CN116271378A - Comfortable device capable of accurately controlling concentration of inhaled air and simultaneously detecting respiratory flow - Google Patents
Comfortable device capable of accurately controlling concentration of inhaled air and simultaneously detecting respiratory flow Download PDFInfo
- Publication number
- CN116271378A CN116271378A CN202310435937.0A CN202310435937A CN116271378A CN 116271378 A CN116271378 A CN 116271378A CN 202310435937 A CN202310435937 A CN 202310435937A CN 116271378 A CN116271378 A CN 116271378A
- Authority
- CN
- China
- Prior art keywords
- flow
- air
- mask
- concentration
- flowmeter
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 230000000241 respiratory effect Effects 0.000 title claims abstract description 31
- 239000007789 gas Substances 0.000 claims abstract description 92
- 239000001257 hydrogen Substances 0.000 claims description 5
- 229910052739 hydrogen Inorganic materials 0.000 claims description 5
- IJGRMHOSHXDMSA-UHFFFAOYSA-N Atomic nitrogen Chemical compound N#N IJGRMHOSHXDMSA-UHFFFAOYSA-N 0.000 claims description 4
- 238000001514 detection method Methods 0.000 claims description 4
- 238000006243 chemical reaction Methods 0.000 claims description 3
- 238000000034 method Methods 0.000 claims description 3
- UBAZGMLMVVQSCD-UHFFFAOYSA-N carbon dioxide;molecular oxygen Chemical compound O=O.O=C=O UBAZGMLMVVQSCD-UHFFFAOYSA-N 0.000 claims description 2
- 229910052757 nitrogen Inorganic materials 0.000 claims description 2
- 239000001307 helium Substances 0.000 claims 1
- 229910052734 helium Inorganic materials 0.000 claims 1
- SWQJXJOGLNCZEY-UHFFFAOYSA-N helium atom Chemical compound [He] SWQJXJOGLNCZEY-UHFFFAOYSA-N 0.000 claims 1
- 125000004435 hydrogen atom Chemical class [H]* 0.000 claims 1
- 238000009423 ventilation Methods 0.000 abstract description 7
- 229940075473 medical gases Drugs 0.000 abstract description 4
- 230000029058 respiratory gaseous exchange Effects 0.000 description 21
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 7
- 238000010586 diagram Methods 0.000 description 7
- 239000001301 oxygen Substances 0.000 description 7
- 229910052760 oxygen Inorganic materials 0.000 description 7
- 238000002640 oxygen therapy Methods 0.000 description 6
- 238000005259 measurement Methods 0.000 description 5
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 5
- UFHFLCQGNIYNRP-UHFFFAOYSA-N Hydrogen Chemical compound [H][H] UFHFLCQGNIYNRP-UHFFFAOYSA-N 0.000 description 4
- 230000001276 controlling effect Effects 0.000 description 4
- 210000001331 nose Anatomy 0.000 description 4
- 229920003023 plastic Polymers 0.000 description 4
- 239000004033 plastic Substances 0.000 description 4
- VYPSYNLAJGMNEJ-UHFFFAOYSA-N Silicium dioxide Chemical compound O=[Si]=O VYPSYNLAJGMNEJ-UHFFFAOYSA-N 0.000 description 3
- 210000003128 head Anatomy 0.000 description 3
- 239000000463 material Substances 0.000 description 3
- 239000000741 silica gel Substances 0.000 description 3
- 229910002027 silica gel Inorganic materials 0.000 description 3
- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 description 2
- 208000008784 apnea Diseases 0.000 description 2
- 230000003434 inspiratory effect Effects 0.000 description 2
- 239000002184 metal Substances 0.000 description 2
- 210000002345 respiratory system Anatomy 0.000 description 2
- 238000004088 simulation Methods 0.000 description 2
- 230000000638 stimulation Effects 0.000 description 2
- 238000012360 testing method Methods 0.000 description 2
- 206010021143 Hypoxia Diseases 0.000 description 1
- 208000004756 Respiratory Insufficiency Diseases 0.000 description 1
- 238000009825 accumulation Methods 0.000 description 1
- 230000037007 arousal Effects 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 210000004369 blood Anatomy 0.000 description 1
- 229910002092 carbon dioxide Inorganic materials 0.000 description 1
- 239000001569 carbon dioxide Substances 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 239000006260 foam Substances 0.000 description 1
- 239000000499 gel Substances 0.000 description 1
- 150000002431 hydrogen Chemical class 0.000 description 1
- 208000000122 hyperventilation Diseases 0.000 description 1
- 230000000870 hyperventilation Effects 0.000 description 1
- 230000007954 hypoxia Effects 0.000 description 1
- 239000003562 lightweight material Substances 0.000 description 1
- 230000014759 maintenance of location Effects 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 238000012544 monitoring process Methods 0.000 description 1
- 210000003928 nasal cavity Anatomy 0.000 description 1
- 229920001296 polysiloxane Polymers 0.000 description 1
- 230000002035 prolonged effect Effects 0.000 description 1
- 238000011002 quantification Methods 0.000 description 1
- 230000001105 regulatory effect Effects 0.000 description 1
- 201000004193 respiratory failure Diseases 0.000 description 1
- 208000023504 respiratory system disease Diseases 0.000 description 1
- 230000033764 rhythmic process Effects 0.000 description 1
- 230000003860 sleep quality Effects 0.000 description 1
- 239000013589 supplement Substances 0.000 description 1
- 230000009469 supplementation Effects 0.000 description 1
- 230000001225 therapeutic effect Effects 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0057—Pumps therefor
- A61M16/0066—Blowers or centrifugal pumps
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes operated by electrical means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes operated by electrical means
- A61M16/022—Control means therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/06—Respiratory or anaesthetic masks
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/20—Valves specially adapted to medical respiratory devices
- A61M16/201—Controlled valves
- A61M16/202—Controlled valves electrically actuated
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
- A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/40—Respiratory characteristics
Abstract
The invention relates to a device capable of accurately controlling the concentration of inhaled air and simultaneously detecting the respiratory flow, which comprises a flow concentration controller, a mask and a flowmeter, wherein the flow concentration controller consists of an air flow generator (such as a blower), a medical air source and an air mixing component, and the flow concentration controller can output air with constant flow and concentration; the face mask has a capacity of 50-1000ml and comprises a mask main body and a proximal pad part, wherein the proximal pad part is soft and can be attached to the face, the proximal end of the mask main body is provided with an air inlet, one side of the air inlet is provided with a baffle for eliminating the impact of air flow on the face, and the distal end of the mask main body is provided with a flowmeter. The constant flow rate concentration air flow output by the flow concentration controller enters from the near end of the mask and then passes through the flowmeter from the exhaust port at the far end of the maskAnd (5) flowing out. The device can promote the discharge of exhaled air, eliminate respiratory resistance and exhaled air CO 2 Can provide a constant flow and concentration of gas to a subject and accurately detect respiratory flow, including tidal volume and minute ventilation, when inhaling various medical gases.
Description
Technical field:
the invention relates to a device for detecting the inhalation and respiratory flow of medical gas with constant concentration
The background technology is as follows:
the quantification of respiratory airflow in a sleeping state is often realized by wearing a mask connected with a flow sensor, and the connecting mode can increase the dead space capacity and the respiratory resistance due to the lengthening of a pipeline, so that not only can the unsmooth breathing of a subject be caused and the sleeping be influenced, but also the pressure in the mask can be increased to cause the gas to enter and exit (leak) from the contact part of the mask and the face, thereby influencing the accuracy of gas flow measurement. "dead space volume" is a physiological term that refers to the inability of exhaled air to escape to the atmosphere, resulting in a portion of the inhaled air for the next respiratory cycle being exhaled air for the previous cycle. Due to exhaled air CO 2 High content, low oxygen concentration, increased dead space capacity and increased CO content 2 The concentration and the aggravation of hypoxia can further aggravate the illness state of patients with respiratory failure. In order to avoid air leakage, the headband is usually tightened, the face is stressed, discomfort is caused, and the sleeping quality is affected. In addition, under the air conditioner or indoor cold environment, due to the high temperature of the exhaled air, water drops can be formed in the cavity of the mask after the exhaled air is cooled, so that the measurement of flow rate is affected, and the water drops can flow back to the face due to excessive accumulation of the water drops in the mask, so that discomfort of a subject is aggravated.
Inhalation of medical gases such as oxygen, carbon dioxide, hydrogen and the like is an important method for treating respiratory diseases, and in order to achieve the therapeutic effect when the medical gases are inhaled, the concentration of the inhaled gases is ensured, and the respiratory flow including tidal volume and minute ventilation volume under the inhaled gases is also required to be detected. When the nasal catheter is used for oxygen therapy, the nasal catheter influences the fit between the mask and the face, so that air leakage is caused, and the accurate measurement of respiratory airflow is influenced. Meanwhile, when the nasal catheter is used for oxygen therapy, the concentration of oxygen inhaled into the respiratory tract changes along with the breathing rhythm and the breathing depth, and the concentration of the inhaled air is difficult to accurately control. If the mask is provided with an additional hole for inputting medical gas, the concentration of inhaled gas still changes along with the breathing mode, and the preset treatment effect cannot be achieved. Clinically, a mask used in noninvasive ventilation is often provided with a small through hole for connecting a central oxygen supply device in a hospital and a household oxygenerator or an oxygen bottle to realize oxygen therapy. CO can also be input from the through hole 2 To supplement CO in the presence of hyperventilation patients 2 Improving blood CO 2 Concentration. However, the method is thatWhile oxygen therapy or CO supplementation is performed through the small through holes 2 When the breathing rate is increased, the concentration of gas in the mask is decreased, while the exhalation phase is prolonged, the gas in the mask is accumulated, the concentration of inhaled gas is increased, and if the patient pauses breathing, the concentration of inhaled gas is further increased. When CO is input 2 At the same time, if too high a concentration of CO is inhaled 2 Can cause arousal and impair sleep quality. In addition, the flow rate often does not exceed 5 liters/minute when medical gas is directly delivered from the nasal cavity due to stimulation by the gas flow.
If a sufficient flow of gas is continuously fed from the proximal end of the mask and mixed well, and discharged through the distal end of the mask, a constant concentration of inhaled gas is ensured. If the distal end of the mask is connected to a flow meter, accurate measurement of the inhaled air flow is ensured at a constant concentration of inhaled air. We have earlier devised an oxygen therapy related device (ZL 2018 0388945.3) comprising a mask with a large aperture at the distal end. The high-flow gas which is uniformly mixed is input from the proximal end of the mask, the patient is supplied with inspiration, the redundant gas is discharged from the distal end of the mask, and the high-flow gas input into the mask is discharged from the distal end exhaust port and the flowmeter together with the expiration gas during expiration. The inner pressure of the face mask is always zero and no respiratory resistance exists because the far end is provided with a large exhaust port communicated with the atmosphere. However, a high flow of air that is uniformly mixed is input from the proximal end of the mask, and the air can impinge on the face and nose and mouth, especially in environments where the air flow is large or cold, and the subject can feel cold discomfort or even be intolerable.
Disclosure of Invention
To overcome the above problems, we have invented a device that can accurately control the concentration of inhaled gas and accurately measure the flow of respiratory gas, and is comfortable to wear.
In order to achieve the above purpose, the invention is realized by the following scheme:
a comfortable device capable of accurately controlling the concentration of inhaled air and simultaneously detecting the respiratory flow comprises a flow concentration controller, a mask and a flowmeter, wherein the flow concentration controller can be used for accurately controlling the concentration of inhaled air.
The flow concentration controller is formed by air flowGenerators, medical sources (they may be oxygen, CO) 2 Or hydrogen, etc.) and a gas mixing assembly. The principle is similar to that of an oxygen therapy related device invented earlier (patent license numbers are ZL 2018 1 0388945.3 respectively). Specifically, a constant air flow is generated by a blower and is combined with air (oxygen, CO) from a medical air source 2 ) Mixing, and inputting into the mask. The air supply quantity can be monitored by a flow sensor built in the flow concentration controller and can be adjusted by manual feedback and automatic feedback or a combination of manual feedback and automatic feedback. The adjusting mode can be used for adjusting the rotating speed of the blower and controlling the size of the pipeline through the valve to adjust the flow. The gas concentration can be monitored by a concentration sensor built in the flow concentration controller and can be manually fed back, automatically fed back or manually fed back and automatically fed back in combination to adjust the gas amount from the medical gas source so as to adjust the gas supply concentration.
The mask is a gas container with an effective gas volume that can be set to any value between 50-1000ml, can be made of metal, plastic, silicone and other materials that can form a container, and can be cylindrical, rectangular, oval or any other shape. The face contact end (proximal end) of the mask is the same as that of a conventional mask, and the mask can be made of soft and light materials such as plastic, silica gel and the like so as to ensure that the face is tightly connected with the mask. The proximal end of the mask has one or more air inlets, the outside of which is connected to the air delivery conduit to receive a constant flow of air from the blower or a uniform mixture of medical gases at a constant flow and concentration. The inner side of the face mask of the air inlet is provided with a baffle plate for reducing or preventing the impact of air flow on the mouth, nose and face. The baffle may be vertical or may be angled, with the inward angle being toward the air inlet and the distal end of the mask, with the angle ranging from any value from 30 to 180. The distal end of the mask has one or more large holes, and the exhaled air from the subject and air from the air delivery conduit are all exhausted from the large holes at the distal end of the mask and their attached flow meters, such that the internal pressure of the mask is always zero.
The flowmeter can be a common differential pressure flowmeter, an electromagnetic flowmeter, an impeller flowmeter, an ultrasonic flowmeter, a mass flowmeter and the like, and also can be a flowmeter with an analog-to-digital conversion function or a flowmeter with a mass flowmeterThe flowmeter has the functions of detection and display. The ventilation caliber of the flowmeter is large enough and the diameter of the flowmeter is 1cm 2 Above, to ensure that the ventilation is unobstructed and the internal pressure of the mask remains zero, the ideal vent for adults is 3cm 2 Even larger. 2-4 headband interfaces are provided outside the mask for securing the mask so that the mask is stably secured to the face.
The following is an example.
When the respiratory flow rate of the subject when the mixed gas having the hydrogen concentration of 2% is inhaled is to be measured, the subject is put on a mask to which a flowmeter is attached. Assuming a mask gas volume of 500ml, a mask inlet gas flow of 60L/min, H 2 A gas stream with a concentration of 2%. Opening high pressure H 2 The gas cylinder outputs 100% pure hydrogen gas, the output flow of the blower is regulated, when the final output flow of the flow concentration controller is 60L/min, H 2 At a concentration of 2%, the air flow from the blower was 58.8 liters/min, from CO 2 The flow rate of the gas cylinder was 1.2 liter/min (output gas H 2 The concentration was 1.2 x 100%/(1.2+58.8) =2%). When gas is delivered to the mask, the gas flow diffuses around the baffle by the baffle, fills the mask and exits the flow meter distally. Due to the baffle plate, the impact of the input air flow on the face and the mouth and nose of the patient is eliminated, and the patient has no uncomfortable feeling. When the subject inhales, the gas delivered to the mask from the flow concentration controller is inhaled, so that the gas flowing out of the flowmeter is reduced; during exhalation, the exhaled air of the subject is exhausted from the far end of the mask through the flowmeter together with the air flow output from the air flow concentration controller, so that the air flowing out through the flowmeter is increased. During an apnea, the flow of air exiting through the distal flow meter was equal to the flow of air input to the mask, i.e., 60L/min of base flow. The flow rate during respiration fluctuates up and down on the basis of 60L/min, so that the inspiration flow rate and the expiration flow rate are measured.
If the respiratory flow rate includes tidal volume and minute ventilation to be measured during certain conditions, such as exercise or sleep, the mask may be secured by the headgear and the flow meter connected by the adapter, and the flow concentration controller may be adjusted to output a predetermined flow of air to the mask, which may facilitate the removal of exhaled air due to the high flow rate of the air from the flow concentration controller. And the air flow output from the flow concentration controller continuously washes and replaces the air containing the exhaled air in the mask, so that the air at the near end of the mask does not contain the exhaled air during inhalation, and the repeated breathing of the traditional mask caused by dead space is avoided. If the subject's inspiratory flow rate is accidentally greater than the gas input to the mask, the subject may inhale the gas from the flow concentration controller that remains in the expiratory phase, the inhaled gas also being free of exhaled gas.
Compared with the prior art, the invention has the following advantages and beneficial effects:
1. the inner diameter of the flowmeter connected with the exhaust port at the far end of the mask is large, and the internal pressure of the mask is almost zero during breathing. Meanwhile, continuous high-flow air flow is input at the proximal end of the mask, so that extra air suction resistance can be eliminated; the high flow rate gas flows out of the far end flowmeter again, and the discharge of the exhaled air is promoted.
2. The high-flow air flow continuously input through the proximal end of the mask can flush and replace exhaled air, so that retention of carbon dioxide in the mask is eliminated, and repeated breathing and dead space ventilation are eliminated.
3. Because the mask exhaust port is large, the internal pressure is zero, and the head band is not required to be excessively tensioned when the mask is worn, the mask can be attached to the face to prevent air leakage, so that discomfort of wearing the mask is reduced, and the influence on sleeping is reduced.
4. Because continuous air flows pass through the mask and the flowmeter channels, the exhaled air is flushed, the formation that the exhaled air is converted into condensed water in a cold environment can be avoided, the measurement accuracy is ensured, and the stimulation of the condensed water to the face can be eliminated.
5. The air inlet in the mask of the device is provided with a baffle plate, so that direct impact of high-flow air flow from the air supply pipeline or cold air flow in a cold environment on the face and the mouth and nose can be eliminated, and the comfort of a subject is improved.
Drawings
The invention will be further described with reference to the drawings.
FIG. 1 shows that suction can be accurately controlledThe structure of the device for detecting the breath flow simultaneously with the gas inlet concentration is schematically shown. It is composed of a flow concentration controller 1, a mask 2 for detecting tidal volume and a flowmeter 3. The mask 2 is composed of a mask body 4, a cushion 5 which is attached to the face, and a baffle 6. The mask body 4 has a capacity of 50-1000ml, and the mask body 4 and the baffle 6 are mainly made of lightweight materials such as plastics, silica gel, metal, etc., and the material of the cushion 5 may be soft silica gel, gel or foam plastic, etc. The baffle 6 may be vertical or may be angled like an angle of refraction, with the angle of refraction being adjustable to any value in the range of 30-180 degrees toward the air inlet and the distal end of the mask. The air inlet pipeline joint 7 is used for connecting an air inlet of the face mask and the air output pipeline 8, and the air inlet pipeline joint 7 can be a joint which is straight-through, corner or can be made into a joint capable of rotating by 360 degrees through pipeline nesting, so that a subject can rotate the head at will after wearing the face mask, the joint between the face mask and the face is kept, and the air leakage of the face mask is avoided. The two outer sides of the face mask 2 are respectively provided with 1-2 head strap fixing bayonets 9. The distal end 10 of the mask body 4 is provided with a flow meter 3. The flowmeter 3 can be a common differential pressure flowmeter, a flowmeter with an analog-to-digital conversion function or a flowmeter with a detection and display function, and can be connected with a biological signal processor through a connecting wire 11 for real-time monitoring, storage and analysis of data. Medical air source (oxygen, CO) 2 Hydrogen or nitrogen, etc.) are uniformly mixed in the flow concentration controller through the air inlet 12 with the air taken in through the air inlet 13. When the testee needs to detect the respiratory airflow and the tidal volume, after the testee wears the mask, the airflow with constant flow rate concentration output by the flow concentration controller enters the cavity of the mask through the gas output pipeline 8 and the gas inlet pipeline connector 7. When the patient inhales, the gas delivered to the mask 2 by the inflow concentration controller 1 is inhaled, so that the gas flowing out through the flowmeter 3 is reduced; during exhalation, the exhaled air is discharged from the mask distal end 10 through the flowmeter 3 together with the air flow outputted from the flow rate concentration controller 1, and the air flow outputted through the flowmeter is increased, thereby measuring the inhalation flow rate and the exhalation flow rate.
FIG. 2 is a schematic diagram of a first embodiment of the flow concentration controller of the present invention. An air flow generator 14 (e.g., a blower) is coupled to the air inlet 13 to generate a sufficient flow of air. The medical air source is passed from the air inlet 12 through a flow control valve 15 and is homogeneously mixed with the air flow from the blower 14 into the air mixing zone 16. The gas mixing zone 16 may be a straight conduit, a curved conduit, or any other shape of chamber. The uniformly mixed gas flows through the gas flow concentration sensor 17 and flows out of the gas flow output port 18, and the display 19 can display the gas flow and concentration of the output gas flow in real time. The signal detected by the gas flow concentration sensor 17 can be automatically transmitted to the controller 20, and the controller 20 controls the blower control component 21 and the flow control valve 15 to automatically adjust the output flow speed and concentration to set values, that is, the flow concentration controller 1 can continuously output the mixed gas flow with constant flow speed and concentration. The operator can also manually adjust the flow and the concentration through a knob or a touch panel arranged on the flow concentration controller 1.
FIG. 3 is a schematic diagram of a second embodiment of the flow concentration controller of the present invention. The medical gas passes through the flow control valve 15 from the gas inlet 12, mixes with the air entering from the gas inlet 13, and is further uniformly mixed by the blower.
FIG. 4 is a schematic diagram of a third embodiment of a flow concentration controller according to the present invention. The high-pressure air flows from the air inlet 13 through the flow control valve 22, is mixed with medical air from the air inlet 12 through the flow control valve 15, then enters the air mixing area 16 to realize uniform mixing of the air, the uniformly mixed air flows through the air flow concentration sensor 17, flows out of the air flow output port 18, is connected with a mask and a flowmeter through a pipeline, and the display 19 can display the air flow and concentration of the output air flow in real time. The signal detected by the gas flow and concentration sensor 17 can be transmitted to the controller 20, and the controller 20 controls the valves 15 and 22 to automatically adjust the output flow speed and concentration to the set values.
Fig. 5 is a partial front view of a first embodiment of the mask of the present invention. It comprises a mask cushion inner face 5, a mask main body 4, a bevel baffle 6, an air inlet pipeline 7 and a mask far end 10 connected with a flowmeter.
Figure 6 is a block diagram of a fixed or removable corner baffle assembly in a mask. The angle baffle 6 consists of an air inlet pipeline connecting part 23, an angle edge 24 connected with the connecting part 23 and a suspended angle edge 25, wherein the inner angle faces the air inlet and the far end of the face cover, and the angle range of the angle baffle is any value in 30-180 degrees.
FIG. 7 is a schematic diagram of detecting respiratory tidal volume of a patient or subject. The patient wears the mask 2 through the headband fixing bayonet 9 and the connected headband 26, and the mask cushion 5 is attached to the face. The flow concentration controller delivers gas into the mask through the mask inlet 7 which is connected to the gas feed line, the direction of the gas flow through the gas feed line is shown by arrow 27, the direction of the gas flow after entering the mask is changed by the corner baffle 6 as shown by arrow 28 and flows to both sides of the mask to fill the mask, and the gas flow is discharged through the flow meter 3 as shown by arrow 29. When the subject holds his breath or apnea, the flow of gas through the flow meter 3 will coincide with the flow of gas 27 output by the flow concentration controller; when the subject exhales, the flow of exhaled air 30, together with the air 28 output by the flow concentration controller, forms an air flow 29 through the flow meter 3, when the amount of air flow through the flow meter 3 is equal to the sum of the flow of exhaled air 30 from the subject and the flow of air 27 from the air output device.
FIG. 8 is a schematic diagram of detecting inspiratory tidal volume of a patient or subject. The patient wears the mask 2 through the headband fixing bayonet 9 and the connected headband 26, and the mask cushion 5 is attached to the face. The flow concentration controller delivers gas into the mask through the mask inlet 7, which is connected to the gas supply line, the direction of the gas flow through the gas supply line is shown by arrow 27, and the direction of the gas flow is changed by the corner baffle 6 as shown by arrow 28 when it enters the mask, and flows to both sides of the mask to fill the mask. When the subject inhales, the flow of air 28, or air flowing on both sides of the mask, will enter the respiratory tract as indicated by arrow 31. When the subject inhalation flow rate is less than the flow rate outputted by the flow rate concentration controller, then the excess gas is discharged through the distal end of the flow meter 3 as indicated by arrow 29, and the flow rate of gas measured by the flow meter 3 is the difference between the flow rate 27 of gas and the patient inhalation flow rate 31.
The flow simulation test example is as follows
Fig. 9 is a schematic diagram of a flow simulation test device. The breathing pattern of the subject, i.e., tidal volumes of 0.5L, 1L, 1.5L, 2L, was simulated using a calibration cylinder 32 provided with 0.5L, 1L, 2L scales. The calibration cylinder 32 is tightly connected with the mask 2 through an adapter 33, and the flow concentration controller 1 is connected with the air inlet 7 of the mask 2 through a pipeline 8. The flow rate concentration controller 1 outputs an air flow rate of a constant flow rate (40L/min). When the air suction of the testee is simulated, the pull rod 34 of the calibration cylinder is pulled to the capacity positions of 0.5L, 1L, 1.5L and 2L of the air cylinder respectively, and the air flow rate curve is below the baseline flow, namely the flow detected by the flowmeter is smaller than the baseline flow; when the subject exhales, the piston of the calibration cylinder is pushed to fully discharge the gas in the cylinder, and the gas flow rate curve is above the baseline flow, namely, the flow detected by the flowmeter 3 is larger than the baseline flow, as shown by the curves in fig. 10, 11, 12 and 13.
FIG. 10 is a schematic illustration of simulated respiration at the 0.5L capacity site by pulling the pull rod 34 of the calibration cylinder 32 to the cartridge. Graph a is a graph of respiratory flow rate curve generated by a 0.5L volume scale drum simulated respiration with a flow concentration controller outputting a 40L/min air flow, and a gas flow rate fluctuating up and down at a base flow rate (40L/min). Graph B shows that the base flow rate 40L/min was set to the baseline flow rate (0L/min), and the suction capacity, i.e., the curve area at the baseline flow rate, was calculated using software to be 0.4981L, 0.4869L, 0.4916L, 0.4920L, 0.5069L, respectively, and the standard capacity error of 0.5L was less than 3%, which was substantially the same.
FIG. 11 is a schematic illustration of simulated respiration in a 1L capacity position by pulling the pull rod 34 of the calibration cylinder 32. Graph a is a graph of a breathing flow rate curve formed by a 1L volume scale drum simulating breathing with a flow concentration controller outputting a 40L/min air flow, and a gas flow rate fluctuating up and down at a base flow rate (40L/min). Graph B shows that the base flow rate 40L/min was set to the baseline flow rate (0L/min), and the suction capacity, i.e., the curve area at the baseline flow rate, was calculated using software to be 0.9903L, 0.9977L, 0.9773L, 0.9851L, 0.9759L, respectively, with a standard capacity error of less than 3% with 1L, and substantially identical.
FIG. 12 is a schematic illustration of simulated respiration in a 1.5L capacity position by pulling the pull rod 34 of the calibration cylinder 32. Graph a is a graph of breathing flow rate curve generated by a 1.5L volume scale drum simulated breathing with a flow concentration controller outputting 40L/min air flow, and a gas flow rate fluctuating up and down at a base flow rate (40L/min). Graph B shows that the base flow rate of 40L/min was set to the baseline flow rate (0L/min), and the suction capacity, i.e., the curve area at the baseline flow rate, was calculated using software to be 1.4805L, 1.4717L, 1.4841L, 1.4755L, respectively, and the standard capacity error of 1.5L was less than 2%, which was substantially the same.
Fig. 13 is a schematic illustration of simulated respiration in a 2L capacity position pulling the pull rod 34 of the calibration cylinder 32 to the cartridge. Graph a is a graph of respiratory flow rate curve generated by a 2L volume calibration cylinder simulating respiration with a flow concentration controller outputting a 40L/min air flow, and a gas flow rate fluctuating up and down at a base flow rate (40L/min). Graph B shows that the base flow rate 40L/min was set to the baseline flow rate (0L/min), and the suction capacity, i.e., the curve area at the baseline flow rate, was calculated using software to be 1.9927L, 1.9627L, 1.9769L, 1.9915L, respectively, with a standard capacity error of less than 2% with 2L, and substantially identical.
The above embodiments are preferred embodiments of the present invention, and any accurate detection of respiratory flow from the proximal end of the mask through the baffled inlet to the open mask at a constant gas concentration and flow is within the scope of this patent.
Claims (10)
1. A device capable of accurately controlling the concentration of inhaled air and simultaneously detecting respiratory flow, which is characterized in that: the device comprises a flow concentration controller, a mask and a flowmeter, wherein the flow concentration controller consists of a constant flow generator (such as a blower), a medical air source and a gas mixing component, and can output air flow with constant flow rate and concentration; the near end of the mask is provided with an air inlet, the inner side of the mask of the air inlet is provided with an air flow baffle, and the far end of the mask main body is provided with a large-caliber flowmeter.
2. A device for accurately controlling the concentration of inhaled air and simultaneously detecting respiratory flow according to claim 1, wherein: the medical gas can be oxygen, carbon dioxide, nitrogen, helium, hydrogen, or mixed gas.
3. A device for accurately controlling the concentration of inhaled air and simultaneously detecting respiratory flow according to claim 1, wherein: the gas mixing method can be a bent pipeline area, an enlarged and reduced pipeline area or an air inlet pipeline of a medical gas access blower through which the gas is mixed.
4. A device for accurately controlling the concentration of inhaled air and simultaneously detecting respiratory flow according to claim 1, wherein: the proximal end of the mask body has an air inlet, which may be one or more that receives an air flow from a flow concentration controller.
5. A device for accurately controlling the concentration of inhaled air and simultaneously detecting respiratory flow according to claim 1, wherein: the mask capacity is any value from 50 to 1000 ml.
6. A device for accurately controlling the concentration of inhaled air and simultaneously detecting respiratory flow according to claim 1, wherein: the caliber of the flowmeter at the far end of the mask main body is larger than 1cm 2 The internal mask pressure remains almost zero.
7. A device for accurately controlling the concentration of inhaled air and simultaneously detecting respiratory flow according to claim 1, wherein: the pad part at the near end of the mask is lightly attached to the face part, and the head band is not required to be tightened and the air leakage can be avoided.
8. A device for accurately controlling the concentration of inhaled air and simultaneously detecting respiratory flow according to claim 1, wherein: the baffle may be vertical or may form an angle of refraction, with the angle of refraction being toward the air inlet and the distal end of the mask, with the angle ranging from any value from 30 to 180 degrees.
9. A device for accurately controlling the concentration of inhaled air and simultaneously detecting respiratory flow according to claim 1, wherein: the flowmeter can be a common differential pressure flowmeter, other types of flowmeters such as an electromagnetic flowmeter, an impeller flowmeter, an ultrasonic flowmeter, a mass flowmeter and the like, and also can be a flowmeter with an analog-to-digital conversion function or a detection and display function.
10. A device for accurately controlling the concentration of inhaled air and simultaneously detecting respiratory flow according to claim 1, wherein: the flow of gas into the mask is anywhere between 10-300 liters/minute.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202310435937.0A CN116271378A (en) | 2023-04-22 | 2023-04-22 | Comfortable device capable of accurately controlling concentration of inhaled air and simultaneously detecting respiratory flow |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202310435937.0A CN116271378A (en) | 2023-04-22 | 2023-04-22 | Comfortable device capable of accurately controlling concentration of inhaled air and simultaneously detecting respiratory flow |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN116271378A true CN116271378A (en) | 2023-06-23 |
Family
ID=86816920
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202310435937.0A Pending CN116271378A (en) | 2023-04-22 | 2023-04-22 | Comfortable device capable of accurately controlling concentration of inhaled air and simultaneously detecting respiratory flow |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN116271378A (en) |
Citations (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5390666A (en) * | 1990-05-11 | 1995-02-21 | Puritan-Bennett Corporation | System and method for flow triggering of breath supported ventilation |
| US6581599B1 (en) * | 1999-11-24 | 2003-06-24 | Sensormedics Corporation | Method and apparatus for delivery of inhaled nitric oxide to spontaneous-breathing and mechanically-ventilated patients |
| CN104014062A (en) * | 2014-06-20 | 2014-09-03 | 昌克勤 | Oxygen uptake instrument |
| CN109303959A (en) * | 2018-10-26 | 2019-02-05 | 北京怡和嘉业医疗科技股份有限公司 | The control method of ventilation therapy equipment and ventilation therapy equipment |
| CN209253872U (en) * | 2018-12-13 | 2019-08-16 | 彭艳 | It is a kind of to facilitate the breathing apparatus for cardiovascular department for adjusting oxygen amount |
| CN110404145A (en) * | 2018-04-26 | 2019-11-05 | 罗远明 | A kind of accurate adjustable and without carbon dioxide retention oxygen therapy device of fraction of inspired oxygen |
| CN111375110A (en) * | 2018-12-29 | 2020-07-07 | 罗远明 | Gas inhalation device capable of keeping concentration of gas entering respiratory tract constant and having no respiratory resistance |
| CN113117206A (en) * | 2019-12-31 | 2021-07-16 | 罗远明 | Inhalation device for preventing and treating altitude stress |
| CN214232339U (en) * | 2020-03-25 | 2021-09-21 | 沈丹 | Oxygenation equipment for severe respiration |
| CN114403995A (en) * | 2021-12-16 | 2022-04-29 | 江南大学附属医院 | Tidal volume controllable breathing amplitude control mask |
-
2023
- 2023-04-22 CN CN202310435937.0A patent/CN116271378A/en active Pending
Patent Citations (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5390666A (en) * | 1990-05-11 | 1995-02-21 | Puritan-Bennett Corporation | System and method for flow triggering of breath supported ventilation |
| US6581599B1 (en) * | 1999-11-24 | 2003-06-24 | Sensormedics Corporation | Method and apparatus for delivery of inhaled nitric oxide to spontaneous-breathing and mechanically-ventilated patients |
| CN104014062A (en) * | 2014-06-20 | 2014-09-03 | 昌克勤 | Oxygen uptake instrument |
| CN110404145A (en) * | 2018-04-26 | 2019-11-05 | 罗远明 | A kind of accurate adjustable and without carbon dioxide retention oxygen therapy device of fraction of inspired oxygen |
| CN109303959A (en) * | 2018-10-26 | 2019-02-05 | 北京怡和嘉业医疗科技股份有限公司 | The control method of ventilation therapy equipment and ventilation therapy equipment |
| CN209253872U (en) * | 2018-12-13 | 2019-08-16 | 彭艳 | It is a kind of to facilitate the breathing apparatus for cardiovascular department for adjusting oxygen amount |
| CN111375110A (en) * | 2018-12-29 | 2020-07-07 | 罗远明 | Gas inhalation device capable of keeping concentration of gas entering respiratory tract constant and having no respiratory resistance |
| CN113117206A (en) * | 2019-12-31 | 2021-07-16 | 罗远明 | Inhalation device for preventing and treating altitude stress |
| CN214232339U (en) * | 2020-03-25 | 2021-09-21 | 沈丹 | Oxygenation equipment for severe respiration |
| CN114403995A (en) * | 2021-12-16 | 2022-04-29 | 江南大学附属医院 | Tidal volume controllable breathing amplitude control mask |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US9884159B2 (en) | Method and system for controlling breathing | |
| JP3043810B2 (en) | Respiratory calorimeter with bidirectional flow monitor | |
| AU757615B2 (en) | Patient monitor and method of using same | |
| US6849049B2 (en) | Patient monitor and method of using same | |
| US20100106037A1 (en) | Method and device for determining cardiac output with carbon dioxide partial re-breathing | |
| US20050121033A1 (en) | Respiratory monitoring during gas delivery | |
| JP2000070370A (en) | Artificial respiratory apparatus | |
| BRPI0616155A2 (en) | system and method of administering a pharmaceutical gas to a patient | |
| JP2010531685A (en) | Gas mixing device for airway maintenance system | |
| CN110404145B (en) | Oxygen therapy device with accurately adjustable inhaled oxygen concentration and without carbon dioxide retention | |
| CN108062976A (en) | Breathing equipment and the operation method for carrying the breathing equipment of definite coughing fit | |
| CN220801650U (en) | Comfortable device capable of accurately controlling concentration of inhaled air and simultaneously detecting respiratory flow | |
| US11865262B2 (en) | Oxygen therapy administration methods and related apparatus | |
| JP3020606B2 (en) | Oxygen consumption meter | |
| CN116271378A (en) | Comfortable device capable of accurately controlling concentration of inhaled air and simultaneously detecting respiratory flow | |
| US20230116240A1 (en) | Improvements relating to gas monitoring | |
| KR102586589B1 (en) | Smart inhaler system and method combined with drug monitoring inhaler and spirometer for asthma patients | |
| US20230372657A1 (en) | Oxygen therapy administration methods and related apparatus | |
| RU18917U1 (en) | ARTIFICIAL LUNG VENTILATION DEVICE | |
| AU2022332689A1 (en) | Method and system of monitoring oxygen | |
| CN117529347A (en) | Device and system for PPV therapy and CPAP therapy | |
| AU2017202586A1 (en) | System and method of administering a pharmaceutical gas to a patient | |
| WO2015002662A1 (en) | Method and system for controlling breathing |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination |