Breathing following atomization method and system based on temperature detection and atomizer

Abstract

The invention discloses a breathing following atomization control method based on temperature detection. The method comprises the following steps: acquiring temperature data when a user breathes in real time; calculating characteristic parameters related to the breathing characteristics of the user based on the temperature data, wherein the characteristic parameters comprise the breathing frequency and the temperature change slope; and controlling an atomization driving circuit to start and stop along with breathing of the user according to the breathing frequency and the temperature change slope. The breathing temperature of a user is detected through the temperature sensor, the real-time breathing frequency and the temperature change slope are calculated through data analysis of software according to the temperature numerical value change, fog is emitted and stopped along with breathing intelligently according to the calculated breathing frequency and the calculated temperature change slope, and the effects that fog is emitted during inspiration and fog is stopped during expiration are achieved; finally, the total liquid medicine utilization rate is increased, and the cost is saved.

Description

Technical Field

[0001] The present invention relates to the technical field of nebulizers, and in particular to a breathing-following nebulization method, system and nebulizer based on temperature detection. Background Art

[0002] The nebulizer can atomize the liquid medicine into tiny particles, and the medicine enters the user's respiratory tract and lungs through inhalation and is deposited. After the nebulizer is turned on, the atomizer is in a continuous working state to ensure continuous delivery of liquid medicine to the user. This continuous delivery ensures that the user can inhale the liquid medicine at any time, but there is also a defect of waste of liquid medicine: the user cannot inhale the liquid medicine when exhaling, resulting in waste of liquid medicine.

[0003] However, if the breathing detection technology is used to detect the user's breathing condition and the intermittent operation of the atomizer is controlled according to the breathing condition to improve the utilization rate of the liquid medicine, there are the following difficulties:

[0004] Existing breathing detection technologies usually use devices such as airflow sensors, chest straps or oxygen concentration sensors to monitor breathing. Although these technologies have a certain degree of accuracy, they have certain shortcomings. First, airflow sensors and chest strap devices usually need to come into contact with the human body, which is not suitable for long-term wear and will cause discomfort to users. Secondly, complex sensor systems may have high cost and power consumption issues, which are limited in portability and long-term use scenarios. Furthermore, airflow sensors are easily affected by external interference when detecting breathing, and the measurement accuracy and stability need to be improved.

[0005] Therefore, how to solve the above-mentioned deficiencies in the prior art has become a subject to be studied and solved by the present invention. Summary of the invention

[0006] During the breathing process, the temperature of the gas exhaled by the human body is higher, and the temperature is lower during inhalation. The temperature change of breathing is closely related to the breathing rhythm. By collecting the temperature fluctuation of the user's exhaled breath in a contactless manner, combining temperature sensors with data processing technology, real-time and accurate monitoring of physiological parameters such as respiratory frequency and breathing depth can be achieved. Therefore, monitoring the breathing process using a temperature sensor is a potential technical solution that can overcome the shortcomings of the prior art and provide a more comfortable and convenient breathing monitoring solution. Based on this, the purpose of the present invention is to provide a breathing-following atomization method, system and atomizer based on temperature detection.

[0007] In order to achieve the above object, the technical solution adopted by the present invention is:

[0008] The first aspect of the present invention provides a breathing-following atomization control method based on temperature detection, comprising:

[0009] Get real-time temperature data of the user's breathing;

[0010] Calculating characteristic parameters related to the user's breathing characteristics based on the temperature data, the characteristic parameters including breathing frequency and temperature change slope;

[0011] The atomization driving circuit is controlled to start and stop following the user's breathing according to the breathing frequency and the temperature change slope.

[0012] Preferably, the characteristic parameters are updated in real time, and the atomization drive circuit is controlled to start and stop following the user's breathing according to the current breathing frequency and the temperature change slope.

[0013] Preferably, the method of controlling the atomization drive circuit to start and stop following the user's breathing according to the breathing frequency and the temperature change slope includes:

[0014] Controlling the interval between stopping and starting the atomization drive circuit according to the breathing frequency;

[0015] The time nodes of stopping and starting the atomization driving circuit are controlled according to the temperature change slope.

[0016] Further preferably, the method for controlling the time nodes of stopping and starting the atomization drive circuit according to the temperature change slope includes:

[0017] If the current temperature change slope is positive and greater than the temperature change slope threshold in the exhalation mode, it is determined that the user is in the exhalation mode, and the atomization drive circuit is controlled to stop;

[0018] If the current temperature change slope is a negative value and is less than the temperature change slope threshold in the inhalation mode, it is determined that the user is in the inhalation mode, and the atomization drive circuit is controlled to start.

[0019] Further preferably, the method for controlling the time nodes of stopping and starting the atomization driving circuit according to the temperature change slope further comprises: controlling the atomization driving circuit to stop or start in advance based on the atomization sensitivity;

[0020] Calculate and adjust the temperature change slope threshold based on the atomization sensitivity to obtain the early braking stop threshold in the exhalation mode and the early braking start threshold in the inhalation mode;

[0021] When the temperature change slope is equal to the early braking stop threshold, the atomization drive circuit is controlled to stop;

[0022] When the current temperature change slope is equal to the early braking start threshold, the atomization drive circuit is controlled to start.

[0023] Preferably, the characteristic parameter also includes breathing depth, and the atomization power output by the atomization drive circuit is controlled according to the breathing depth to adjust the atomization rate.

[0024] Further preferably, the method for calculating the respiratory frequency and the respiratory depth includes: extracting a peak value or a valley value in the temperature data within at least two consecutive respiratory events, and calculating the respiratory frequency and the respiratory depth based on the peak value or the valley value.

[0025] Preferably, the temperature data is generated by converting a temperature signal collected by a temperature sensor, and the temperature signal is a low-frequency temperature signal within the frequency band of the user's breathing rhythm after filtering and denoising.

[0026] Further preferably, the filtering method comprises:

[0027] Using a low-pass filter to remove high-frequency noise in the respiratory temperature signal;

[0028] A bandpass filter was used to remove signals outside the respiratory rhythm frequency band.

[0029] Further preferably, the denoising method comprises:

[0030] reducing fluctuations in the respiratory temperature signal by a smoothing algorithm;

[0031] Artifacts not related to normal breathing are identified and removed through an oversampling algorithm.

[0032] Preferably, the atomization control method further comprises performing abnormal breathing monitoring based on the temperature change slope and a preset abnormal threshold:

[0033] Adjusting the current temperature change slope according to the influence coefficient of temperature change on respiratory characteristics to obtain a slope correction value;

[0034] The slope correction value is compared with the abnormal threshold value, and when the slope correction value is lower than the abnormal threshold value, it is determined that the breathing is abnormal.

[0035] A second aspect of the present invention provides an atomization control system, including a controller for implementing the above-mentioned atomization control method, and also including a temperature sensor for real-time acquisition of temperature data of the user's breathing, wherein the temperature sensor is electrically connected to the controller for outputting the temperature data to the controller.

[0036] The third aspect of the present invention provides a nebulizer, comprising a main unit, a medicine cup, a nebulizer sheet assembly, a mist outlet, a user inhalation end and the above-mentioned nebulizer control system;

[0037] The medicine cup is arranged on the top of the main unit, and the mouth of the medicine cup, the mist outlet and the user inhalation end are assembled in sequence;

[0038] The atomizing sheet assembly is arranged in a medicine liquid output channel formed by assembling the medicine cup and the mist outlet;

[0039] The temperature sensor is arranged in a mist outlet channel formed by assembling the mist outlet and the user inhalation end, and is electrically connected to the controller via a connector.

[0040] Preferably, the connector comprises a first contact and a first probe;

[0041] The first contact is electrically connected to the temperature sensor via a wire, and both are arranged at the mist outlet or the user inhalation end;

[0042] The first probe is disposed on the medicine cup or the host and is electrically connected to the controller;

[0043] When the mist outlet or the user inhalation end is assembled, the first contact is directly or indirectly connected to the first probe, so that the temperature sensor and the controller are electrically connected.

[0044] Further preferably, when the temperature sensor is arranged in the outlet of the mist outlet, the first contact is arranged in the inlet of the mist outlet and is indirectly connected to the first probe;

[0045] The atomizer sheet assembly has a conductive plate, the conductive plate is electrically connected to a second probe disposed at the mouth of the medicine cup, the second probe is connected to an atomizer drive circuit, and the atomizer drive circuit is electrically connected to a controller;

[0046] When the mist outlet is assembled with the medicine cup, the first contact is in contact with and connected to one side of the conductive plate, and the first probe and the second probe are in contact with and connected to the other side of the conductive plate.

[0047] Further preferably, when the temperature sensor is arranged in the user inhalation end, the first contact is arranged at the edge of the assembly end of the user inhalation end, and when the user inhalation end is assembled with the medicine cup, the first contact is directly contacted and connected with the first probe.

[0048] Further preferably, the first probe is arranged at the outer edge of the mouth of the medicine cup, and the mist outlet is provided with a through hole for passing the first probe or the first contact.

[0049] The working principle and advantages of the present invention are as follows:

[0050] The present invention utilizes a temperature sensor to detect the user's breathing temperature. The temperature value change is analyzed by software to calculate the real-time breathing frequency and the temperature change slope. The mist is emitted and stopped according to the calculated breathing frequency and temperature change slope, thereby achieving the effect of emitting mist when inhaling and stopping mist when exhaling, and ultimately achieving the improvement of the overall utilization rate of the medicine solution and saving costs.

[0051] The present invention arranges the temperature sensor at the mist outlet of the atomizer, in the mask or the mouthpiece. When the user exhales, air flows through the surface. The optimal installation position makes the detected temperature more accurate and makes it easier to identify the temperature characteristics of exhalation and inhalation, thereby making the detection more accurate.

[0052] The present invention can achieve breathing follow-up adjustment by updating breathing parameters in real time, so that the breathing follow-up atomization effect is better, the user comfort is better, and it is particularly suitable for use in scenarios requiring rapid response such as medical monitoring.

[0053] The present invention adjusts the atomization state by following the breathing, so that the atomizer has low power consumption and is suitable for long-term use.

[0054] The present invention can set different atomization rates according to different breathing depths, thereby improving the utilization rate of the medicine. BRIEF DESCRIPTION OF THE DRAWINGS

[0055] Attached Figure 1 This is an axonometric view of the atomizer of Example 1 of the present invention when the user inhalation end is not installed;

[0056] Attached Figure 2 For the present invention Figure 1 Sectional drawing;

[0057] Attached Figure 3 This is an exploded view of the installation of the atomizer assembly of Example 1 of the present invention;

[0058] Attached Figure 4 This is a right isometric exploded view of the installation of the atomizer assembly of Example 1 of the present invention;

[0059] Attached Figure 5 This is a left isometric exploded view of the installation of the atomizer assembly of Example 1 of the present invention;

[0060] Attached Figure 6 This is an axonometric view of the mist outlet of Example 1 of the present invention;

[0061] Attached Figure 7 This is a cross-sectional view of the mist outlet of Example 1 of the present invention;

[0062] Attached Figure 8 This is an axonometric view of the atomizer of Example 2 of the present invention when it is installed in a mask;

[0063] Attached Fig. 9 It is a left side view of the mask of embodiment 2 of the present invention;

[0064] Attached Fig.10 This is an axonometric view of the atomizer of Example 2 of the present invention when it is not installed in the mask;

[0065] Attached Fig.11 It is a left side view of the nozzle attachment of Example 3 of the present invention;

[0066] Attached Fig.12 is a flow chart of the method of embodiment 1 of the present invention;

[0067] Attached Fig.13 This is a temperature waveform diagram of Example 1 of the present invention.

[0068] In the above figures: 1 main unit; 2 medicine cup; 3 atomizer assembly; 4 mist outlet; 41 through hole; 5 sealing ring; 51 perforation; 6 controller; 7 temperature sensor; 8 first contact; 9 first probe; 10 conductive plate; 11 second probe; 12 mask; 13 mouthpiece. DETAILED DESCRIPTION

[0069] The present invention will be further described below in conjunction with the accompanying drawings and embodiments:

[0070] Embodiment: The present invention will be clearly described below with diagrams and detailed descriptions. After understanding the embodiments of the present invention, any person skilled in the art can make changes and modifications based on the techniques taught by the present invention without departing from the spirit and scope of the present invention.

[0071] The terms used herein are only for describing specific embodiments and are not intended to be limiting of the present invention. Singular forms such as "a", "this", "here", "this" and "the" as used herein also include plural forms.

[0072] The terms “first”, “second”, etc. used in this document do not specifically refer to an order or sequence, nor are they used to limit the present case. They are only used to distinguish components or operations described with the same technical terms.

[0073] As used herein, “connected” or “positioned” may refer to two or more components or devices being in direct physical contact with each other, or being in indirect physical contact with each other, or may refer to two or more components or devices operating or moving with each other.

[0074] The terms “include,” “including,” “have,” etc. used in this document are open-ended terms, meaning including but not limited to.

[0075] The terms used herein generally have the ordinary meanings of each term used in the art, in the context of the present invention, and in the specific context, unless otherwise noted. Certain terms used to describe the present invention will be discussed below or elsewhere in this specification to provide additional guidance to those skilled in the art regarding the description of the present invention.

[0076] Embodiment 1:

[0077] See attached Fig.12 As shown, the first aspect of this embodiment provides a breathing-following atomization control method based on temperature detection, comprising the following steps:

[0078] Step 1: Start the device and initialize it.

[0079] Step 2: Use the temperature sensor 7 to collect the temperature signal of the user's breathing in real time, convert the temperature signal into temperature data, obtain the temperature data, and obtain the temperature waveform. Fig.13 Since the general breathing frequency is 12-20 times / minute, the sampling rate of the temperature signal can be 50 or 100 times per second, and a time series signal can be formed to ensure that the details of temperature fluctuations can be captured. When collecting the temperature signal, atomization can be turned on or off.

[0080] Since the temperature signal collected by the temperature sensor 7 may contain environmental noise or other interference signals, it may be affected by factors such as external environmental temperature changes and airflow fluctuations in actual breathing scenarios. Therefore, this embodiment filters and denoises the temperature signal to obtain a low-frequency temperature signal within the frequency band of the user's breathing rhythm. Among them:

[0081] The filtering method includes: using a low-pass filter to remove high-frequency noise in the respiratory temperature signal, retaining only the low-frequency part related to the respiratory rhythm; using a band-pass filter to set a specific frequency band range, removing signals outside the respiratory rhythm frequency band range, and retaining only the signal part related to the normal respiratory frequency (for example, 0.1Hz to 1Hz).

[0082] The denoising method includes: reducing the fluctuations in the respiratory temperature signal through a smoothing algorithm (such as sliding average or Kalman filtering), reducing the interference of short-term temperature fluctuations on respiratory detection, making the respiratory waveform smoother, and facilitating subsequent feature extraction; identifying and removing false signals unrelated to normal breathing through an oversampling algorithm to avoid erroneous respiratory cycle detection.

[0083] Step three: Calculate characteristic parameters related to the user's breathing characteristics based on the temperature data, where the characteristic parameters include breathing frequency and temperature change slope.

[0084] The calculation method of temperature change slope S(t) includes:

[0085]

[0086] Among them, t and t+Δt are two time points before and after respectively.

[0087] The method for calculating the respiratory frequency includes: extracting the peak value or valley value in the temperature data within at least two consecutive respiratory events, and locating and extracting the peak value or valley value from the temperature waveform using a threshold comparison method or a derivative-based algorithm. In the temperature waveform, the temperature increases during exhalation and decreases during inhalation. The peak value is the highest point of the temperature waveform, and the valley value is the lowest point of the temperature waveform.

[0088] The respiratory cycle Tcycle is calculated based on the peak value or the valley value, and the respiratory frequency f is calculated according to the respiratory cycle Tcycle;

[0089]

[0090] Among them, t1 is the time when the first respiratory event occurs, tN is the time when the last respiratory event occurs, and the time when the respiratory event occurs is also the time corresponding to the peak or valley value; C is the total number of respiratory events recorded during the monitoring period. To improve the real-time performance of the exhalation cycle, C can be 2, and Tcycle is updated every two respiratory events.

[0091] Since breathing is not completely regular and sometimes abnormal, especially in medical monitoring and other scenarios that require rapid response, the delay of breathing data must be reduced as much as possible. Therefore, the characteristic parameters of this embodiment are updated in real time, and the atomization drive circuit is controlled to start and stop following the user's breathing according to the current breathing frequency and the temperature change slope, thereby achieving breathing follow-up adjustment. For example, to improve the real-time performance of the exhalation cycle, C can be 2, and Tcycle is updated every two breathing events.

[0092] Step 4: Control the atomization drive circuit to start and stop following the user's breathing according to the breathing frequency and the temperature change slope:

[0093] The interval time between stopping and starting the atomization driving circuit is controlled according to the breathing frequency.

[0094] The time nodes of stopping and starting the atomization driving circuit are controlled according to the temperature change slope; specifically:

[0095] The temperature change slope S(t) and the preset slope thresholds in the exhalation and inhalation modes can be used to determine the user's current breathing mode:

[0096] If the current temperature change slope is positive and greater than the temperature change slope threshold ∈1 in the exhalation mode, that is, |S(t)|>∈1 and S(t)>0, it indicates that the temperature rises, and it is determined that the user is in the exhalation mode, and the atomization drive circuit is controlled to stop at this time;

[0097] If the current temperature change slope is a negative value and is less than the temperature change slope threshold ∈2 in the inhalation mode, that is, |S(t)|<∈2 and S(t)<0, it indicates that the temperature has dropped, and it is judged that the user is in the inhalation mode. At this time, the atomization drive circuit is controlled to start.

[0098] In addition, the sensitivity of breathing detection can be adjusted by adjusting ∈1 and ∈2, and different thresholds can be set for different children and adults to improve the accuracy of detection.

[0099] In order to avoid the lag problem between atomization and breathing, the atomization drive circuit is also controlled to stop or start in advance based on the atomization sensitivity, as follows:

[0100] The temperature change slope threshold S(t) is calculated and adjusted based on the sensitivity A1 of atomization stop and the sensitivity A2 of atomization start, so as to obtain the early braking stop threshold W1 in the exhalation mode and the early braking start threshold W2 in the inhalation mode;

[0101] W1=∈1-A1;

[0102] W2=∈2+A2;

[0103] When the temperature change slope S(t) is equal to the early braking stop threshold W1, the atomization drive circuit is controlled to stop atomization before exhalation to avoid a situation where atomization is still occurring after exhalation.

[0104] When the temperature change slope S(t) is equal to the early brake start threshold W2, the atomization drive circuit is controlled to start atomization before inhalation to avoid the situation where atomization has not yet occurred at the beginning of inhalation.

[0105] ∈1, ∈2, W1, W2 are updated every two respiratory events.

[0106] The present atomization control method further includes controlling the atomization power output by the atomization drive circuit based on the breathing depth to adjust the atomization rate.

[0107] The breathing depth ΔT can be estimated by the difference between the maximum exhalation temperature and the minimum inhalation temperature.

[0108] ΔT=Tmax-Tmin

[0109] Wherein, Tmax is the maximum value of exhalation temperature, and Tmin is the minimum value of inhalation temperature.

[0110] The greater the temperature difference, the greater the breathing depth ΔT, which means the deeper the breathing depth.

[0111] Adults usually have a greater breathing depth, and they can usually inhale more gas with each breath. Children usually have a smaller breathing depth, especially infants and young children, who inhale relatively less gas with each breath. According to the breathing depth, we can also adjust the atomization rate of the atomization output to improve the utilization rate of the liquid medicine.

[0112] The atomization control method further includes performing abnormal breathing monitoring based on the temperature change slope S(t) and a preset abnormal threshold r:

[0113] According to the influence coefficient k of temperature change on respiratory characteristics, the current temperature change slope S(t) is adjusted to obtain the slope correction value R. The calculation model is as follows:

[0114] R=k*S(t)+b

[0115] Here, k is a constant that indicates the degree of influence of temperature change on respiratory characteristics.

[0116] b is the baseline value used to adjust the above model to fit a specific individual or condition.

[0117] The slope correction value R is compared with the abnormal threshold value r. When the slope correction value R is lower than the abnormal threshold value r, it is determined that the breathing is abnormal.

[0118] When abnormal breathing is determined, the controller 6 of the nebulizer can control the alarm device to sound an alarm to check whether the user has difficulty breathing or whether the user has taken off the mask or the mouthpiece.

[0119] The second aspect of this embodiment provides an atomization control system, including a controller 6 for implementing the above-mentioned atomization control method, and also including a temperature sensor 7 for real-time acquisition of temperature data of the user's breathing, wherein the temperature sensor 7 is electrically connected to the controller 6 for outputting the temperature data to the controller 6.

[0120] See attached Figure 1-7 As shown, the third aspect of this embodiment provides a nebulizer, which is a mesh nebulizer, including a main unit 1, a medicine cup 2, a nebulizer sheet assembly 3, a mist outlet 4, a user inhalation end and the above-mentioned nebulization control system.

[0121] The medicine cup 2 is arranged on the top of the main unit 1, and the cup mouth of the medicine cup 2, the mist outlet 4 and the user inhalation end are assembled in sequence.

[0122] The atomizer assembly 3 is arranged in a medicine liquid output channel formed by assembling the medicine cup 2 and the mist outlet 4 .

[0123] The temperature sensor 7 is arranged in the mist outlet channel formed by assembling the mist outlet 4 and the user inhalation end, and is electrically connected to the controller 6 via a connector.

[0124] In this embodiment, the temperature sensor 7 can be arranged in the outlet of the mist outlet 4. Figure 7 .

[0125] In this embodiment, the connector includes a first contact 8 and a first probe 9. In other embodiments, the connector may also be a plug.

[0126] The first probe 9 is disposed at the outer edge of the mouth of the medicine cup 2 and does not contact the medicine solution. The first probe 9 is electrically connected to the controller 6 .

[0127] To facilitate connection with the first probe 9, the first contact 8 is disposed in the entrance of the mist outlet 4, and is electrically connected to the temperature sensor 7 via a wire. The first contact 8 is indirectly connected to the first probe 9, so that the temperature sensor 7 and the controller 6 are electrically connected.

[0128] In this embodiment, the atomizer sheet assembly 3 includes a micro-mesh sheet and a piezoelectric ceramic sheet connected to each other, and the surface of the piezoelectric ceramic sheet has a conductive drive layer. The atomizer sheet assembly 3 has a conductive plate 10, which is fixed on the piezoelectric ceramic sheet and connected to the piezoelectric ceramic sheet through the conductive drive layer. The conductive plate 10 is electrically connected to a second probe 11 disposed at the mouth of the medicine cup 2, and the second probe 11 is connected to an atomization drive circuit, and the atomization drive circuit is electrically connected to the controller 6.

[0129] When the mist outlet 4 is assembled with the cup mouth of the medicine cup 2, the atomizer assembly 3 is limited at the cup mouth, and a sealing ring 5 is provided between the mist outlet 4 and the cup mouth. At the same time, the first contact 8 is in contact with and connected to one side of the conductive plate 10, and the first probe 9 and the second probe 11 are in contact with and connected to the other side of the conductive plate 10, thereby realizing the conduction of the atomization circuit and the conduction of the temperature collection circuit.

[0130] The conductive plate 10 is provided with four contacts, two of which are used to connect the second probe 11 , and the other two are used to connect the two first probes 9 and the two first contacts 8 . The two first contacts 8 are fixed on a connecting plate, which is fixed in the mist outlet 4 and can be supported by the groove on the sealing ring 5 .

[0131] Example 2

[0132] See attached Figure 8-10 As shown, this embodiment is basically the same as Embodiment 1, except that:

[0133] The temperature sensor 7 and the first contact 8 are arranged at the user inhalation end, and the user inhalation end is a mask 12 .

[0134] The temperature sensor 7 is preferably arranged on the outlet side of the mask 12, closer to the user's mouth, so that the temperature data is more accurate.

[0135] The first contact 8 is preferably arranged at the entrance side of the mask 12, and is preferably arranged at the edge of the assembly end of the mask 12, so as to be conveniently connected to the first probe 9. The first contact 8 is electrically connected to the temperature sensor 7 through a wire, and the wire can be hidden and buried in the wall of the mask 12.

[0136] The first probe 9 is arranged at the outer edge of the cup mouth of the medicine cup 2, the mist outlet 4 is provided with a through hole 41 for passing the first probe 9 or the first contact 8, and the sealing ring 5 is provided with a through hole 51 for passing the first probe 9 or the first contact 8. In other embodiments, the first probe 9 can also be arranged on the host 1.

[0137] When the mask 12 is assembled with the mist outlet 4 , the first contact 8 is directly connected with the first probe 9 , thereby realizing the conduction of the temperature acquisition circuit.

[0138] In other embodiments, the first contact 8 may also be indirectly connected to the first probe 9 via an intermediate contact, and the intermediate contact may be integrally formed on the mist outlet 4 .

[0139] Example 3

[0140] See attached Fig.11 As shown, this embodiment is basically the same as Embodiment 2, except that the user inhalation end is a mouthpiece 13 .

[0141] The above embodiments are only for illustrating the technical concept and features of the present invention, and their purpose is to enable people familiar with the technology to understand the content of the present invention and implement it accordingly, and they cannot be used to limit the protection scope of the present invention. Any equivalent changes or modifications made according to the spirit of the present invention should be included in the protection scope of the present invention.

Claims

1. A breathing-following atomization control method based on temperature detection, characterized in that: include: Get real-time temperature data of the user's breathing; Calculating characteristic parameters related to the user's breathing characteristics based on the temperature data, the characteristic parameters including breathing frequency and temperature change slope; The atomization driving circuit is controlled to start and stop following the user's breathing according to the breathing frequency and the temperature change slope.

2. A breathing-following atomization control method based on temperature detection according to claim 1, characterized in that: The characteristic parameters are updated in real time, and the atomization drive circuit is controlled to start and stop following the user's breathing according to the current breathing frequency and the temperature change slope.

3. The breathing-following atomization control method based on temperature detection according to claim 1, characterized in that: The method of controlling the atomization drive circuit to start and stop following the user's breathing according to the breathing frequency and the temperature change slope includes: Controlling the interval between stopping and starting the atomization drive circuit according to the breathing frequency; The time nodes of stopping and starting the atomization driving circuit are controlled according to the temperature change slope.

4. The breathing-following atomization control method based on temperature detection according to claim 3, characterized in that: The method for controlling the time nodes of stopping and starting the atomization driving circuit according to the temperature change slope includes: If the current temperature change slope is positive and greater than the temperature change slope threshold in the exhalation mode, it is determined that the user is in the exhalation mode, and the atomization drive circuit is controlled to stop; If the current temperature change slope is a negative value and is less than the temperature change slope threshold in the inhalation mode, it is determined that the user is in the inhalation mode, and the atomization drive circuit is controlled to start.

5. The breathing-following atomization control method based on temperature detection according to claim 4, characterized in that: The method of controlling the time nodes of stopping and starting the atomization driving circuit according to the temperature change slope also includes: controlling the atomization driving circuit to stop or start in advance based on the atomization sensitivity; Calculate and adjust the temperature change slope threshold based on the atomization sensitivity to obtain the early braking stop threshold in the exhalation mode and the early braking start threshold in the inhalation mode; When the temperature change slope is equal to the early braking stop threshold, the atomization drive circuit is controlled to stop; When the current temperature change slope is equal to the early braking start threshold, the atomization drive circuit is controlled to start.

6. The breathing-following atomization control method based on temperature detection according to claim 1, characterized in that: The characteristic parameters also include breathing depth, and the atomization power output by the atomization drive circuit is controlled according to the breathing depth to adjust the atomization rate.

7. A breathing-following atomization control method based on temperature detection according to claim 6, characterized in that: The method for calculating the respiratory frequency and the respiratory depth includes: extracting a peak value or a valley value in the temperature data within at least two consecutive respiratory events, and calculating the respiratory frequency and the respiratory depth based on the peak value or the valley value.

8. The breathing-following atomization control method based on temperature detection according to claim 1, characterized in that: The temperature data is generated by converting a temperature signal collected by a temperature sensor, and the temperature signal is a low-frequency temperature signal within the frequency band of the user's breathing rhythm after filtering and denoising.

9. A breathing-following atomization control method based on temperature detection according to claim 8, characterized in that: The filtering method comprises: Using a low-pass filter to remove high-frequency noise in the respiratory temperature signal; A bandpass filter was used to remove signals outside the respiratory rhythm frequency band.

10. The breathing-following atomization control method based on temperature detection according to claim 8, characterized in that: The denoising method comprises: reducing fluctuations in the respiratory temperature signal by a smoothing algorithm; Artifacts not related to normal breathing are identified and removed through an oversampling algorithm.

11. The breathing-following atomization control method based on temperature detection according to claim 1, characterized in that: It also includes monitoring abnormal breathing based on the temperature change slope and a preset abnormal threshold: Adjusting the current temperature change slope according to the influence coefficient of temperature change on respiratory characteristics to obtain a slope correction value; The slope correction value is compared with the abnormal threshold value, and when the slope correction value is lower than the abnormal threshold value, it is determined that the breathing is abnormal.

12. An atomization control system, characterized in that: It includes a controller for implementing the atomization control method described in any one of claims 1-11, and also includes a temperature sensor for real-time acquisition of temperature data of the user's breathing, wherein the temperature sensor is electrically connected to the controller and is used to output the temperature data to the controller.

13. An atomizer, characterized in that: It comprises a main unit, a medicine cup, an atomizing sheet assembly, a mist outlet, a user inhalation end and the atomizing control system according to claim 12; The medicine cup is arranged on the top of the main unit, and the mouth of the medicine cup, the mist outlet and the user inhalation end are assembled in sequence; The atomizing sheet assembly is arranged in a medicine liquid output channel formed by assembling the medicine cup and the mist outlet; The temperature sensor is arranged in a mist outlet channel formed by assembling the mist outlet and the user inhalation end, and is electrically connected to the controller via a connector.

14. A temperature-detection-based breathing-following nebulizer according to claim 13, characterized in that: The connector includes a first contact and a first probe; The first contact is electrically connected to the temperature sensor via a wire, and both are arranged at the mist outlet or the user inhalation end; The first probe is disposed on the medicine cup or the host and is electrically connected to the controller; When the mist outlet or the user inhalation end is assembled, the first contact is directly or indirectly connected to the first probe, so that the temperature sensor and the controller are electrically connected.

15. A temperature-detection-based breath-following nebulizer according to claim 14, characterized in that: When the temperature sensor is arranged in the outlet of the mist outlet, the first contact is arranged in the inlet of the mist outlet and is indirectly connected to the first probe; The atomizer sheet assembly has a conductive plate, the conductive plate is electrically connected to a second probe disposed at the mouth of the medicine cup, the second probe is connected to an atomizer drive circuit, and the atomizer drive circuit is electrically connected to a controller; When the mist outlet is assembled with the medicine cup, the first contact point is in contact with and connected to one side of the conductive plate, and the first probe and the second probe are in contact with and connected to the other side of the conductive plate.

16. A temperature-detection-based breathing-following nebulizer according to claim 14, characterized in that: When the temperature sensor is arranged in the user inhalation end, the first contact is arranged at the edge of the assembly end of the user inhalation end, and when the user inhalation end is assembled with the medicine cup, the first contact is directly contacted and connected with the first probe.

17. A temperature-detection-based breathing-following nebulizer according to claim 16, characterized in that: The first probe is arranged at the outer edge of the cup mouth of the medicine cup, and a through hole for passing the first probe or the first contact is opened on the mist outlet.

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