Oxygen inhalation device capable of monitoring oxygen inhalation state of patient

Abstract

The invention discloses an oxygen inhalation device capable of monitoring the oxygen inhalation state of a patient. The oxygen inhalation device comprises a nasal catheter assembly connected with an oxygen supply source, an oxygen supply existence detection module, an inspiration existence detection module and a judgment and timing module. The oxygen supply existence detection module detects the pressure difference through a throttling structure in the main oxygen supply channel and a first pressure detector so as to judge the oxygen supply state; the inspiration existence detection module detects the snorting state through a pressure tapping hole in the nasal vestibule and a second pressure detector. The judging and timing module accumulates effective oxygen uptake time when oxygen supply and snuffing signals meet conditions at the same time, and can dynamically correct a judging threshold value to adapt to working condition differences such as water level changes of a humidifying bottle. A low-damping microporous cover and a waste liquid cavity are arranged outside the pressure tapping hole to prevent blockage and keep signals stable, and the device can prompt states such as mouth breathing and abnormal oxygen supply and record events. The device is simple in structure, good in compatibility and capable of accurately and stably metering the effective oxygen uptake time in a complex clinical environment.

Description

TECHNICAL FIELD

[0001] The application belongs to the technical field of medical devices, and specifically relates to an oxygen inhalation device capable of monitoring the oxygen inhalation state of a patient. BACKGROUND

[0002] Oxygen inhalation therapy is a common and important treatment method in hospital respiratory departments, intensive care, postoperative rehabilitation and other scenarios. The existing clinical practice generally uses devices such as nasal catheters and face masks to deliver oxygen from an oxygen supply source to the patient's respiratory tract to improve blood oxygen saturation. However, in actual application, the recording of oxygen inhalation time and medical insurance settlement in hospitals are usually based on the running time of the oxygen supply equipment or the use time of the oxygen flow meter in the ward. This method has a significant deficiency, that is, it cannot determine whether the patient has actually inhaled oxygen during the operation of the equipment.

[0003] In a clinical environment, the patient's oxygen inhalation process is easily affected by various factors, such as nasal catheter displacement, falling off, nasal obstruction, the patient changing to oral breathing, changes in the water level of the humidification bottle, the oxygen supply pipeline being pulled out or blocked, etc. Even if the oxygen supply equipment continues to work, the patient may not have effectively inhaled oxygen, resulting in a discrepancy between the recorded time and the actual effective oxygen inhalation time. This error not only affects the accuracy of medical insurance charges, but also misleads medical staff in judging the patient's oxygen compliance and therapeutic effect.

[0004] In the prior art, some devices install flow sensors or pressure sensors at the oxygen supply end to determine whether there is oxygen flow, but such methods can only detect the oxygen supply state at the equipment end and cannot determine the actual inhalation behavior at the patient end. When the patient breathes orally, pauses breathing, or the nasal cavity is blocked, such devices will still count the time as effective oxygen inhalation time, causing statistical bias. Some research has proposed using nasal pressure changes to detect breathing signals, but if the oxygen supply state is not combined, it is easy to miscount the inhalation action without oxygen supply as effective oxygen inhalation.

[0005] Therefore, there is an urgent need for an oxygen inhalation monitoring device that can simultaneously detect the presence of oxygen supply and inhalation, and has long-term stable pressure sampling capability, to accurately count the actual effective oxygen inhalation time of the patient, thereby improving the accuracy of medical insurance settlement, optimizing clinical oxygen management, and reducing the manual intervention of nursing staff. SUMMARY

[0006] The purpose of the present application is to provide an oxygen inhalation device capable of monitoring the oxygen inhalation state of a patient. The present application achieves coordinated optimization in multiple links such as oxygen supply determination, nasal inhalation recognition, dynamic baseline correction, signal blocking prevention, abnormality detection and event recording, and can continuously and stably obtain the true effective oxygen inhalation time in a complex and variable clinical environment, overcoming the deficiencies of the prior art in terms of measurement accuracy, anti-interference ability and auditability.

[0007] The technical solution adopted by the present application is as follows:

[0008] An oxygen inhalation device capable of monitoring the oxygen inhalation state of a patient, comprising:

[0009] A nasal catheter assembly comprising a main oxygen supply channel connected to an oxygen supply source, and an inhalation pressure tapping hole located in the nasal vestibule dead space;

[0010] An oxygen supply presence detection module arranged in the main oxygen supply channel, comprising a throttling structure and a first pressure detector connected thereto, for detecting the pressure difference on both sides of the throttling structure in the main oxygen supply channel to determine whether oxygen supply is present;

[0011] An inhalation presence detection module comprising a second pressure detector in communication with the inhalation pressure tapping hole, for detecting the inhalation negative pressure in the patient's nasal cavity;

[0012] A determination and timing module comprising a microcontroller connected to the first pressure detector and the second pressure detector respectively, the microcontroller being configured to only accumulate the effective oxygen inhalation time when both the oxygen supply presence is detected and the patient's nasal cavity is in the inhalation state, and output the effective oxygen inhalation time.

[0013] Wherein the throttling structure is a Venturi throat or a short throttling hole, the size of which is set to generate a detectable pressure difference under the rated oxygen supply flow without significantly affecting the treatment flow.

[0014] Wherein the inhalation pressure tapping hole has a hole diameter of ~ mm, and its position is ~ mm away from the nasal prong outlet, and is covered with a hydrophobic membrane on the outside to reduce the influence of exhalation turbulence and condensate.

[0015] Wherein the microcontroller is configured to perform debouncing processing when accumulating the effective oxygen inhalation time, and only when both the oxygen supply presence signal and the inhalation presence signal have a duration greater than a preset holding time threshold value, the accumulation is performed.

[0016] Wherein the microcontroller is further configured to pause the accumulation of the effective oxygen inhalation time when an outgoing check or oxygen supply interruption occurs.

[0017] Wherein the device comprises a display module for displaying the effective oxygen inhalation time, the display module being one of a segment code liquid crystal screen, an electronic paper display screen or a light emitting diode display screen.

[0018] Wherein the inhalation presence detection module is also used to identify the switching of the patient's oral-nasal breathing channel, and to pause the accumulation of the effective oxygen inhalation time when the nasal cavity negative pressure signal disappears.

[0019] Wherein the microcontroller is configured to issue a prompt signal when the oxygen supply presence is detected and the duty cycle of the nasal cavity inhalation signal is abnormal, to prompt the patient or the caregiver to check the nasal catheter wearing state.

[0020] The nasal catheter assembly is a detachable link structure, wherein the thin catheter in communication with the air intake pressure hole is a disposable consumable.

[0021] A method for monitoring the oxygen inhalation state of a patient, comprising the following steps:

[0022] 1) detecting the pressure difference on both sides of the oxygen supply channel throttle structure by a first pressure detector to obtain an oxygen supply presence signal;

[0023] 2) detecting the pressure change at the nasal vestibule by a second pressure detector to obtain an inhalation presence signal;

[0024] 3) when the oxygen supply presence signal and the inhalation presence signal simultaneously meet the preset threshold condition and the duration exceeds the preset holding time threshold, accumulating the effective oxygen inhalation time by a microcontroller;

[0025] 4) outputting the accumulated effective oxygen inhalation time by a display module.

[0026] As described above, due to the adoption of the above technical solutions, the beneficial effects of the present application are:

[0027] By setting a throttle structure in the oxygen supply path and cooperating with the first pressure detector to obtain a pressure difference signal, the present application can accurately determine whether oxygen supply exists; at the same time, a pressure hole is arranged at the patient's nasal catheter, and a second pressure detector is used to obtain a nasal inhalation signal in real time. The determination and timing module only accumulates the effective oxygen inhalation time when the oxygen supply and the nasal inhalation exist simultaneously, thereby avoiding the problems of false high timing or false low timing caused by only relying on the oxygen supply state of the equipment or only relying on the patient's inhalation state.

[0028] To adapt to the daily disturbances such as the change of water level in the humidification bottle and the fluctuation of oxygen supply flow in the clinical environment, the present application introduces a dynamic baseline self-calibration mechanism in the determination logic, so that the oxygen supply determination threshold can be automatically corrected according to the actual pressure difference in the stable period, thereby maintaining the stability of the determination under different flows and different equipment conditions and reducing the misjudgment caused by the change of working conditions.

[0029] At the nasal inhalation signal acquisition end, the present application sets a low-damping micropore cover outside the pressure hole, and forms a hydrophilic inner wall and a liquid guide tube structure leading to the waste liquid chamber in the cover body, which can guide and lock the secretions or condensate in the waste liquid chamber, preventing them from flowing back or entering the pressure detection channel. This passive self-cleaning and water locking design makes the nasal inhalation signal clear and stable in long-term use, reducing the problems of blockage, attenuation or waveform distortion.

[0030] In the case where the patient's nasal inhalation duty cycle significantly decreases due to mouth breathing or speaking, the present application automatically suspends the accumulation of effective oxygen inhalation time by analyzing the waveform characteristics and phase relationship of the nasal inhalation signal in real time, and can trigger a prompt, thereby avoiding the non-nasal inhalation stage being mistakenly counted as effective oxygen inhalation time.

[0031] For the oxygen supply interruption caused by outgoing inspection, transfer, etc., the application can determine the interruption state through the rapid disappearance of the pressure difference signal, stop timing in a short time, and automatically reset to continue timing after the oxygen supply is restored, effectively preventing the mis-timing during the interruption. At the same time, the system can identify the abnormal state of incomplete interruption but significant flow reduction such as obstruction of the humidification bottle air inlet part, and prompt through the display module to realize the active identification and recording of early oxygen supply abnormalities.

[0032] In addition, the determination and timing module of the application can save event timestamps and cumulative effective time, realize the traceability and reviewability of data, and provide reliable basis for clinical quality control and medical insurance audit. The device is compatible with the conventional nasal catheter structure, and only needs to add small pressure taking and detection components at the oxygen supply end and the nasal fork end to realize the function, has the characteristics of low deployment cost, high compatibility and easy popularization. 2 In summary, the application realizes the coordinated optimization in oxygen supply determination, nasal inhalation identification, dynamic baseline correction, signal blocking prevention, abnormality detection and event recording, etc., and can continuously and stably obtain the real effective oxygen inhalation time in complex and variable clinical environments, overcoming the deficiencies of the prior art in measurement accuracy, anti-interference ability and auditability. BRIEF DESCRIPTION OF DRAWINGS

[0034] Figure 1 is a structural schematic diagram of the device of the application;

[0035] Figure 2 is a structural schematic diagram of the oxygen supply presence detection module of the application;

[0036] Figure 3 is a flowchart of the method of monitoring the oxygen inhalation state of a patient of the application.

[0037] In the figure, 1, nasal catheter assembly; 11, main oxygen supply channel; 12, inhalation pressure tapping hole; 121, microporous cover; 122, liquid guide pipe; 123, waste liquid cavity; 14, fine catheter; 2, oxygen supply source; 3, oxygen supply presence detection module; 31, throttling structure; 32, first pressure detector; 4, inhalation presence detection module; 41, second pressure detector; 5, determination and timing module; 6, display module. DETAILED DESCRIPTION

[0038] In order to make the purpose, technical scheme and advantages of the application clearer, the application will be further described in detail below in combination with the drawings and examples. It should be understood that the specific examples described herein are only used to explain the application and do not limit the application.

[0039] The application discloses an oxygen inhalation device capable of monitoring the oxygen inhalation state of a patient, comprising a nasal catheter assembly 1, an oxygen supply presence detection module 3, an inhalation presence detection module 4, a judgment and timing module 5 and a display module 6, which can monitor and accumulate the effective oxygen inhalation time of a patient in real time in a clinical environment, avoids the problem of over-counting time caused by no oxygen inhalation in the middle of medical insurance charging, and comprises components as shown in Figure 1 and 2 .

[0040] The nasal catheter assembly 1 comprises a main oxygen supply channel 11 connected with an oxygen supply source 2 and an inhalation pressure tapping hole 12 located in the nasal vestibule dead space.

[0041] The inhalation pressure tapping hole 12 is arranged on the side wall of the nasal prong, has a hole diameter of 0.25-0.35 mm and a hole distance of 3-5 mm from the nasal prong outlet, and can ensure that the negative pressure change in the nasal cavity can be perceived during inhalation. The inhalation pressure tapping hole 12 is covered with a hydrophobic film on the outside to prevent exhalation moisture and condensed water from entering the detection pipeline. The inhalation pressure tapping hole 12 is connected with a second pressure detector 41 in the inhalation presence detection module 4 through a thin catheter 14, and the thin catheter 14 is made of disposable medical plastic hose, which is convenient to replace and avoids cross infection.

[0042] The oxygen supply presence detection module 3 is installed on the main oxygen supply channel 11 and comprises a throttling structure 31 and a first pressure detector 32. The throttling structure 31 is preferably a Venturi throat, the inner diameter of which is reduced by 20%-40% compared with the main channel, so that a stable detectable pressure difference is formed. The throttling structure 31 is provided with pressure tapping holes at two ends, which are connected with the first pressure detector 32 through short pipes. The first pressure detector 32 is a differential pressure sensor, which can detect the pressure difference in the range of 0-5 kPa.

[0043] When the oxygen supply source 2 outputs oxygen, a stable pressure difference is generated on both sides of the throttling structure 31, and the first pressure detector 32 detects the pressure difference and outputs an oxygen supply presence signal.

[0044] The inhalation presence detection module 4 monitors the pressure change in the thin catheter 14 through the second pressure detector 41. The second pressure detector 41 is a high-sensitivity micro-pressure sensor, which has a detection range of -2 kPa to +2 kPa and is used for perceiving the instantaneous negative pressure signal generated by the nasal cavity of the patient during inhalation. If there is no inhalation action of the nasal cavity or the patient changes to oral breathing, the negative pressure signal output by the second pressure detector 41 will be obviously weakened or disappeared.

[0045] Judgment and timing module 5: Judgment and timing module 5 includes a microcontroller MCU, which receives the oxygen supply presence signal from the first pressure detector 32 and the inhalation presence signal from the second pressure detector 41.

[0046] The microcontroller is programmed to execute the following logic:

[0047] Only when both signals simultaneously meet the preset threshold (e.g., oxygen supply pressure difference > 0.2 kPa, inhalation negative pressure)

[0048] Only when the pressure is less than -0.05 kPa and the duration exceeds 200 ms (de-shaking time) can the period be considered as effective oxygen inhalation.

[0049] Effective oxygen inhalation time is accumulated and stored in seconds.

[0050] When an oxygen supply interruption is detected or an inspection is conducted (the oxygen supply signal disappears for more than 3 seconds), the pause time is accumulated.

[0051] When an abnormal nasal inspiratory signal duty cycle is detected (e.g., the inspiratory ratio is less than 30% of the normal breathing pattern), the patient or caregiver will be prompted to check the nasal cannula wearing status via a buzzer or display screen.

[0052] Display Module 6: Display Module 6 is connected to the microcontroller and is used to display the cumulative effective oxygen inhalation time. Display Module 6 can be one of a segment LCD screen, an electronic paper display screen, or an LED digital tube. The display unit can be "hour:minute" or "minute:second", and the timer can be restarted after the reset button is pressed.

[0053] like Figure 3 As shown, a method for monitoring the effective oxygen inhalation time of a patient is described. This method, used to monitor the effective oxygen inhalation time of a patient, specifically includes the following steps:

[0054] Oxygen supply presence detection: The first pressure detector 32 detects the pressure difference across the throttling structure 31 in real time, and outputs an oxygen supply presence signal when the pressure difference is greater than the set value.

[0055] Inhalation presence detection: The second pressure detector 41 detects the negative pressure signal of the inhalation pressure tap 12 at the nasal vestibule in real time. When the negative pressure is greater than the set value, an inhalation presence signal is output.

[0056] Effective oxygen inhalation determination and timing: After the microcontroller receives both the oxygen supply presence signal and the inhalation presence signal simultaneously and the duration exceeds the set de-jittering time, it begins to accumulate the effective oxygen inhalation time.

[0057] Display output: The effective oxygen inhalation time is displayed in real time on display module 6, which can be used for medical insurance settlement and clinical oxygen use assessment.

[0058] In the traditional oxygen inhalation process, hospital billing and clinical assessment are usually based on the running time of the oxygen supply equipment. However:

[0059] If the patient's nasal cannula is displaced, falls off or the oral-nasal breathing mode is switched, oxygen bypass leakage occurs even if the equipment continues to supply oxygen, and the patient does not actually inhale oxygen.

[0060] Medical insurance policies require billing to be based on the actual effective oxygen inhalation time of the patient, otherwise it is easy to cause charging bias.

[0061] Most existing devices can only detect the flow rate and pressure at the equipment end, and lack of synchronization monitoring of the patient's inhalation action and oxygen supply flow.

[0062] Therefore, a "oxygen supply exists + inhalation exists" dual condition judgment mechanism must be established to accurately calculate the effective oxygen inhalation time.

[0063] The present application realizes accurate monitoring of the patient's effective oxygen inhalation time by introducing an oxygen supply existence detection module 3 and an inhalation existence detection module 4 based on the traditional nasal cannula oxygen inhalation device. Specifically, the nasal cannula assembly 1 is connected with the oxygen source 2 through the main oxygen supply channel 11, and a throttling structure 31 is arranged in the main oxygen supply channel 11, which will form a measurable small pressure difference on both sides during the oxygen supply process. The first pressure detector 32 is used to detect the pressure difference and output an oxygen supply existence signal when the pressure difference exceeds a preset threshold, so as to determine that there is indeed oxygen flowing through the nasal cannula assembly 1. At the same time, an inhalation pressure tapping hole 12 is opened inside the nasal fork outlet of the nasal cannula, which is located in the quiet zone of the nasal vestibule and can stably collect the negative pressure signal formed in the nasal cavity when the patient inhales. The negative pressure signal is transmitted to the second pressure detector 41 through the thin catheter 14, and when the patient inhales through the nasal cavity, the second pressure detector 41 outputs an inhalation existence signal; when the patient changes to oral breathing, the nasal cannula is displaced or blocked, the negative pressure signal disappears, so as to determine that the patient does not inhale through the nasal cavity.

[0064] The determination and timing module 5 adopts a microcontroller as the core control unit, simultaneously receives the oxygen supply existence signal output by the first pressure detector 32 and the inhalation existence signal output by the second pressure detector 41, and performs logical AND operation on the two signals. Only when both signals are in the valid state at the same time, and the duration of the state exceeds a preset holding time threshold, the microcontroller will start to accumulate the effective oxygen inhalation time. When the signal appears a short fluctuation, the system prevents misjudgment through debouncing processing, effectively ensuring the accuracy of time statistics. Once one of the oxygen supply existence signal or the inhalation existence signal disappears, the accumulation process is immediately suspended, so that in the case of patient going out for examination, oxygen supply interruption, nasal cannula falling off, etc., the phenomenon of overcharging time will not occur.

[0065] In addition, the determination and timing module 5 can also identify the patient's breathing pattern by analyzing the duty cycle of the nasal negative pressure signal, and when an abnormally reduced nasal inhalation duty cycle is detected, the system will issue a prompt signal to remind the patient or the nursing staff to check the wearing state of the nasal cannula assembly 1. This mechanism can timely discover abnormal conditions such as nasal cannula displacement and oral-nasal breathing mode switching, further ensuring the authenticity of the effective oxygen inhalation time statistics. Finally, the accumulated effective oxygen inhalation time is output through the display module 6, which can be displayed in real time or periodically on a segment code liquid crystal screen, an electronic paper display screen or an LED display screen, facilitating the nursing staff to directly read and interface with the medical insurance settlement. The present application uses the combination of micro-pressure-difference detection and nasal vestibule negative pressure detection through the throttling structure 31, and can accurately monitor the actual inhaled oxygen state at the patient end without relying on expensive flow sensors, thereby solving the error problem caused by the existing technology of charging based on only the equipment running time, and ensuring the accuracy of medical insurance charging and the reliability of clinical dose evaluation.

[0066] In addition, in the oxygen supply presence detection module 3, the microcontroller 5 records the pressure difference value measured by the first pressure detector 32 in a short time after the device is started and oxygen supply is stable as an initial reference value for the presence of oxygen supply. During the operation of the device, the microcontroller will periodically reacquire the oxygen supply pressure difference and automatically correct the determination threshold value in combination with the current oxygen supply flow data. When the current pressure difference is higher than the corrected determination threshold value, it is determined that oxygen supply is present. This method can automatically adapt to changes in the water level of the humidification bottle and fluctuations in the oxygen supply flow, avoiding misjudgment caused by pressure difference fluctuations.

[0067] A low-damping microporous cover 121 is added outside the hydrophobic membrane of the inhalation pressure tapping hole 12, and the microporous cover 121 is located lower than the hydrophobic membrane; the inner wall of the microporous cover 121 is coated with a hydrophilic coating, so that the condensed water or nasal secretions can quickly spread on the inner wall after entering the cover, and flow into the micro-waste liquid chamber 123 suspended on the fine catheter 14 along the liquid guide pipe 122. The waste liquid chamber 123 is filled with a water-absorbing medical non-woven cotton core, which can lock the liquid to prevent it from flowing back to the pressure tapping hole 12, thereby ensuring that the pressure tapping hole is not blocked during long-term use, and achieving passive self-cleaning without external power.

[0068] In this embodiment, five typical clinical cases are summarized as follows:

[0069] Case 1: Oxygen supply determination under humidification bottle water level fluctuation:

[0070] Patient: male, 68 years old, COPD stable period, nasal cannula 3L / min;

[0071] Gold standard: mass flowmeter at the back end of the humidification bottle (bypass clamp connection);

[0072] Timeline (excerpt):

[0073] 00:00-00:10 start-up and stabilization: ΔΡ (first pressure detector 32) fluctuates between 0.24-0.26 kPa, microcontroller 5 records baseline.

[0074] 00:10 nurse changes humidification bottle water level from "high" to "medium": ΔΡ drops to 0.21 kPa, returns to 0.22-0.23 kPa within 30 s; microcontroller 5 threshold follows.

[0075] 00:30 water level changed from "medium" to "low": ΔΡ 0.19-0.20 kPa; threshold automatically lowered, no interruption determined.

[0076] 01:00 water level changed back to "medium": ΔΡ returns to 0.22-0.23 kPa.

[0077] Key recordings: mass flow meter readings 3.0 ± 0.1 L / min throughout; no interruption event.

[0078] Device determination: "oxygen present" throughout; alarm count = 0; threshold stabilization times (two changes) 17 s, 23 s, respectively.

[0079] Effective oxygen uptake time (to 01:00): device 60:00, gold standard 60:00; difference 0:00.

[0080] Case 2: effect of secretions and condensation on pressure tapping

[0081] Patient: female, 54 years old, bronchiectasis with rhinitis, nasal catheter 2 L / min;

[0082] Gold standard: intranasal disposable micro-pressure probe (for research only), chest and abdominal RIP belt;

[0083] Timeline (extract):

[0084] 00:00-00:20 stable nasal inhalation: B channel (second pressure detector 41) peak inspiratory -0.12 ~ -0.18 kPa; waveform consistent with RIP phase.

[0085] 00:21 patient blows nose, sees a small amount of secretions splashing to the outside of the nasal prong; (micropore cover 121) inner wall appears water film, 10 s into (waste liquid chamber 123) along (liquid guide tube 122).

[0086] 00:22-00:24 B channel peak briefly drops to -0.07 kPa, then rises to -0.13 kPa; RIP phase remains unchanged.

[0087] 00:50 room temperature drops to 21°C, condensation is seen on the outer wall of the nasal prong; (micropore cover 121) inner wall water droplets flow into (waste liquid chamber 123), no backflow is seen.

[0088] Key records:

[0089] Waste chamber (123) weight: +0.21 mL (60 min).

[0090] Wave loss statistics (>3 s continuous absence): 0 times; single-breath cycle waveform distortion events: 2 times (each <2 s).

[0091] 60 min effective oxygen inhalation time: device 58:46; gold standard 59:05; difference -0:19 (mainly from the de-bouncing effect of 00:21-00:24 short amplitude drop).

[0092] Case 3: Timing inhibition during mouth breathing / talking phase

[0093] Patient: male, 73 years old, heart failure combined with mild nasal congestion, nasal catheter 2.5 L / min;

[0094] Gold standard: nasal wing hot-wire flowmeter (nose breathing determination), mass flowmeter (oxygen supply presence);

[0095] Timeline (excerpt):

[0096] 00:00-00:10 Quiet nose breathing: B channel peak -0.10~ -0.16 kPa; device accumulates 10:00.

[0097] 00:10-00:25 Continuous conversation, mainly mouth breathing: hot-wire shows that the nose breathing absence rate is approximately 85%; B channel is mostly noise small peaks; (determination and timing module 5) triggers "low nose breathing duty cycle" prompt and pauses timing.

[0098] 00:25-00:35 Resume nose breathing: B channel resumes -0.12~ -0.15 kPa; device resumes timing.

[0099] Key records:

[0100] Mouth breathing phase 15:00: device counts 01:12; wall clock 15:00;

[0101] Whole process (35:00) device accumulates 21:12; gold standard (AND) 21:28; difference -0:16.

[0102] Prompt event: 1 time (00:11), patient adjusts the nasal prong, and the B channel amplitude rises.

[0103] Case 4: Supply interruption and stop watch during an outpatient examination

[0104] Patient: female, 62 years old, postoperative recovery, nasal catheter 3 L / min;

[0105] Gold standard: mass flowmeter behind humidification bottle;

[0106] Timeline (extract):

[0107] 00:00 - 00:15 Ward oxygen: ΔP 0.23 - 0.25 kPa, device timer = 15:00.

[0108] 00:15:08 Push-bed transport, oxygen tube unplugged from wall oxygen: mass flow meter = 0 L / min; (first pressure detector 32) ΔP drops to 0; (decision and timer module 5) switches to "oxygen supply interrupted" after 1.6 s, stops timer.

[0109] 00:36:20 Return to ward, reconnected: ΔP back to 0.24 kPa; (decision and timer module 5) "oxygen supply present" within 5 s; timer continues.

[0110] 00:51:00 End.

[0111] Key records:

[0112] During transport (approx. 21:12) device cumulative = 0; wall clock = 21:12;

[0113] Device effective oxygen throughout = 29:48; gold standard = 30:02; difference -0:14 (mainly from supply interruption decision delay and reset debounce).

[0114] Case 5: Early indication of wetting bottle inlet obstruction

[0115] Patient: Male, 58 years, pneumonia, oxygen 4 L / min;

[0116] Gold standard: Wetting bottle rear mass flow meter continuous recording;

[0117] Timeline (extract):

[0118] 00:00 - 00:20 Steady period: mass flow meter 4.0 ± 0.1 L / min; ΔP 0.31 - 0.33 kPa.

[0119] 00:21 Engineer adjusts wetting bottle inlet without informing nursing: mass flow meter drops to 2.7 - 2.8 L / min; ΔP drops with reduced high-frequency fluctuations.

[0120] 00:23:10 Device (5) decides "oxygen supply abnormal, check wetting bottle", display module (6) flashes indication; nursing changes wetting bottle at 00:26:40.

[0121] 00:27:20 New bottle online: mass flow meter returns to 4.0 L / min; ΔP back to 0.32 kPa; device status returns to "oxygen supply present".

[0122] Key records:

[0123] Abnormal prompt trigger point: the time point when the mass flow meter drops by ≥30% lags 02:05.

[0124] Abnormal duration: 6:10; During this period, the device is still timed according to AND logic (nasal inhalation is sufficient), and the effective oxygen inhalation time is not overcounted; The event is logged.

[0125] From the above real records of different clinical scenarios, it can be seen that the present application can still maintain accurate measurement of effective oxygen inhalation time in the presence of humidification bottle water level fluctuation, secretion and condensation, oral-nasal breathing switching, out-of-examination interruption, humidification bottle air intake obstruction, etc. The difference is all controlled within ±20 seconds, and there is no false high counting. Compared with the prior art, the differential pressure dynamic baseline self-calibration, passive self-cleaning pressure taking structure, nasal inhalation duty cycle judgment, quick interruption stop watch and abnormal fluctuation analysis functions of the present application specifically solve the long-neglected but significant problems in clinical practice, making the data verifiable, quantifiable, and useful for medical insurance settlement and efficacy evaluation.

[0126] The above only describes the preferred embodiments of the present application and is not intended to limit the present application. Any modification, equivalent replacement and improvement made within the spirit and principle of the present application shall be included in the protection scope of the present application.

Claims

1. An oxygen inhalation device capable of monitoring the oxygen inhalation state of a patient, characterized by comprising: The device comprises: a nasal cannula assembly (1) comprising a main oxygen supply channel (11) connected to an oxygen source (2), and an inhalation pressure tapping hole (12) located in the nasal vestibule dead space; an oxygen presence detection module (3) disposed in the main oxygen supply channel (11) and comprising a throttling structure (31) and a first pressure detector (32) connected thereto, for detecting the pressure difference on both sides of the throttling structure (31) to determine whether oxygen is present; an inhalation presence detection module (4) comprising a second pressure detector (41) in communication with the inhalation pressure tapping hole (12) for detecting the inhalation negative pressure in the patient's nasal cavity; a determination and timing module (5) comprising a microcontroller connected to the first pressure detector (32) and the second pressure detector (41) respectively, the microcontroller being configured to only accumulate the effective oxygen inhalation time when both the oxygen presence signal and the inhalation presence signal are detected, and output the effective oxygen inhalation time.

2. The oxygen inhalation apparatus capable of monitoring an oxygen inhalation state of a patient according to claim 1, characterized by The throttling structure (31) is a Venturi throat or a short throttling hole, and its size is set to generate a detectable pressure difference under the rated oxygen supply flow without significantly affecting the treatment flow.

3. The oxygen inhalation apparatus capable of monitoring an oxygen inhalation state of a patient according to claim 1, wherein The inhalation pressure tapping hole (12) has a hole diameter of 0.25-0.35 mm, and its position is 3-5 mm away from the nasal outlet, and is covered with a hydrophobic film on the outside to reduce the influence of exhalation turbulence and condensate.

4. The oxygen inhalation apparatus capable of monitoring an oxygen inhalation state of a patient according to claim 1, characterized by The microcontroller is configured to perform debouncing processing when accumulating the effective oxygen inhalation time, and only when the duration of both the oxygen presence signal and the inhalation presence signal is greater than the preset retention time threshold value, the accumulation is performed.

5. The oxygen inhalation apparatus capable of monitoring an oxygen inhalation state of a patient according to claim 1, wherein The microcontroller is further configured to pause the accumulation of the effective oxygen inhalation time when the device is checked or the oxygen supply is interrupted.

6. The oxygen inhalation apparatus capable of monitoring an oxygen inhalation state of a patient according to claim 1, wherein The device comprises a display module (6) for displaying the effective oxygen inhalation time, and the display module (6) is one of a segment code liquid crystal screen, an electronic paper display screen or a light emitting diode display screen.

7. The oxygen inhalation apparatus capable of monitoring an oxygen inhalation state of a patient according to claim 1, wherein The inhalation presence detection module (4) is also used to identify the switching of the patient's oral-nasal breathing channel, and to pause the accumulation of the effective oxygen inhalation time when the nasal cavity negative pressure signal disappears.

8. The oxygen inhalation apparatus capable of monitoring an oxygen inhalation state of a patient according to claim 1, wherein The microcontroller is configured to issue a prompt signal when the oxygen presence signal and the nasal cavity inhalation signal duty cycle are abnormal, to prompt the patient or the caregiver to check the nasal cannula wearing state.

9. The oxygen inhalation apparatus capable of monitoring an oxygen inhalation state of a patient according to claim 1, wherein The nasal cannula assembly (1) is a detachable link structure, and the fine cannula (14) in communication with the inhalation pressure tapping hole (12) is a disposable consumable.

10. A method for monitoring the oxygenation status of a patient, characterized in that, The method comprises the following steps: 1) detecting the pressure difference on both sides of the throttling structure (31) of the oxygen supply channel by the first pressure detector (32) to obtain an oxygen presence signal; 2) detecting the pressure change at the nasal vestibule by the second pressure detector (41) to obtain an inhalation presence signal; 3) accumulating the effective oxygen inhalation time by the microcontroller when the oxygen presence signal and the inhalation presence signal simultaneously meet the preset threshold condition and the duration exceeds the preset retention time threshold value; 4) outputting the accumulated effective oxygen inhalation time by the display module (6).

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