening control valve on the side close to the second retainer; The first airflow probe and the second airflow probe are fixedly arranged on the guide plate, and the detection parts of the first airflow probe and the second airflow probe are located at different heights in the airway passage; The first retainer and the second retainer are provided with wiping grooves on their surfaces close to the opening control valve; The wiping channel is filled with a moisture absorbing layer made of a moisture absorbing material.

8. An artificial nose control system according to claim 7, characterized in that: A liquid collecting groove is provided at the portion where the guide plate is connected to the opening control valve; A liquid conducting channel is also provided in the opening control valve, one end of which is connected to the liquid collecting tank, and one end of which is opened in a surface area of ​​the opening control valve that contacts the hygroscopic layer formed of hygroscopic material on the first retaining frame.

9. An artificial nose control system according to claim 4, characterized in that: Also includes: Temperature and humidity sensor and oxygen partial pressure sensor, The temperature and humidity sensor and the oxygen partial pressure sensor are both arranged inside the main shell. The temperature and humidity sensor is used to detect the temperature and humidity of the air in the airway passage, and the oxygen partial pressure sensor is used to detect the oxygen content of the air in the airway passage.

10. An artificial nose control system according to claim 4, characterized in that: A plurality of elastic valve sheets are connected to the air passage holes of the main shell; and an auxiliary gas passage is arranged on the side wall of the main shell.

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