CA2112884C - Inhalation/exhalation respiratory phase detection circuit - Google Patents
Inhalation/exhalation respiratory phase detection circuitInfo
- Publication number
- CA2112884C CA2112884C CA002112884A CA2112884A CA2112884C CA 2112884 C CA2112884 C CA 2112884C CA 002112884 A CA002112884 A CA 002112884A CA 2112884 A CA2112884 A CA 2112884A CA 2112884 C CA2112884 C CA 2112884C
- Authority
- CA
- Canada
- Prior art keywords
- signal
- signals
- set forth
- phases
- producing
- 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.)
- Expired - Lifetime
Links
- 230000000241 respiratory effect Effects 0.000 title claims abstract description 46
- 238000001514 detection method Methods 0.000 title abstract description 16
- 238000004519 manufacturing process Methods 0.000 claims description 13
- 238000000034 method Methods 0.000 claims description 11
- 230000000875 corresponding effect Effects 0.000 claims description 8
- 230000003111 delayed effect Effects 0.000 claims description 7
- 230000001276 controlling effect Effects 0.000 claims description 6
- 230000002596 correlated effect Effects 0.000 claims description 4
- 230000029058 respiratory gaseous exchange Effects 0.000 claims description 4
- 230000001747 exhibiting effect Effects 0.000 claims description 2
- 230000007704 transition Effects 0.000 abstract description 8
- 239000007789 gas Substances 0.000 description 16
- 239000003990 capacitor Substances 0.000 description 6
- 230000035945 sensitivity Effects 0.000 description 6
- 210000003205 muscle Anatomy 0.000 description 4
- 208000001797 obstructive sleep apnea Diseases 0.000 description 4
- ORILYTVJVMAKLC-UHFFFAOYSA-N Adamantane Natural products C1C(C2)CC3CC1CC2C3 ORILYTVJVMAKLC-UHFFFAOYSA-N 0.000 description 2
- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 description 2
- 230000008859 change Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 229910052760 oxygen Inorganic materials 0.000 description 2
- 230000004044 response Effects 0.000 description 2
- 206010021079 Hypopnoea Diseases 0.000 description 1
- 101100001347 Mus musculus Akt1s1 gene Proteins 0.000 description 1
- 208000036366 Sensation of pressure Diseases 0.000 description 1
- 206010041235 Snoring Diseases 0.000 description 1
- 238000009825 accumulation Methods 0.000 description 1
- 230000037007 arousal Effects 0.000 description 1
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 1
- 229910002092 carbon dioxide Inorganic materials 0.000 description 1
- 239000001569 carbon dioxide Substances 0.000 description 1
- 230000001143 conditioned effect Effects 0.000 description 1
- 229920005994 diacetyl cellulose Polymers 0.000 description 1
- 238000009499 grossing Methods 0.000 description 1
- 238000007689 inspection Methods 0.000 description 1
- 230000003434 inspiratory effect Effects 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 239000001301 oxygen Substances 0.000 description 1
- 230000003252 repetitive effect Effects 0.000 description 1
- 208000019116 sleep disease Diseases 0.000 description 1
- 208000020685 sleep-wake disease Diseases 0.000 description 1
- 229920003002 synthetic resin Polymers 0.000 description 1
- 239000000057 synthetic resin Substances 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
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
- A61M16/20—Valves specially adapted to medical respiratory devices
-
- 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
- A61M16/024—Control means therefor including calculation means, e.g. using a processor
-
- 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
- A61M16/0666—Nasal cannulas or tubing
- A61M16/0672—Nasal cannula assemblies for oxygen therapy
- A61M16/0677—Gas-saving devices 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
- A61M16/20—Valves specially adapted to medical respiratory devices
- A61M16/201—Controlled valves
- A61M16/202—Controlled valves electrically actuated
- A61M16/203—Proportional
- A61M16/204—Proportional used for inhalation control
-
- 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
- A61M16/203—Proportional
- A61M16/205—Proportional used for exhalation control
-
- H—ELECTRICITY
- H03—ELECTRONIC CIRCUITRY
- H03K—PULSE TECHNIQUE
- H03K5/00—Manipulating of pulses not covered by one of the other main groups of this subclass
- H03K5/01—Shaping pulses
- H03K5/08—Shaping pulses by limiting; by thresholding; by slicing, i.e. combined limiting and thresholding
- H03K5/082—Shaping pulses by limiting; by thresholding; by slicing, i.e. combined limiting and thresholding with an adaptive threshold
- H03K5/086—Shaping pulses by limiting; by thresholding; by slicing, i.e. combined limiting and thresholding with an adaptive threshold generated by feedback
- H03K5/088—Shaping pulses by limiting; by thresholding; by slicing, i.e. combined limiting and thresholding with an adaptive threshold generated by feedback modified by switching, e.g. by a periodic signal or by a signal in synchronism with the transitions of the output signal
-
- 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
- A61M2016/0015—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors
- A61M2016/0018—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical
- A61M2016/0021—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical with a proportional output signal, e.g. from a thermistor
Abstract
An apparatus (10) for controlling the pressure of a respiratory gas delivered to a patient includes a phase detection circuit (24) for determining the inhalation and exhalation phases of the patient's respiratory cycle.
More particularly, a flow signal representative of the respiratory flow is compared to second signal, offset in time and scaled in magnitude relative to the flow signal, in order to determine the transition from one phase to the next.
More particularly, a flow signal representative of the respiratory flow is compared to second signal, offset in time and scaled in magnitude relative to the flow signal, in order to determine the transition from one phase to the next.
Description
~21 1~8~1 I~R~T~TION/FX~TION RESPIRATORY PRAS~ DETECTION CIRC~I~
BAc~ground of the Invention 1. Field of the Invention The present invention is concerned with an apparatus for controlling the pressure of a respiratory gas delivered to a patient. More particularly, the preferred apparatus includes a trigger circuit for determining the inhalation and exhalation phases of the patient's respiratory cycle.
BAc~ground of the Invention 1. Field of the Invention The present invention is concerned with an apparatus for controlling the pressure of a respiratory gas delivered to a patient. More particularly, the preferred apparatus includes a trigger circuit for determining the inhalation and exhalation phases of the patient's respiratory cycle.
2. Description of the Prior Art obstructive sleep apnea is a sleep disorder characte-rized by relaxation of the airway including the genioglos-sus throat muscle during sleep. When this occurs, the relaxed muscle can partially or completely block the patient's airway. Partial blockage can result in snoring or hypopnea. Complete blockage results in obstructive sleep apnea.
When complete blockage occurs, the patient's inhala-tion efforts do not result in the intake of air and the patient becomes oxygen deprived. In reaction the patient begins to awaken. Upon reaching a nearly awakened state, the genioglossus muscle resumes normal tension which clears the airway and allows inhalation to occur. The patient then falls back into a deeper sleep whereupon the genioglossus muscle again relaxes and the apneic cycle repeats. In consequence, the patient does not achieve a fully relaxed deep sleep session because of the repetitive arousal to a nearly awakened state. People with obstructive sleep apnea are continually tired even after an apparently normal night's sleep.
In order to treat obstructive sleep apnea, a system of continuous positive airway pressure (CPAP) has been devised in which a prescribed level of positive airway pressure is - continuously imposed on the patient's airway. The presence - 2 - ~ ~ 12~8~ ~
of such positive pressure provides a pressure splint to the airway in order to offset the negative inspiratory pressure that can draw the relaxed airway tissues into an occlusive state. The most desired device for achieving a positive airway connection is the use of a nasal pillow such as that disclosed in U.S. Pat. No. 4,782,832. The nasal pillow seals with the patient's nares and imposes the positive airway pressure by way of the nasal passages. The nasal pillow also includes a small vent for continuously exhausting a small amount of air in order to prevent carbon dioxide and moisture accumulation.
In the CPAP system, the patient must exhale against the prescribed positive pressure. This can result in patient discomfort, especially at the higher pressure levels. Because of this problem, the so-called bi-level positive airway pressure (BiPAP) system has been developed in which the pressure is lowered during the exhalation phase of the respiratory cycle. Practical implementation of the BiPAP
system has met with only marginal success because of the difficulty in accurately and reliably detecting the occurrence of the exhalation and inhalation phases of the respiratory cycle. Respiratory phase detection has been a problem because the continual air exhaust at the nasal pillow, and other system leaks, results in a net positive air flow to the patient. Thus, phase transition cannot be determined merely on the basis of a change in the direction of air flow.
iB
8 ~ 4 Summary of the Invention The apparatus of the present invention solves the prior art problems discussed above and provldes a distinct advance in the state of the art. More particularly, the apparatus hereof reliably determines inhalation and exhalation phases in the respiratory cycle in order to control respiratory gas pressure in response.
The preferred embodiment of the invention hereof includes a gas supply for supplying a respiratory gas under pressure from a source thereof to a patient, a phase detection circuit for detecting the inhalation and exhalation respiratory phases, and a pressure controller for controlling the pressure delivered to the patient in a predetermined manner correlated with the respiratory phases.
The preferred phase detection circuit produces first and second signals representative of respiratory gas flow with these signals being time displaced relative to one another and scaled in magnitude. With this configuration, the signals present different gains and voltage offsets relative to one another during respective phases of the respiratory cycle.
These two signals are compared to determine transitions, which correlate with transitions from one respiratory phase to another. With reliable phase detection, the gas pressure delivered to the patient is controlled in accordance with the phases.
In accordance with the present invention, there is _ 62948-185 r~
~ .
3a ~ 8 4 provided an apparatus for detecting the inhalation and exhalation phases of a respiratory cycle having associated respiratory gas flow, said apparatus comprising: signal production means for producing first and second signals representative of the respiratory gas flow with said signals being time displaced relative to one another and with said signals having respective amplitudes so that one of said signals presents the greater amplitude during at least a portion of one of the phases and so that the other of said signals presents the greater amplitude during at least a portion of the other of said phases; and processing means for processing said signals for determining therefrom the occurrence of said respective phases and for producing outputs representative of said phases.
In accordance with the present invention, there is further provided an apparatus for facilitating the respiration of a patient having a respiratory cycle with associated respiratory gas flow and exhibiting inhalation and exhalation phases, said apparatus comprising: supply means for supplying a respiratory gas under pressure from a source thereof to a patient; means for producing first and second signals representative of the respiratory gas flow with said signals being time displaced relative to one another and with said signals having respective amplitude so that one of said signals presents the greater amplitude during at least a portion of one of the phases and so that the other of said 3b signals presents the greater amplitude during at least a portion of the other of said phases; processing means for processing said signals for determining therefrom the occurrence of said respective phases and for producing outputs representative of said phases; control means coupled with said supply means and said processing means for receiving said outputs and responsive thereto for controlling said respiratory gas pressure to the patient in a predetermined manner correlated with said phases.
In accordance with the present invention, there is further provided a method for detecting the inhalation and exhalation phases of a respiratory cycle having associated respiratory gas flow, said method comprising: producing first and second signals representative of the respiratory gas flow from a signal production means, said signals being time displaced relative to one another, said signals having respective amplitudes, said first signal presents the greater amplitude during at least a portion of the inhalation phase, said second signal presents the greater amplitude during at least a portion of the exhalation phase; and processing said signals with a processing means for determining the occurrence of said inhalation and exhalation phases and for producing a first output corresponding to the inhalation phase and a second output corresponding to the exhalation phase.
Brief Description of the Drawings Figure 1 is a schematic representation of the B~
3c _-preferred apparatus for facilitating the respiration of a patient;
Figure 2 is an electrical schematic of the preferred phase detection circuit of the apparatus of Fig. 1;
Figure 3 is a graph illustrating the flow and offset signals of the detection circuit of Fig. 2 and illustrating patient inhalation and exhalation phases;
Figure 4 is an electrical block diagram illustrating the preferred pressure controller of Fig. 1;
, .! ~
2112~8~
Fig. 5 is an exploded perspèctive view of the major components of the preferred valve of Fig. 1;
Fig. 6 is a lower perspective view of the inlet/outlet housing of the valve of Fi~. 5;
- Fig. 7 is a partial sectional view of the assembled valve of Fig. 5 illustrating the shiftable components in a first position;
Fig. 8 is a partial sectional view of the assembled valve of Fig. 5 illustrating the shiftable components in a second position;
Fig. 9 is a perspective view of a second embodiment of the valve of Fig. 1;
Fig. 10 is a cut-away perspective view of the valve of Fig. 9; and Fig. 11 is a sectional view of the valve of Fig. 9.
Detailed Descri~tion of the Preferred ~mbodiment Referring initially to Fig. 1, apparatus 10 includes gas source 12, control valve 14, pressure sensor 16 and Zo flow sensor 18 coupled with a so-called ADAM circuit available from Puritan Bennett Corp. of Lenexa, Kansas, which includes pneumatic hose 20 and nasal pillow 22.
Apparatus 10 further includes phase detection circuit 24 and pressure controller 26. In the preferred embodiment, components 12-18 and 24-28 are enclosed in a single housing to which the ADAM circuit is coupled.
Gas source is preferably a variable speed blower operable to produce 120 liters per minute at 30 cm. water pressure. The preferred pressure sensor 16 is available from Sensym Company as model number SCX01. Flow sensor 18 is preferably model AWM2300 available from Microswitch Corp., transducer operable for producing an electrical signal on line 30 representative of the air flow there-through and thereby representative of the air flow deliv-ered to the patient.
Fig. 2 is an electrical schematic of phase detection circuit Z4 which includes signal production circuit 32 and signal processing circuit 34. Signal production circuit 32 receives the flow signal from flow sensor 18 by way of line 30. This signal is filtered for noise and other transients by resistor R1 (22K) and capacitor Cl (luF) connected as shown in Fig. 2 and delivered as signal "S" to signal processing circuit 34.
Signal production circuit 32 also transforms the flow sensor signal into an offset signal "Sd" which is delayed in time and scaled in magnitude relative to signal S.
Initially the flow sensor signal is time delayed by 200 milliseconds using resistor R2 (lOOK) and capacitor C2 (2.2 uF) interconnected as shown. The relative time delay between time signals S and Sd is illustrated by the graphs in Fig. 3.
The time delayed signal is then delivered to the positive input terminal of amplifier Al (type 358A) with the output therefrom connected as feedback to a negative input terminal. The output of amplifier Al is also connect-ed to output resistor R3 (221K). Amplifier Al functions as a voltage follower to provide a high impedance input to the flow signal.
The conditioned time delay signal is then processed to scale the magnitude thereof so that signal Sd presents lower amplitude than signal S during the inhalation phase, and so that signal Sd presents a higher amplitude than signal S during the exhalation phase as illustrated in Fig.
When complete blockage occurs, the patient's inhala-tion efforts do not result in the intake of air and the patient becomes oxygen deprived. In reaction the patient begins to awaken. Upon reaching a nearly awakened state, the genioglossus muscle resumes normal tension which clears the airway and allows inhalation to occur. The patient then falls back into a deeper sleep whereupon the genioglossus muscle again relaxes and the apneic cycle repeats. In consequence, the patient does not achieve a fully relaxed deep sleep session because of the repetitive arousal to a nearly awakened state. People with obstructive sleep apnea are continually tired even after an apparently normal night's sleep.
In order to treat obstructive sleep apnea, a system of continuous positive airway pressure (CPAP) has been devised in which a prescribed level of positive airway pressure is - continuously imposed on the patient's airway. The presence - 2 - ~ ~ 12~8~ ~
of such positive pressure provides a pressure splint to the airway in order to offset the negative inspiratory pressure that can draw the relaxed airway tissues into an occlusive state. The most desired device for achieving a positive airway connection is the use of a nasal pillow such as that disclosed in U.S. Pat. No. 4,782,832. The nasal pillow seals with the patient's nares and imposes the positive airway pressure by way of the nasal passages. The nasal pillow also includes a small vent for continuously exhausting a small amount of air in order to prevent carbon dioxide and moisture accumulation.
In the CPAP system, the patient must exhale against the prescribed positive pressure. This can result in patient discomfort, especially at the higher pressure levels. Because of this problem, the so-called bi-level positive airway pressure (BiPAP) system has been developed in which the pressure is lowered during the exhalation phase of the respiratory cycle. Practical implementation of the BiPAP
system has met with only marginal success because of the difficulty in accurately and reliably detecting the occurrence of the exhalation and inhalation phases of the respiratory cycle. Respiratory phase detection has been a problem because the continual air exhaust at the nasal pillow, and other system leaks, results in a net positive air flow to the patient. Thus, phase transition cannot be determined merely on the basis of a change in the direction of air flow.
iB
8 ~ 4 Summary of the Invention The apparatus of the present invention solves the prior art problems discussed above and provldes a distinct advance in the state of the art. More particularly, the apparatus hereof reliably determines inhalation and exhalation phases in the respiratory cycle in order to control respiratory gas pressure in response.
The preferred embodiment of the invention hereof includes a gas supply for supplying a respiratory gas under pressure from a source thereof to a patient, a phase detection circuit for detecting the inhalation and exhalation respiratory phases, and a pressure controller for controlling the pressure delivered to the patient in a predetermined manner correlated with the respiratory phases.
The preferred phase detection circuit produces first and second signals representative of respiratory gas flow with these signals being time displaced relative to one another and scaled in magnitude. With this configuration, the signals present different gains and voltage offsets relative to one another during respective phases of the respiratory cycle.
These two signals are compared to determine transitions, which correlate with transitions from one respiratory phase to another. With reliable phase detection, the gas pressure delivered to the patient is controlled in accordance with the phases.
In accordance with the present invention, there is _ 62948-185 r~
~ .
3a ~ 8 4 provided an apparatus for detecting the inhalation and exhalation phases of a respiratory cycle having associated respiratory gas flow, said apparatus comprising: signal production means for producing first and second signals representative of the respiratory gas flow with said signals being time displaced relative to one another and with said signals having respective amplitudes so that one of said signals presents the greater amplitude during at least a portion of one of the phases and so that the other of said signals presents the greater amplitude during at least a portion of the other of said phases; and processing means for processing said signals for determining therefrom the occurrence of said respective phases and for producing outputs representative of said phases.
In accordance with the present invention, there is further provided an apparatus for facilitating the respiration of a patient having a respiratory cycle with associated respiratory gas flow and exhibiting inhalation and exhalation phases, said apparatus comprising: supply means for supplying a respiratory gas under pressure from a source thereof to a patient; means for producing first and second signals representative of the respiratory gas flow with said signals being time displaced relative to one another and with said signals having respective amplitude so that one of said signals presents the greater amplitude during at least a portion of one of the phases and so that the other of said 3b signals presents the greater amplitude during at least a portion of the other of said phases; processing means for processing said signals for determining therefrom the occurrence of said respective phases and for producing outputs representative of said phases; control means coupled with said supply means and said processing means for receiving said outputs and responsive thereto for controlling said respiratory gas pressure to the patient in a predetermined manner correlated with said phases.
In accordance with the present invention, there is further provided a method for detecting the inhalation and exhalation phases of a respiratory cycle having associated respiratory gas flow, said method comprising: producing first and second signals representative of the respiratory gas flow from a signal production means, said signals being time displaced relative to one another, said signals having respective amplitudes, said first signal presents the greater amplitude during at least a portion of the inhalation phase, said second signal presents the greater amplitude during at least a portion of the exhalation phase; and processing said signals with a processing means for determining the occurrence of said inhalation and exhalation phases and for producing a first output corresponding to the inhalation phase and a second output corresponding to the exhalation phase.
Brief Description of the Drawings Figure 1 is a schematic representation of the B~
3c _-preferred apparatus for facilitating the respiration of a patient;
Figure 2 is an electrical schematic of the preferred phase detection circuit of the apparatus of Fig. 1;
Figure 3 is a graph illustrating the flow and offset signals of the detection circuit of Fig. 2 and illustrating patient inhalation and exhalation phases;
Figure 4 is an electrical block diagram illustrating the preferred pressure controller of Fig. 1;
, .! ~
2112~8~
Fig. 5 is an exploded perspèctive view of the major components of the preferred valve of Fig. 1;
Fig. 6 is a lower perspective view of the inlet/outlet housing of the valve of Fi~. 5;
- Fig. 7 is a partial sectional view of the assembled valve of Fig. 5 illustrating the shiftable components in a first position;
Fig. 8 is a partial sectional view of the assembled valve of Fig. 5 illustrating the shiftable components in a second position;
Fig. 9 is a perspective view of a second embodiment of the valve of Fig. 1;
Fig. 10 is a cut-away perspective view of the valve of Fig. 9; and Fig. 11 is a sectional view of the valve of Fig. 9.
Detailed Descri~tion of the Preferred ~mbodiment Referring initially to Fig. 1, apparatus 10 includes gas source 12, control valve 14, pressure sensor 16 and Zo flow sensor 18 coupled with a so-called ADAM circuit available from Puritan Bennett Corp. of Lenexa, Kansas, which includes pneumatic hose 20 and nasal pillow 22.
Apparatus 10 further includes phase detection circuit 24 and pressure controller 26. In the preferred embodiment, components 12-18 and 24-28 are enclosed in a single housing to which the ADAM circuit is coupled.
Gas source is preferably a variable speed blower operable to produce 120 liters per minute at 30 cm. water pressure. The preferred pressure sensor 16 is available from Sensym Company as model number SCX01. Flow sensor 18 is preferably model AWM2300 available from Microswitch Corp., transducer operable for producing an electrical signal on line 30 representative of the air flow there-through and thereby representative of the air flow deliv-ered to the patient.
Fig. 2 is an electrical schematic of phase detection circuit Z4 which includes signal production circuit 32 and signal processing circuit 34. Signal production circuit 32 receives the flow signal from flow sensor 18 by way of line 30. This signal is filtered for noise and other transients by resistor R1 (22K) and capacitor Cl (luF) connected as shown in Fig. 2 and delivered as signal "S" to signal processing circuit 34.
Signal production circuit 32 also transforms the flow sensor signal into an offset signal "Sd" which is delayed in time and scaled in magnitude relative to signal S.
Initially the flow sensor signal is time delayed by 200 milliseconds using resistor R2 (lOOK) and capacitor C2 (2.2 uF) interconnected as shown. The relative time delay between time signals S and Sd is illustrated by the graphs in Fig. 3.
The time delayed signal is then delivered to the positive input terminal of amplifier Al (type 358A) with the output therefrom connected as feedback to a negative input terminal. The output of amplifier Al is also connect-ed to output resistor R3 (221K). Amplifier Al functions as a voltage follower to provide a high impedance input to the flow signal.
The conditioned time delay signal is then processed to scale the magnitude thereof so that signal Sd presents lower amplitude than signal S during the inhalation phase, and so that signal Sd presents a higher amplitude than signal S during the exhalation phase as illustrated in Fig.
3. To accomplish this, the gain of the signal is changed independently for the inhalation and exhalation portions of 2112~81 -the signal and a variable offset is added by the sensi-tivity potentiometers R4 and R9.
As discussed further hereinbelow, the output from phase detection circuit 24 produces a logic high output during exhalation and a logic low during inhalation. These outputs are also provided as feedback to signal production circuit 32, specifically to control terminal C of CMOS
inhalation switch Sl and to control terminal C of CMOS
switch S2. These CMOS switches are type 4066B and operate so that when a logic high input is provided to terminal C, the switch is "on," that is, connection is made between ~ terminals "I and "O" thereof. When terminal C is low, the connection between terminals I and O is open.
During inhalation, terminal C of switch S1 is low and the switch is off. Voltage is then supplied to the negative input terminal of amplifier A2 (type 358A) by way of inhale sensitivity potentiometer R4 (500 Ohms full scale), resis-tor R5 (lOK) and resistor R6 (221K). Resistor R7 (221K) interconnects the output of amplifier A2 with the negative input terminal thereof. The level of the voltage delivered to negative input terminal of amplifier A2 determines the amplitude scaling of the delayed flow sensor signal deliv-ered to the positive input terminal. More specifically, potentiometer R4 is adjusted to provide the desired offset of output signal Sd relative to signal S during inhalation.
Also during inhalation, the logic low signal is delivered to terminal C of switch S2, which turns this switch off. In turn, a logic high signal is imposed on terminal C of CMOS switch S3 by way of resistor R8 (10K).
This turns on switch S3 which imposes ground potential on the voltage output from potentiometer R9 and resistor R10 and thereby disables the exhale sensitivity portion of the circuit.
21128~
During exhalation, a logic high signal is delivered to terminal C of switch Sl which then turns on and imposes ground potential on the voltage output from potentiometer R4 and resistor R5 in order to disable the inhalation sensitivity portion of the circuit. The logic high exhala-tion signal also turns on switch S2 which imposes ground potential on the voltage output from resistor R8. In turn, switch S3 turns off. This allows exhale sensitivity voltage to be delivered to the positive input terminal of amplifier A2 by way of exhale sensitivity potentiometer R9 (500 Ohms full scale), resistor R10 (lOK) and resistor Rll (Z21K).
Potentiometer R9 is adjusted to provide the desired offset of signal Sd relative to signal S during inhalation.
As illustrated in the graph of Fig. 3, signal produc-tion circuit 32 produces signals S and Sd so that the voltage level of signal Sd is less than that of signal S
during inhalation. Conversely, the voltage level of signal S is less than that of signal Sd during exhalation.
Signal processing circuit 34 receives signals S and Sd and compares these signals to determine the occurrence of the inhalation and exhalation phases of the respiratory cycle. Specifically, signal S is received at the negative input terminal of comparator A3 (type 358A) and signal Sd is received at the positive input terminal thereof by way of resistor R12 (100K). When the voltage level of signal S
is greater than that of signal Sd, the output from compara-tor A3 is logic low and inhalation is indicated thereby.
When the voltage level of signal Sd is the greater of the two, comparator A3 output goes high and exhalation is indicated.
Resistor R13 (100X), resistor R14 (lOm), and capacitor C3 (2.2 uF) are interconnected with comparator A3 as illus-trated in Fig. 2 and provide a signal blanking interval after a transition in the output of comparator A3. More particularly, resistor R13 and capacitor C3 provide in-creased voltage hysteresis in the delivery of feedback from the output to the positive input terminal of comparator A3 in order to eliminate false triggering due to transients, noise or the like. Capacitor C4 (lOO nF) provides input smoothing for the supply voltage delivered to comparator A3.
An inspection of the graphs of signals S and Sd in Fig. 3 illustrates crossover points 36 and 38, and artifact 40 at the inhalation peak in signal Sd. Crossover points 36,38 are determined by the time delay imposed by resistor R2 and capacitor C2, by the amplitude scaling, and by the offset voltages which can be adjusted by potentiometers R4 and R9 for the respective phases. Artifact 40 corresponds to the phase change from inhalation and exhalation, and occurs because of the transition of signal production circuit 32 between the inhalation and exhalation offset modes. The time delay from crossover 36 to artifact 40 corresponds to the blanking interval determined by the hysteresis of comparator A3 as set by resistors R12, R13 and R14. Phase detection circuit 24 provides an output on line 42 representative of the inhalation and exhalation phases of the patient. More particularly, circuit 24 provides a logic high output at +10 VDC during exhalation and a logic low output at O volts during inhalation.
Fig. 4 is an electrical block diagram illustrating pressure controller 26, control valve 14 and pressure sensor 16. In general, controller 26 receives signals from phase detection circuit 24 and pressure sensor 16 and, in response, operates valve 14 to maintain the respective inhalation and exhalation pressures delivered to the patient.
~ 2112884 g Pressure sensor 16 p~ovides a pair of differential voltage signals to the corresponding inputs of differential amplifier 44 that responds by providing a voltaqe output (Vp) to error detector 46 representative of the pressure being delivered to the patient. Conventional error detector 46 compares the pressure signal Vp with a set point pres-sure signal Vs in order to produce error signal Ve.
Set point signal Vs is produced by digital-to-analog converter (DAC) 48, DAC 50 and CMOS switch 52. DAC 48 lo receives a digital input representative of the desired exhalation positive air pressure (EPAP) by way of a set of five DIP switches 54, and converts the digital output to a representative analog signal delivered to terminal I2 of switch 52. Similarly, DAC 50 receives its digital input for inhalation positive air pressure (IPAP) from a set of five DIP switches 56, and delivers its analog output to terminal Il of switch 52. Control terminal C is connected to line 42 and receives the inhalation and exhalation signals from phase detection circuit 24. During exhalation, the +10 VDC
signal received at terminal C activates switch 52 to provide the EPAP voltage at terminal I2 as the output Vs.
During inhalation, the logic low signal at terminal C
causes switch 52 to provide the IPAP voltage at terminal I1 as the output Vs.
Error signal Ve is provided to interface 58 which is a conventional interface circuit designed to transform error signal Ve into a signal Vc compatible with valve 14 according to the specifications supplied by the manufac-turer. Signal Vc is delivered to power amplifier 66 and is inverted as a corresponding input to power amplifier 68.
The net result is a differential voltage output from amplifiers 66 and 68 which is delivered to the terminals of the valve motor of control valve 14, as explained further hereinbelow.
Figs. 5-8 illustrate preferred control valve 14, which includes valve base 70, shiftable valve element 72 and valve element cover 74. Valve base 70 includes housing 76 and valve motor 78 having motor shaft 80 with locking hole 81 defined in the end thereo~.
Housing 76 is preferably composed of synthetic resin material having a generally cylindrical configuration and lo presents upper and lower sections 82 and 84. Upper section 82 includes upper face 86 having centrally defined opening 88 for receiving motor shaft 80, which extends upwardly therethrough. Sidewalls 90 of upper section 82 present a slightly smaller diameter than sidewalls 92 of lower section 84 and thereby define shelf 94 for supporting valve cover 74. Housing 76 also includes three, outwardly and upwardly opening recesses 96a, 96b and 96c presenting a generally trapezoidal configuration in cross section. Each recess is defined by lower wall 98, and side walls 100, 102 and 104. Additionally, upper section sidewalls 90 include three outwardly locking bosses 106 located midway between adjacent recesses 96a-c.
Integral valve element 72 includes frusto-conically shaped hub 108, support ring 110, three, pie-shaped, equally spaced, support bodies 114a, 114b and 114C inter-connecting hub 108 and support ring 110, and three, rectan-gularly shaped valve fingers 116a, 116b and 116c equally spaced about the periphery of hub 108 and extending upward-ly therefrom. Hub 108 includes hole 118 defined in the lower surface thereof for receiving motor shaft 80. Addi-tionally, hub 108 includes aperture 120 centrally defined through the upper surface thereof for receiving a locking screw therethrough which is further received in motor shaft locking hole 81 for securing element 72 to shaft 80. Hub 108, rlng 110 and support bodies 114a-c define three, equally spaced, exhaust ports 122a, 122b and 122c present-ing a shape congruent with ~ecesses 96a-c and configured for registration therewith.
Valve element cover 74 includes inverted cup shaped member 124, presenting sidewall 126 and top wall 128, and further includes inlet tube 130, outlet tube 132 and valve fingers 134a, 134b and 134c. Inlet tube 130 is coaxial with lo cup shaped member 124 at top wall 128 while outlet tube 132 ex~ends outwardly from sidewall 126. Equally spaced fingers ~ 134a-c depend downwardly from inner surface 136 of top wall 128 and are configured intercalate with fingers 116a-c and with the spaces therebetween. Tubular member further includes spaced slots 138 defined in the lower edge of sidewall 126 and configured to register with a correspond-ing locking boss L06 in o-der to secure cover 74 to valve base 70.
Figs. 7 and 8 illustrate assembled control valve 14 with valve fingers 134a-c of cover 74 fitting concentric-ally about valve fingers 116a-c of rotatable element 72. In operation, pressure controller 26 energizes valve motor 78 in order to rotate element 72 clock-wise or counter clock-wise between a fully closed position (Fig. 7), a fully opened position (Fig. 8), and intermediate positions therebetween.
In the fully closed position of Fig. 7, fingers 116a-c and 134a-c are fully meshed in order to block the respec-tive spaces and ports 122 are in complete registration with recesses 96a-c. In this position, all of the air entering inlet tube 130 from source 12 exhausts through ports 122a-c and recesses 96a-c. In the fully open position of Fig. 8, fingers 116a-c and 134a-c are in registration so that the i~- 211288~
spaces therebetween are open, and support bodies 114a-c are in registration with and thereby block recesses 96a-c. With this orientation, all of the air is exAausted through outlet tube 132 for delivery to the patient.
The intermediate positions between fully opened and fully closed allow respective portions of the inlet air to exhaust through recesses 96a-c and through outlet tube 132.
In this way, control valve 14 provides more precise control over the pressure delivered to the patient, and provides lo smoother transition between pressure settings.
In the operation of apparatus 10 during inhalation, it is necessary to provide sufficient pressure to maintain the airway pressure splint in the patient in order to prevent occlusion. For patient comfort, however, it is desirable to lower the pressure to a level as low as possible, including ambient pressure, while still maintaining sufficient pressure to keep the airway open. In order to accomplish these benefits, phase detection circuit 24 detects the inhalation and exhalation phases of the patient's respira-tion, and provides corresponding outputs to pressure con-troller 14. In the preferred embodiment, controller 14 controls its output pressure in a predetermined manner correlated with inhalation and exhalation as indicated by the outputs received from circuit 24. More particularly, pressure controller 14 controls the pressure delivered to the patient at a higher level during inhalation and a lower level during exhalation as determined by the settings on DACs 48,50. Typically, the respective inhalation and exhalation pressure levels are prescribed by the patient's physician.
Figs. 9-11 illustrate control valve 140 which is another embodiment of a control valve for use in place of valve 14. Valve 140 includes valve body 142 and actuator 2112~84 assembly 144. Valve body 142 includes external tubular inlet coupler 146 in communication with inlet passaqe 148, and further ~ncludes exhaust passage 150 and outlet passage 152 having external outlet coupler 154 extending therefrom.
As illustrated in Figs. 10-11, exhaust and outlet passages 150,152 communicate with inlet passage 148 and extend -ransversely therefrom, parallel to one another.
~ctuator assembly 144 includes valve motor 156, valve stem 158, exhaust valve element 160 and outlet valve iO element 162. As illustrated in Figs. 9-11, motor 156 is coupled to the bottom of body 142 with motor-actuated stem 158 extending upwardly therefrom through, and transverse ~o, exhaust and outlet passages 150,152. Valve elements 160,162 present oval-shaped configurations and are coupled with stem 158 for rotation therewith. Element 160 is positioned in exhaust passage 150, and element 152 is positioned in outlet passage 152. Valve elements 160,162 function in a manner analogous to conventional butterfly valves. As illustrated, valve elements 160,162 are angular-ly displaced from one another on stem 158 by about 45 .
Valve motor 156 is coupled electrically with pressure controller 26 and receives signals therefrom in the same manner as valve motor 78 or valve 14.
Figs. 10 and 11 illustrate control valve 140 in the closed/exhaust position. In this position, exhaust valve element 160 is positioned parallel to the air flow and outlet valve element 162 is positioned so that its edges engage the sidewalls of outlet passage 152 to block all outflow. In other words, all of the inlet air entering through inlet passage 148 would exhaust through exhaust passage 150 and none would be provided through outlet passage 152 to the patient. In the open/outlet position, elements 160 and 162 would be rotated clockwise as viewed -14- 211~84 from above until the edges of exhaust element 160 engage the walls defining exhaust passage 150. In this position, outlet element 162 is positioned parallel to the air flow through outlet passage 152. In this way, no air is ex-hausted but rather, the full supply is provided through outlet passage 152.
Motor 156 responds to the signals received from pressure controller 26 in order to position valve 140 in the closed or open positions or any intermediate position therebetween. As with control valve 14, this arrangement allows smooth controllable transition between the various ~ valve positions.
Having thus described the preferred embodiment of the present invention the following is claimed as new and desired to be secured by Letters Patent:
As discussed further hereinbelow, the output from phase detection circuit 24 produces a logic high output during exhalation and a logic low during inhalation. These outputs are also provided as feedback to signal production circuit 32, specifically to control terminal C of CMOS
inhalation switch Sl and to control terminal C of CMOS
switch S2. These CMOS switches are type 4066B and operate so that when a logic high input is provided to terminal C, the switch is "on," that is, connection is made between ~ terminals "I and "O" thereof. When terminal C is low, the connection between terminals I and O is open.
During inhalation, terminal C of switch S1 is low and the switch is off. Voltage is then supplied to the negative input terminal of amplifier A2 (type 358A) by way of inhale sensitivity potentiometer R4 (500 Ohms full scale), resis-tor R5 (lOK) and resistor R6 (221K). Resistor R7 (221K) interconnects the output of amplifier A2 with the negative input terminal thereof. The level of the voltage delivered to negative input terminal of amplifier A2 determines the amplitude scaling of the delayed flow sensor signal deliv-ered to the positive input terminal. More specifically, potentiometer R4 is adjusted to provide the desired offset of output signal Sd relative to signal S during inhalation.
Also during inhalation, the logic low signal is delivered to terminal C of switch S2, which turns this switch off. In turn, a logic high signal is imposed on terminal C of CMOS switch S3 by way of resistor R8 (10K).
This turns on switch S3 which imposes ground potential on the voltage output from potentiometer R9 and resistor R10 and thereby disables the exhale sensitivity portion of the circuit.
21128~
During exhalation, a logic high signal is delivered to terminal C of switch Sl which then turns on and imposes ground potential on the voltage output from potentiometer R4 and resistor R5 in order to disable the inhalation sensitivity portion of the circuit. The logic high exhala-tion signal also turns on switch S2 which imposes ground potential on the voltage output from resistor R8. In turn, switch S3 turns off. This allows exhale sensitivity voltage to be delivered to the positive input terminal of amplifier A2 by way of exhale sensitivity potentiometer R9 (500 Ohms full scale), resistor R10 (lOK) and resistor Rll (Z21K).
Potentiometer R9 is adjusted to provide the desired offset of signal Sd relative to signal S during inhalation.
As illustrated in the graph of Fig. 3, signal produc-tion circuit 32 produces signals S and Sd so that the voltage level of signal Sd is less than that of signal S
during inhalation. Conversely, the voltage level of signal S is less than that of signal Sd during exhalation.
Signal processing circuit 34 receives signals S and Sd and compares these signals to determine the occurrence of the inhalation and exhalation phases of the respiratory cycle. Specifically, signal S is received at the negative input terminal of comparator A3 (type 358A) and signal Sd is received at the positive input terminal thereof by way of resistor R12 (100K). When the voltage level of signal S
is greater than that of signal Sd, the output from compara-tor A3 is logic low and inhalation is indicated thereby.
When the voltage level of signal Sd is the greater of the two, comparator A3 output goes high and exhalation is indicated.
Resistor R13 (100X), resistor R14 (lOm), and capacitor C3 (2.2 uF) are interconnected with comparator A3 as illus-trated in Fig. 2 and provide a signal blanking interval after a transition in the output of comparator A3. More particularly, resistor R13 and capacitor C3 provide in-creased voltage hysteresis in the delivery of feedback from the output to the positive input terminal of comparator A3 in order to eliminate false triggering due to transients, noise or the like. Capacitor C4 (lOO nF) provides input smoothing for the supply voltage delivered to comparator A3.
An inspection of the graphs of signals S and Sd in Fig. 3 illustrates crossover points 36 and 38, and artifact 40 at the inhalation peak in signal Sd. Crossover points 36,38 are determined by the time delay imposed by resistor R2 and capacitor C2, by the amplitude scaling, and by the offset voltages which can be adjusted by potentiometers R4 and R9 for the respective phases. Artifact 40 corresponds to the phase change from inhalation and exhalation, and occurs because of the transition of signal production circuit 32 between the inhalation and exhalation offset modes. The time delay from crossover 36 to artifact 40 corresponds to the blanking interval determined by the hysteresis of comparator A3 as set by resistors R12, R13 and R14. Phase detection circuit 24 provides an output on line 42 representative of the inhalation and exhalation phases of the patient. More particularly, circuit 24 provides a logic high output at +10 VDC during exhalation and a logic low output at O volts during inhalation.
Fig. 4 is an electrical block diagram illustrating pressure controller 26, control valve 14 and pressure sensor 16. In general, controller 26 receives signals from phase detection circuit 24 and pressure sensor 16 and, in response, operates valve 14 to maintain the respective inhalation and exhalation pressures delivered to the patient.
~ 2112884 g Pressure sensor 16 p~ovides a pair of differential voltage signals to the corresponding inputs of differential amplifier 44 that responds by providing a voltaqe output (Vp) to error detector 46 representative of the pressure being delivered to the patient. Conventional error detector 46 compares the pressure signal Vp with a set point pres-sure signal Vs in order to produce error signal Ve.
Set point signal Vs is produced by digital-to-analog converter (DAC) 48, DAC 50 and CMOS switch 52. DAC 48 lo receives a digital input representative of the desired exhalation positive air pressure (EPAP) by way of a set of five DIP switches 54, and converts the digital output to a representative analog signal delivered to terminal I2 of switch 52. Similarly, DAC 50 receives its digital input for inhalation positive air pressure (IPAP) from a set of five DIP switches 56, and delivers its analog output to terminal Il of switch 52. Control terminal C is connected to line 42 and receives the inhalation and exhalation signals from phase detection circuit 24. During exhalation, the +10 VDC
signal received at terminal C activates switch 52 to provide the EPAP voltage at terminal I2 as the output Vs.
During inhalation, the logic low signal at terminal C
causes switch 52 to provide the IPAP voltage at terminal I1 as the output Vs.
Error signal Ve is provided to interface 58 which is a conventional interface circuit designed to transform error signal Ve into a signal Vc compatible with valve 14 according to the specifications supplied by the manufac-turer. Signal Vc is delivered to power amplifier 66 and is inverted as a corresponding input to power amplifier 68.
The net result is a differential voltage output from amplifiers 66 and 68 which is delivered to the terminals of the valve motor of control valve 14, as explained further hereinbelow.
Figs. 5-8 illustrate preferred control valve 14, which includes valve base 70, shiftable valve element 72 and valve element cover 74. Valve base 70 includes housing 76 and valve motor 78 having motor shaft 80 with locking hole 81 defined in the end thereo~.
Housing 76 is preferably composed of synthetic resin material having a generally cylindrical configuration and lo presents upper and lower sections 82 and 84. Upper section 82 includes upper face 86 having centrally defined opening 88 for receiving motor shaft 80, which extends upwardly therethrough. Sidewalls 90 of upper section 82 present a slightly smaller diameter than sidewalls 92 of lower section 84 and thereby define shelf 94 for supporting valve cover 74. Housing 76 also includes three, outwardly and upwardly opening recesses 96a, 96b and 96c presenting a generally trapezoidal configuration in cross section. Each recess is defined by lower wall 98, and side walls 100, 102 and 104. Additionally, upper section sidewalls 90 include three outwardly locking bosses 106 located midway between adjacent recesses 96a-c.
Integral valve element 72 includes frusto-conically shaped hub 108, support ring 110, three, pie-shaped, equally spaced, support bodies 114a, 114b and 114C inter-connecting hub 108 and support ring 110, and three, rectan-gularly shaped valve fingers 116a, 116b and 116c equally spaced about the periphery of hub 108 and extending upward-ly therefrom. Hub 108 includes hole 118 defined in the lower surface thereof for receiving motor shaft 80. Addi-tionally, hub 108 includes aperture 120 centrally defined through the upper surface thereof for receiving a locking screw therethrough which is further received in motor shaft locking hole 81 for securing element 72 to shaft 80. Hub 108, rlng 110 and support bodies 114a-c define three, equally spaced, exhaust ports 122a, 122b and 122c present-ing a shape congruent with ~ecesses 96a-c and configured for registration therewith.
Valve element cover 74 includes inverted cup shaped member 124, presenting sidewall 126 and top wall 128, and further includes inlet tube 130, outlet tube 132 and valve fingers 134a, 134b and 134c. Inlet tube 130 is coaxial with lo cup shaped member 124 at top wall 128 while outlet tube 132 ex~ends outwardly from sidewall 126. Equally spaced fingers ~ 134a-c depend downwardly from inner surface 136 of top wall 128 and are configured intercalate with fingers 116a-c and with the spaces therebetween. Tubular member further includes spaced slots 138 defined in the lower edge of sidewall 126 and configured to register with a correspond-ing locking boss L06 in o-der to secure cover 74 to valve base 70.
Figs. 7 and 8 illustrate assembled control valve 14 with valve fingers 134a-c of cover 74 fitting concentric-ally about valve fingers 116a-c of rotatable element 72. In operation, pressure controller 26 energizes valve motor 78 in order to rotate element 72 clock-wise or counter clock-wise between a fully closed position (Fig. 7), a fully opened position (Fig. 8), and intermediate positions therebetween.
In the fully closed position of Fig. 7, fingers 116a-c and 134a-c are fully meshed in order to block the respec-tive spaces and ports 122 are in complete registration with recesses 96a-c. In this position, all of the air entering inlet tube 130 from source 12 exhausts through ports 122a-c and recesses 96a-c. In the fully open position of Fig. 8, fingers 116a-c and 134a-c are in registration so that the i~- 211288~
spaces therebetween are open, and support bodies 114a-c are in registration with and thereby block recesses 96a-c. With this orientation, all of the air is exAausted through outlet tube 132 for delivery to the patient.
The intermediate positions between fully opened and fully closed allow respective portions of the inlet air to exhaust through recesses 96a-c and through outlet tube 132.
In this way, control valve 14 provides more precise control over the pressure delivered to the patient, and provides lo smoother transition between pressure settings.
In the operation of apparatus 10 during inhalation, it is necessary to provide sufficient pressure to maintain the airway pressure splint in the patient in order to prevent occlusion. For patient comfort, however, it is desirable to lower the pressure to a level as low as possible, including ambient pressure, while still maintaining sufficient pressure to keep the airway open. In order to accomplish these benefits, phase detection circuit 24 detects the inhalation and exhalation phases of the patient's respira-tion, and provides corresponding outputs to pressure con-troller 14. In the preferred embodiment, controller 14 controls its output pressure in a predetermined manner correlated with inhalation and exhalation as indicated by the outputs received from circuit 24. More particularly, pressure controller 14 controls the pressure delivered to the patient at a higher level during inhalation and a lower level during exhalation as determined by the settings on DACs 48,50. Typically, the respective inhalation and exhalation pressure levels are prescribed by the patient's physician.
Figs. 9-11 illustrate control valve 140 which is another embodiment of a control valve for use in place of valve 14. Valve 140 includes valve body 142 and actuator 2112~84 assembly 144. Valve body 142 includes external tubular inlet coupler 146 in communication with inlet passaqe 148, and further ~ncludes exhaust passage 150 and outlet passage 152 having external outlet coupler 154 extending therefrom.
As illustrated in Figs. 10-11, exhaust and outlet passages 150,152 communicate with inlet passage 148 and extend -ransversely therefrom, parallel to one another.
~ctuator assembly 144 includes valve motor 156, valve stem 158, exhaust valve element 160 and outlet valve iO element 162. As illustrated in Figs. 9-11, motor 156 is coupled to the bottom of body 142 with motor-actuated stem 158 extending upwardly therefrom through, and transverse ~o, exhaust and outlet passages 150,152. Valve elements 160,162 present oval-shaped configurations and are coupled with stem 158 for rotation therewith. Element 160 is positioned in exhaust passage 150, and element 152 is positioned in outlet passage 152. Valve elements 160,162 function in a manner analogous to conventional butterfly valves. As illustrated, valve elements 160,162 are angular-ly displaced from one another on stem 158 by about 45 .
Valve motor 156 is coupled electrically with pressure controller 26 and receives signals therefrom in the same manner as valve motor 78 or valve 14.
Figs. 10 and 11 illustrate control valve 140 in the closed/exhaust position. In this position, exhaust valve element 160 is positioned parallel to the air flow and outlet valve element 162 is positioned so that its edges engage the sidewalls of outlet passage 152 to block all outflow. In other words, all of the inlet air entering through inlet passage 148 would exhaust through exhaust passage 150 and none would be provided through outlet passage 152 to the patient. In the open/outlet position, elements 160 and 162 would be rotated clockwise as viewed -14- 211~84 from above until the edges of exhaust element 160 engage the walls defining exhaust passage 150. In this position, outlet element 162 is positioned parallel to the air flow through outlet passage 152. In this way, no air is ex-hausted but rather, the full supply is provided through outlet passage 152.
Motor 156 responds to the signals received from pressure controller 26 in order to position valve 140 in the closed or open positions or any intermediate position therebetween. As with control valve 14, this arrangement allows smooth controllable transition between the various ~ valve positions.
Having thus described the preferred embodiment of the present invention the following is claimed as new and desired to be secured by Letters Patent:
Claims (27)
1. An apparatus for detecting the inhalation and exhalation phases of a respiratory cycle having associated respiratory gas flow, said apparatus comprising:
signal production means for producing first and second signals representative of the respiratory gas flow with said signals being time displaced relative to one another and with said signals having respective amplitudes so that one of said signals presents the greater amplitude during at least a portion of one of the phases and so that the other of said signals presents the greater amplitude during at least a portion of the other of said phases; and processing means for processing said signals for determining therefrom the occurrence of said respective phases and for producing outputs representative of said phases.
signal production means for producing first and second signals representative of the respiratory gas flow with said signals being time displaced relative to one another and with said signals having respective amplitudes so that one of said signals presents the greater amplitude during at least a portion of one of the phases and so that the other of said signals presents the greater amplitude during at least a portion of the other of said phases; and processing means for processing said signals for determining therefrom the occurrence of said respective phases and for producing outputs representative of said phases.
2. The apparatus as set forth in claim 1, said signal production means including flow sensor means for producing said first signal representative of instantaneous respiratory gas flow and time delay means for producing said second signal delayed in time relative to said first signal.
3. The apparatus as set forth in claim 2, further including amplitude scaling means for producing said second signal scaled in amplitude relative to said first signal.
4. The apparatus as set forth in claim 3, said scaling means including means for scaling said amplitude at a first level during one of said phases and means for scaling said amplitude at a second level during the other of said phases.
5. The apparatus as set forth in claim 1, said processing means including means for comparing the amplitudes of said first and second signals, for producing a first output when said first signal presents a greater amplitude than said second signal, and for producing a second output when said second signal presents a greater amplitude than said first signal.
6. The apparatus as set forth in claim 1, said first and second signals being electrical signals.
7. The apparatus as set forth in claim 1, said outputs including electrical signals.
8. An apparatus for facilitating the respiration of a patient having a respiratory cycle with associated respiratory gas flow and exhibiting inhalation and exhalation phases, said apparatus comprising:
supply means for supplying a respiratory gas under pressure from a source thereof to a patient;
means for producing first and second signals representative of the respiratory gas flow with said signals being time displaced relative to one another and with said signals having respective amplitudes so that one of said signals presents the greater amplitude during at least a portion of one of the phases and so that the other of said signals presents the greater amplitude during at least a portion of the other of said phases;
processing means for processing said signals for determining therefrom the occurrence of said respective phases and for producing outputs representative of said phases;
control means coupled with said supply means and said processing means for receiving said outputs and responsive thereto for controlling said respiratory gas pressure to the patient in a predetermined manner correlated with said phases.
supply means for supplying a respiratory gas under pressure from a source thereof to a patient;
means for producing first and second signals representative of the respiratory gas flow with said signals being time displaced relative to one another and with said signals having respective amplitudes so that one of said signals presents the greater amplitude during at least a portion of one of the phases and so that the other of said signals presents the greater amplitude during at least a portion of the other of said phases;
processing means for processing said signals for determining therefrom the occurrence of said respective phases and for producing outputs representative of said phases;
control means coupled with said supply means and said processing means for receiving said outputs and responsive thereto for controlling said respiratory gas pressure to the patient in a predetermined manner correlated with said phases.
9. The apparatus as set forth in claim 8, said control means including means for controlling said respiratory gas pressure at a first pressure level during the inhalation phase and for controlling said respiratory gas pressure at a second pressure level lower than said first level during the exhalation phase.
10. The apparatus as set forth in claim 9, said second pressure level including ambient pressure.
11. The apparatus as set forth in claim 9, said second pressure level including a pressure level greater than ambient.
12. The apparatus as set forth in claim 8, said signal production means including flow sensor means for producing said first signal representative of instantaneous respiratory gas flow and time delay means for producing said second signal delayed in time relative to said first signal.
13. The apparatus as set forth in claim 12, further including amplitude scaling means for producing said second signal scaled in amplitude relative to said first signal.
14. The apparatus as set forth in claim 13, said scaling means including means for scaling said amplitude at a first level during one of said phases and means for scaling said amplitude at a second level during the other of said phases.
15. The apparatus as set forth in claim 8, said processing means including means for comparing the amplitudes of said first and second signals, for producing a first output when said first signal presents a greater amplitude than said second signal, and for producing a second output when said second signal presents a greater amplitude than said first signal.
16. The apparatus as set forth in claim 8, said first and second signals being electrical signals.
17. The apparatus as set forth in claim 8, said outputs including electrical signals.
18. The apparatus as set forth in claim 4, wherein said means for scaling said amplitudes at a first level and a second level are accessible by a patient.
19. The apparatus as set forth in claim 14, wherein said means for scaling said amplitudes at a first level and a second level are adjustable by a patient.
20. A method for detecting the inhalation and exhalation phases of a respiratory cycle having associated respiratory gas flow, said method comprising:
producing first and second signals representative of the respiratory gas flow from a signal production means, said signals being time displaced relative to one another, said signals having respective amplitudes, said first signal presents the greater amplitude during at least a portion of the inhalation phase, said second signal presents the greater amplitude during at least a portion of the exhalation phase; and processing said signals with a processing means for determining the occurrence of said inhalation and exhalation phases and for producing a first output corresponding to the inhalation phase and a second output corresponding to the exhalation phase.
producing first and second signals representative of the respiratory gas flow from a signal production means, said signals being time displaced relative to one another, said signals having respective amplitudes, said first signal presents the greater amplitude during at least a portion of the inhalation phase, said second signal presents the greater amplitude during at least a portion of the exhalation phase; and processing said signals with a processing means for determining the occurrence of said inhalation and exhalation phases and for producing a first output corresponding to the inhalation phase and a second output corresponding to the exhalation phase.
21. The method as set forth in claim 20, wherein said signal production means includes flow sensor means for producing said first signal representative of instantaneous respiratory gas flow and time delay means for producing said second signal delayed in time relative to said first signal.
22. The method as set forth in claim 21, further including amplitude scaling means for producing said second signal scaled in amplitude relative to said first signal.
23. The method as set forth in claim 22, wherein said scaling means includes means for scaling said amplitude at a first level during one of said phases and means for scaling said amplitude at a second level during the other of said phases.
24. The method as set forth in claim 23, wherein said means for scaling said amplitudes at a first level and a second level are accessible by a patient.
25. The method as set forth in claim 20, wherein said processing means includes means for comparing the amplitude of said first signal and said second signal, for producing a first output when said first signal presents a greater amplitude than said second signal, and for producing a second output when said second signal presents a greater amplitude than said first signal.
26. The method as set forth in claim 20, wherein said first signal and said second signal are electrical signals.
27. The method as set forth in claim 20, wherein said outputs include electrical signals.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/003,129 | 1993-01-12 | ||
US08/003,129 US5438980A (en) | 1993-01-12 | 1993-01-12 | Inhalation/exhalation respiratory phase detection circuit |
Publications (2)
Publication Number | Publication Date |
---|---|
CA2112884A1 CA2112884A1 (en) | 1994-07-13 |
CA2112884C true CA2112884C (en) | 1999-01-12 |
Family
ID=21704309
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002112884A Expired - Lifetime CA2112884C (en) | 1993-01-12 | 1994-01-05 | Inhalation/exhalation respiratory phase detection circuit |
Country Status (6)
Country | Link |
---|---|
US (2) | US5438980A (en) |
EP (1) | EP0606687B1 (en) |
JP (1) | JP3682986B2 (en) |
AU (1) | AU669237B2 (en) |
CA (1) | CA2112884C (en) |
DE (2) | DE69333268T2 (en) |
Families Citing this family (234)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5632269A (en) | 1989-09-22 | 1997-05-27 | Respironics Inc. | Breathing gas delivery method and apparatus |
US5490502A (en) * | 1992-05-07 | 1996-02-13 | New York University | Method and apparatus for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5645054A (en) * | 1992-06-01 | 1997-07-08 | Sleepnet Corp. | Device and method for the treatment of sleep apnea syndrome |
US5438980A (en) * | 1993-01-12 | 1995-08-08 | Puritan-Bennett Corporation | Inhalation/exhalation respiratory phase detection circuit |
US6675797B1 (en) * | 1993-11-05 | 2004-01-13 | Resmed Limited | Determination of patency of the airway |
EP1900324B1 (en) | 1993-11-05 | 2009-06-03 | ResMed Limited | Apparatus for determining patency of the airway |
DE69422900T2 (en) | 1993-12-01 | 2000-06-08 | Resmed Ltd | Continuous positive airway pressure (CPAP) device |
US6237593B1 (en) | 1993-12-03 | 2001-05-29 | Resmed Limited | Estimation of flow and detection of breathing CPAP treatment |
US6932084B2 (en) * | 1994-06-03 | 2005-08-23 | Ric Investments, Inc. | Method and apparatus for providing positive airway pressure to a patient |
FI954092A (en) * | 1994-09-08 | 1996-03-09 | Weinmann G Geraete Med | Method of controlling a respirator in the treatment of sleep apnea |
US6866040B1 (en) * | 1994-09-12 | 2005-03-15 | Nellcor Puritan Bennett France Developpement | Pressure-controlled breathing aid |
FR2725137B1 (en) * | 1994-09-29 | 1997-01-10 | Taema | DEVICE FOR DETECTING RESPIRATORY CYCLES, PARTICULARLY FOR MONITORING THE EXECUTION OF A TREATMENT |
US5551419A (en) * | 1994-12-15 | 1996-09-03 | Devilbiss Health Care, Inc. | Control for CPAP apparatus |
AUPN236595A0 (en) | 1995-04-11 | 1995-05-11 | Rescare Limited | Monitoring of apneic arousals |
AUPN344195A0 (en) | 1995-06-08 | 1995-07-06 | Rescare Limited | Monitoring of oro-nasal respiration |
AUPN394895A0 (en) | 1995-07-03 | 1995-07-27 | Rescare Limited | Auto-calibration of pressure transducer offset |
AUPN547895A0 (en) | 1995-09-15 | 1995-10-12 | Rescare Limited | Flow estimation and compenstion of flow-induced pressure swings cpap treatment |
AU716135B2 (en) * | 1995-09-18 | 2000-02-17 | Resmed Limited | Pressure control in CPAP treatment or assisted respiration |
EP0862474A4 (en) * | 1995-09-18 | 2000-05-03 | Resmed Ltd | Pressure control in cpap treatment or assisted respiration |
AUPN616795A0 (en) | 1995-10-23 | 1995-11-16 | Rescare Limited | Ipap duration in bilevel cpap or assisted respiration treatment |
US5865173A (en) * | 1995-11-06 | 1999-02-02 | Sunrise Medical Hhg Inc. | Bilevel CPAP system with waveform control for both IPAP and EPAP |
US6158432A (en) | 1995-12-08 | 2000-12-12 | Cardiopulmonary Corporation | Ventilator control system and method |
US6463930B2 (en) | 1995-12-08 | 2002-10-15 | James W. Biondi | System for automatically weaning a patient from a ventilator, and method thereof |
AUPN973596A0 (en) | 1996-05-08 | 1996-05-30 | Resmed Limited | Control of delivery pressure in cpap treatment or assisted respiration |
JP3323745B2 (en) * | 1996-07-25 | 2002-09-09 | 株式会社日立製作所 | Characteristic adjustment means of physical quantity detection device and heating resistance type air flow device |
US5705735A (en) * | 1996-08-09 | 1998-01-06 | Medical Graphics Corporation | Breath by breath nutritional requirements analyzing system |
AUPO163896A0 (en) | 1996-08-14 | 1996-09-05 | Resmed Limited | Determination of respiratory airflow |
AUPO247496A0 (en) * | 1996-09-23 | 1996-10-17 | Resmed Limited | Assisted ventilation to match patient respiratory need |
US6371113B1 (en) * | 1996-10-10 | 2002-04-16 | Datex-Ohmeda, Inc. | Zero flow pause during volume ventilation |
AUPO301796A0 (en) | 1996-10-16 | 1996-11-07 | Resmed Limited | A vent valve apparatus |
AUPO418696A0 (en) | 1996-12-12 | 1997-01-16 | Resmed Limited | A substance delivery apparatus |
DE29622321U1 (en) * | 1996-12-21 | 1997-03-06 | Medicap Medizintechnik Gmbh | Device for dosed gas supply to users |
DE19706092C2 (en) * | 1997-02-17 | 2000-02-24 | Map Gmbh | Procedure for switching to the inhalation or exhalation phase with a CPAP therapy device |
US5937851A (en) * | 1997-02-27 | 1999-08-17 | Respironics, Inc. | Swivel device utilizing bearing clearance to allow carbon dioxide laden exhaust |
US5915380A (en) | 1997-03-14 | 1999-06-29 | Nellcor Puritan Bennett Incorporated | System and method for controlling the start up of a patient ventilator |
AUPO742297A0 (en) | 1997-06-18 | 1997-07-10 | Resmed Limited | An apparatus for supplying breathable gas |
WO1999004841A1 (en) * | 1997-07-25 | 1999-02-04 | Minnesota Innovative Technologies & Instruments Corporation (Miti) | Control device for supplying supplemental respiratory oxygen |
US6371114B1 (en) | 1998-07-24 | 2002-04-16 | Minnesota Innovative Technologies & Instruments Corporation | Control device for supplying supplemental respiratory oxygen |
AUPP026997A0 (en) * | 1997-11-07 | 1997-12-04 | Resmed Limited | Administration of cpap treatment pressure in presence of apnea |
USD421298S (en) | 1998-04-23 | 2000-02-29 | Resmed Limited | Flow generator |
SE9802123D0 (en) * | 1998-06-15 | 1998-06-15 | Siemens Elema Ab | directional valve |
US6626176B1 (en) | 1998-08-19 | 2003-09-30 | Map Medizintechnik Fur Arzt Und Patient Gmbh & Co. Kg | Method and device for switching the inspiration or expiration phase during CPAP therapy |
US6123674A (en) * | 1998-10-15 | 2000-09-26 | Ntc Technology Inc. | Airway valve to facilitate re-breathing, method of operation, and ventilator circuit so equipped |
US6098622A (en) * | 1998-10-15 | 2000-08-08 | Ntc Technology Inc. | Airway valve to facilitate re-breathing, method of operation, and ventilator circuit so equipped |
US8701664B2 (en) * | 1998-11-06 | 2014-04-22 | Caradyne (R&D) Limited | Apparatus and method for relieving dyspnoea |
FR2789593B1 (en) * | 1999-05-21 | 2008-08-22 | Mallinckrodt Dev France | APPARATUS FOR SUPPLYING AIR PRESSURE TO A PATIENT WITH SLEEP DISORDERS AND METHODS OF CONTROLLING THE SAME |
US6615831B1 (en) * | 1999-07-02 | 2003-09-09 | Respironics, Inc. | Pressure support system and method and a pressure control valve for use in such system and method |
US6708690B1 (en) * | 1999-09-03 | 2004-03-23 | Respironics, Inc. | Apparatus and method for providing high frequency variable pressure to a patient |
US7063086B2 (en) * | 1999-09-23 | 2006-06-20 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
WO2001087395A1 (en) * | 2000-05-12 | 2001-11-22 | E.M.E. (Electro Medical Equipment) Ltd. | Method and apparatus for the administration of continuous positive airway pressure therapy |
DE10031079A1 (en) * | 2000-06-30 | 2002-02-07 | Map Gmbh | Measuring patient breathing and state, correlates present respiration signals with prior reference measurements, to adjust CPAP therapy pressure accordingly |
EP1322367A4 (en) * | 2000-09-28 | 2009-08-26 | Invacare Corp | Carbon dioxide-based bi-level cpap control |
SE517723C2 (en) * | 2000-11-07 | 2002-07-09 | Aneo Ab | Arrangement for pulmonary ventilatory therapy |
AU2002308423B2 (en) * | 2001-05-23 | 2007-11-01 | Resmed Limited | Ventilator patient synchronization |
US6810877B2 (en) * | 2001-08-02 | 2004-11-02 | Medical Electronics Devices Corp. | High sensitivity pressure switch |
KR20040070339A (en) * | 2001-10-18 | 2004-08-07 | 더 유니버시티 오브 마이애미 | Continuous gas leakage for elimination of ventilator dead space |
GB0221044D0 (en) * | 2002-09-11 | 2002-10-23 | Micro Medical Ltd | Apparatus for measuring the strength of a person's respiratory muscles |
GB2401668A (en) * | 2003-05-16 | 2004-11-17 | Helmet Integrated Syst Ltd | Expiratory valve unit |
US7588033B2 (en) | 2003-06-18 | 2009-09-15 | Breathe Technologies, Inc. | Methods, systems and devices for improving ventilation in a lung area |
DE10337138A1 (en) * | 2003-08-11 | 2005-03-17 | Freitag, Lutz, Dr. | Method and arrangement for the respiratory assistance of a patient as well as tracheal prosthesis and catheter |
AU2003903138A0 (en) | 2003-06-20 | 2003-07-03 | Resmed Limited | Method and apparatus for improving the comfort of cpap |
US7152598B2 (en) * | 2003-06-23 | 2006-12-26 | Invacare Corporation | System and method for providing a breathing gas |
US7621270B2 (en) * | 2003-06-23 | 2009-11-24 | Invacare Corp. | System and method for providing a breathing gas |
FR2858236B1 (en) | 2003-07-29 | 2006-04-28 | Airox | DEVICE AND METHOD FOR SUPPLYING RESPIRATORY GAS IN PRESSURE OR VOLUME |
JP2007506480A (en) | 2003-08-18 | 2007-03-22 | ワンドカ,アンソニー・ディ | Methods and apparatus for non-invasive ventilation with a nasal interface |
US7066985B2 (en) * | 2003-10-07 | 2006-06-27 | Inogen, Inc. | Portable gas fractionalization system |
US20050072426A1 (en) * | 2003-10-07 | 2005-04-07 | Deane Geoffrey Frank | Portable gas fractionalization system |
WO2005035037A2 (en) | 2003-10-07 | 2005-04-21 | Inogen, Inc. | Portable gas fractionalization system |
US20050072423A1 (en) * | 2003-10-07 | 2005-04-07 | Deane Geoffrey Frank | Portable gas fractionalization system |
US7135059B2 (en) * | 2003-10-07 | 2006-11-14 | Inogen, Inc. | Portable gas fractionalization system |
US8146592B2 (en) | 2004-02-26 | 2012-04-03 | Ameriflo, Inc. | Method and apparatus for regulating fluid flow or conserving fluid flow |
US7617826B1 (en) | 2004-02-26 | 2009-11-17 | Ameriflo, Inc. | Conserver |
CA2567865A1 (en) * | 2004-06-28 | 2006-01-12 | Inogen, Inc. | Conserver design for a therapeutic breathing gas system |
FR2875138B1 (en) | 2004-09-15 | 2008-07-11 | Mallinckrodt Dev France Sa | CONTROL METHOD FOR A HEATING HUMIDIFIER |
US10610228B2 (en) | 2004-12-08 | 2020-04-07 | Theravent, Inc. | Passive nasal peep devices |
US9833354B2 (en) | 2004-12-08 | 2017-12-05 | Theravent, Inc. | Nasal respiratory devices |
US7644714B2 (en) | 2005-05-27 | 2010-01-12 | Apnex Medical, Inc. | Devices and methods for treating sleep disorders |
US7347205B2 (en) * | 2005-08-31 | 2008-03-25 | The General Electric Company | Method for use with the pressure triggering of medical ventilators |
EP1926517A2 (en) | 2005-09-20 | 2008-06-04 | Lutz Freitag | Systems, methods and apparatus for respiratory support of a patient |
US7686870B1 (en) | 2005-12-29 | 2010-03-30 | Inogen, Inc. | Expandable product rate portable gas fractionalization system |
CN100998902B (en) * | 2006-01-13 | 2010-12-08 | 深圳迈瑞生物医疗电子股份有限公司 | Method and device for mornitering and controlling flow |
US7412891B2 (en) * | 2006-02-09 | 2008-08-19 | Pivot International, Inc. | Sip and puff mouse |
US8021310B2 (en) | 2006-04-21 | 2011-09-20 | Nellcor Puritan Bennett Llc | Work of breathing display for a ventilation system |
JP5191005B2 (en) | 2006-05-18 | 2013-04-24 | ブリーズ テクノロジーズ, インコーポレイテッド | Method and device for tracheostomy |
EP2026723B1 (en) * | 2006-05-23 | 2018-11-21 | Theravent, Inc. | Nasal respiratory devices |
EP2068992B1 (en) | 2006-08-03 | 2016-10-05 | Breathe Technologies, Inc. | Devices for minimally invasive respiratory support |
GB2441583A (en) * | 2006-09-05 | 2008-03-12 | South Bank Univ Entpr Ltd | Breathing device |
US20080060647A1 (en) * | 2006-09-12 | 2008-03-13 | Invacare Corporation | System and method for delivering a breathing gas |
US7784461B2 (en) | 2006-09-26 | 2010-08-31 | Nellcor Puritan Bennett Llc | Three-dimensional waveform display for a breathing assistance system |
US8902568B2 (en) | 2006-09-27 | 2014-12-02 | Covidien Lp | Power supply interface system for a breathing assistance system |
US8327848B2 (en) * | 2006-09-28 | 2012-12-11 | Ric Investments, Llc | Pressure reducing valve |
US20080078390A1 (en) * | 2006-09-29 | 2008-04-03 | Nellcor Puritan Bennett Incorporated | Providing predetermined groups of trending parameters for display in a breathing assistance system |
US7809442B2 (en) | 2006-10-13 | 2010-10-05 | Apnex Medical, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US9744354B2 (en) | 2008-12-31 | 2017-08-29 | Cyberonics, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US9913982B2 (en) | 2011-01-28 | 2018-03-13 | Cyberonics, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US9186511B2 (en) | 2006-10-13 | 2015-11-17 | Cyberonics, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US8855771B2 (en) | 2011-01-28 | 2014-10-07 | Cyberonics, Inc. | Screening devices and methods for obstructive sleep apnea therapy |
US9205262B2 (en) | 2011-05-12 | 2015-12-08 | Cyberonics, Inc. | Devices and methods for sleep apnea treatment |
AU2008240290A1 (en) * | 2007-04-13 | 2008-10-23 | Invacare Corporation | Apparatus and method for providing positive airway pressure |
WO2008144589A1 (en) | 2007-05-18 | 2008-11-27 | Breathe Technologies, Inc. | Methods and devices for sensing respiration and providing ventilation therapy |
EP3871722A1 (en) * | 2007-07-18 | 2021-09-01 | Vapotherm, Inc. | System for delivering a heated and humidified gas |
WO2009026582A1 (en) | 2007-08-23 | 2009-02-26 | Invacare Corporation | Method and apparatus for adjusting desired pressure in positive airway pressure devices |
US8567399B2 (en) | 2007-09-26 | 2013-10-29 | Breathe Technologies, Inc. | Methods and devices for providing inspiratory and expiratory flow relief during ventilation therapy |
JP5513392B2 (en) | 2007-09-26 | 2014-06-04 | ブリーズ・テクノロジーズ・インコーポレーテッド | Method and apparatus for treating sleep apnea |
US20090165795A1 (en) * | 2007-12-31 | 2009-07-02 | Nellcor Puritan Bennett Llc | Method and apparatus for respiratory therapy |
US20090205663A1 (en) * | 2008-02-19 | 2009-08-20 | Nellcor Puritan Bennett Llc | Configuring the operation of an alternating pressure ventilation mode |
US20090205661A1 (en) * | 2008-02-20 | 2009-08-20 | Nellcor Puritan Bennett Llc | Systems and methods for extended volume range ventilation |
US8640699B2 (en) | 2008-03-27 | 2014-02-04 | Covidien Lp | Breathing assistance systems with lung recruitment maneuvers |
US8792949B2 (en) | 2008-03-31 | 2014-07-29 | Covidien Lp | Reducing nuisance alarms |
US8272380B2 (en) | 2008-03-31 | 2012-09-25 | Nellcor Puritan Bennett, Llc | Leak-compensated pressure triggering in medical ventilators |
US8746248B2 (en) | 2008-03-31 | 2014-06-10 | Covidien Lp | Determination of patient circuit disconnect in leak-compensated ventilatory support |
EP2313138B1 (en) | 2008-03-31 | 2018-09-12 | Covidien LP | System and method for determining ventilator leakage during stable periods within a breath |
US8267085B2 (en) | 2009-03-20 | 2012-09-18 | Nellcor Puritan Bennett Llc | Leak-compensated proportional assist ventilation |
US8425428B2 (en) | 2008-03-31 | 2013-04-23 | Covidien Lp | Nitric oxide measurements in patients using flowfeedback |
US8770193B2 (en) | 2008-04-18 | 2014-07-08 | Breathe Technologies, Inc. | Methods and devices for sensing respiration and controlling ventilator functions |
JP5758799B2 (en) | 2008-04-18 | 2015-08-05 | ブリーズ・テクノロジーズ・インコーポレーテッド | Method and device for sensing respiratory effects and controlling ventilator function |
CN102056539B (en) | 2008-06-06 | 2015-10-07 | 柯惠有限合伙公司 | For making great efforts with patient the system and method that carries out pro rata taking a breath |
CA2734296C (en) | 2008-08-22 | 2018-12-18 | Breathe Technologies, Inc. | Methods and devices for providing mechanical ventilation with an open airway interface |
US8528554B2 (en) | 2008-09-04 | 2013-09-10 | Covidien Lp | Inverse sawtooth pressure wave train purging in medical ventilators |
US8551006B2 (en) | 2008-09-17 | 2013-10-08 | Covidien Lp | Method for determining hemodynamic effects |
US8424520B2 (en) | 2008-09-23 | 2013-04-23 | Covidien Lp | Safe standby mode for ventilator |
EP2349420B1 (en) | 2008-09-25 | 2016-08-31 | Covidien LP | Inversion-based feed-forward compensation of inspiratory trigger dynamics in medical ventilators |
US8181648B2 (en) | 2008-09-26 | 2012-05-22 | Nellcor Puritan Bennett Llc | Systems and methods for managing pressure in a breathing assistance system |
US8302602B2 (en) | 2008-09-30 | 2012-11-06 | Nellcor Puritan Bennett Llc | Breathing assistance system with multiple pressure sensors |
US8439032B2 (en) * | 2008-09-30 | 2013-05-14 | Covidien Lp | Wireless communications for a breathing assistance system |
US8302600B2 (en) | 2008-09-30 | 2012-11-06 | Nellcor Puritan Bennett Llc | Battery management for a breathing assistance system |
US8652064B2 (en) | 2008-09-30 | 2014-02-18 | Covidien Lp | Sampling circuit for measuring analytes |
US8393323B2 (en) | 2008-09-30 | 2013-03-12 | Covidien Lp | Supplemental gas safety system for a breathing assistance system |
US8585412B2 (en) | 2008-09-30 | 2013-11-19 | Covidien Lp | Configurable respiratory muscle pressure generator |
CA2739435A1 (en) | 2008-10-01 | 2010-04-08 | Breathe Technologies, Inc. | Ventilator with biofeedback monitoring and control for improving patient activity and health |
WO2010115170A2 (en) | 2009-04-02 | 2010-10-07 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive open ventilation for treating airway obstructions |
US9132250B2 (en) | 2009-09-03 | 2015-09-15 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with an entrainment port and/or pressure feature |
US8424521B2 (en) | 2009-02-27 | 2013-04-23 | Covidien Lp | Leak-compensated respiratory mechanics estimation in medical ventilators |
US8434479B2 (en) | 2009-02-27 | 2013-05-07 | Covidien Lp | Flow rate compensation for transient thermal response of hot-wire anemometers |
US8418691B2 (en) | 2009-03-20 | 2013-04-16 | Covidien Lp | Leak-compensated pressure regulated volume control ventilation |
US9186075B2 (en) * | 2009-03-24 | 2015-11-17 | Covidien Lp | Indicating the accuracy of a physiological parameter |
US9962512B2 (en) | 2009-04-02 | 2018-05-08 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with a free space nozzle feature |
US20100262031A1 (en) * | 2009-04-14 | 2010-10-14 | Yongji Fu | Method and system for respiratory phase classification using explicit labeling with label verification |
US8776790B2 (en) | 2009-07-16 | 2014-07-15 | Covidien Lp | Wireless, gas flow-powered sensor system for a breathing assistance system |
US20110023878A1 (en) * | 2009-07-31 | 2011-02-03 | Nellcor Puritan Bennett Llc | Method And System For Delivering A Single-Breath, Low Flow Recruitment Maneuver |
US8789529B2 (en) | 2009-08-20 | 2014-07-29 | Covidien Lp | Method for ventilation |
CA2774902C (en) | 2009-09-03 | 2017-01-03 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with an entrainment port and/or pressure feature |
US8469030B2 (en) | 2009-12-01 | 2013-06-25 | Covidien Lp | Exhalation valve assembly with selectable contagious/non-contagious latch |
US8439036B2 (en) | 2009-12-01 | 2013-05-14 | Covidien Lp | Exhalation valve assembly with integral flow sensor |
US8469031B2 (en) | 2009-12-01 | 2013-06-25 | Covidien Lp | Exhalation valve assembly with integrated filter |
US8439037B2 (en) | 2009-12-01 | 2013-05-14 | Covidien Lp | Exhalation valve assembly with integrated filter and flow sensor |
US8421465B2 (en) | 2009-12-02 | 2013-04-16 | Covidien Lp | Method and apparatus for indicating battery cell status on a battery pack assembly used during mechanical ventilation |
US8434483B2 (en) | 2009-12-03 | 2013-05-07 | Covidien Lp | Ventilator respiratory gas accumulator with sampling chamber |
US8677996B2 (en) | 2009-12-04 | 2014-03-25 | Covidien Lp | Ventilation system with system status display including a user interface |
US8924878B2 (en) | 2009-12-04 | 2014-12-30 | Covidien Lp | Display and access to settings on a ventilator graphical user interface |
US8482415B2 (en) | 2009-12-04 | 2013-07-09 | Covidien Lp | Interactive multilevel alarm |
US9119925B2 (en) | 2009-12-04 | 2015-09-01 | Covidien Lp | Quick initiation of respiratory support via a ventilator user interface |
US8499252B2 (en) | 2009-12-18 | 2013-07-30 | Covidien Lp | Display of respiratory data graphs on a ventilator graphical user interface |
US9262588B2 (en) | 2009-12-18 | 2016-02-16 | Covidien Lp | Display of respiratory data graphs on a ventilator graphical user interface |
US20110146681A1 (en) * | 2009-12-21 | 2011-06-23 | Nellcor Puritan Bennett Llc | Adaptive Flow Sensor Model |
US20110146683A1 (en) * | 2009-12-21 | 2011-06-23 | Nellcor Puritan Bennett Llc | Sensor Model |
US8400290B2 (en) | 2010-01-19 | 2013-03-19 | Covidien Lp | Nuisance alarm reduction method for therapeutic parameters |
US8707952B2 (en) | 2010-02-10 | 2014-04-29 | Covidien Lp | Leak determination in a breathing assistance system |
US20110209702A1 (en) * | 2010-02-26 | 2011-09-01 | Nellcor Puritan Bennett Llc | Proportional Solenoid Valve For Low Molecular Weight Gas Mixtures |
US9302061B2 (en) | 2010-02-26 | 2016-04-05 | Covidien Lp | Event-based delay detection and control of networked systems in medical ventilation |
US8511306B2 (en) | 2010-04-27 | 2013-08-20 | Covidien Lp | Ventilation system with system status display for maintenance and service information |
US8539949B2 (en) | 2010-04-27 | 2013-09-24 | Covidien Lp | Ventilation system with a two-point perspective view |
US8453643B2 (en) | 2010-04-27 | 2013-06-04 | Covidien Lp | Ventilation system with system status display for configuration and program information |
US8638200B2 (en) | 2010-05-07 | 2014-01-28 | Covidien Lp | Ventilator-initiated prompt regarding Auto-PEEP detection during volume ventilation of non-triggering patient |
US8607790B2 (en) | 2010-06-30 | 2013-12-17 | Covidien Lp | Ventilator-initiated prompt regarding auto-PEEP detection during pressure ventilation of patient exhibiting obstructive component |
US8607791B2 (en) | 2010-06-30 | 2013-12-17 | Covidien Lp | Ventilator-initiated prompt regarding auto-PEEP detection during pressure ventilation |
US8607789B2 (en) | 2010-06-30 | 2013-12-17 | Covidien Lp | Ventilator-initiated prompt regarding auto-PEEP detection during volume ventilation of non-triggering patient exhibiting obstructive component |
US8607788B2 (en) | 2010-06-30 | 2013-12-17 | Covidien Lp | Ventilator-initiated prompt regarding auto-PEEP detection during volume ventilation of triggering patient exhibiting obstructive component |
US8676285B2 (en) | 2010-07-28 | 2014-03-18 | Covidien Lp | Methods for validating patient identity |
JP5891226B2 (en) | 2010-08-16 | 2016-03-22 | ブリーズ・テクノロジーズ・インコーポレーテッド | Method, system and apparatus for providing ventilatory assistance using LOX |
US8554298B2 (en) | 2010-09-21 | 2013-10-08 | Cividien LP | Medical ventilator with integrated oximeter data |
WO2012045051A1 (en) | 2010-09-30 | 2012-04-05 | Breathe Technologies, Inc. | Methods, systems and devices for humidifying a respiratory tract |
US8844537B1 (en) | 2010-10-13 | 2014-09-30 | Michael T. Abramson | System and method for alleviating sleep apnea |
US8595639B2 (en) | 2010-11-29 | 2013-11-26 | Covidien Lp | Ventilator-initiated prompt regarding detection of fluctuations in resistance |
US8757152B2 (en) | 2010-11-29 | 2014-06-24 | Covidien Lp | Ventilator-initiated prompt regarding detection of double triggering during a volume-control breath type |
US8757153B2 (en) | 2010-11-29 | 2014-06-24 | Covidien Lp | Ventilator-initiated prompt regarding detection of double triggering during ventilation |
US8788236B2 (en) | 2011-01-31 | 2014-07-22 | Covidien Lp | Systems and methods for medical device testing |
US8676529B2 (en) | 2011-01-31 | 2014-03-18 | Covidien Lp | Systems and methods for simulation and software testing |
US8783250B2 (en) | 2011-02-27 | 2014-07-22 | Covidien Lp | Methods and systems for transitory ventilation support |
US9038633B2 (en) | 2011-03-02 | 2015-05-26 | Covidien Lp | Ventilator-initiated prompt regarding high delivered tidal volume |
CN102678957A (en) * | 2011-03-17 | 2012-09-19 | 德昌电机(深圳)有限公司 | Medical liquid control device |
US8714154B2 (en) | 2011-03-30 | 2014-05-06 | Covidien Lp | Systems and methods for automatic adjustment of ventilator settings |
US9629971B2 (en) | 2011-04-29 | 2017-04-25 | Covidien Lp | Methods and systems for exhalation control and trajectory optimization |
US8776792B2 (en) | 2011-04-29 | 2014-07-15 | Covidien Lp | Methods and systems for volume-targeted minimum pressure-control ventilation |
US9089657B2 (en) | 2011-10-31 | 2015-07-28 | Covidien Lp | Methods and systems for gating user initiated increases in oxygen concentration during ventilation |
US9364624B2 (en) | 2011-12-07 | 2016-06-14 | Covidien Lp | Methods and systems for adaptive base flow |
US9498589B2 (en) | 2011-12-31 | 2016-11-22 | Covidien Lp | Methods and systems for adaptive base flow and leak compensation |
US9022031B2 (en) | 2012-01-31 | 2015-05-05 | Covidien Lp | Using estimated carinal pressure for feedback control of carinal pressure during ventilation |
KR101180309B1 (en) * | 2012-03-27 | 2012-09-06 | (주)서일퍼시픽 | Direction change valve module and Cough assistance machine using the direction change valve module |
US9327089B2 (en) | 2012-03-30 | 2016-05-03 | Covidien Lp | Methods and systems for compensation of tubing related loss effects |
US8844526B2 (en) | 2012-03-30 | 2014-09-30 | Covidien Lp | Methods and systems for triggering with unknown base flow |
US9993604B2 (en) | 2012-04-27 | 2018-06-12 | Covidien Lp | Methods and systems for an optimized proportional assist ventilation |
US9144658B2 (en) | 2012-04-30 | 2015-09-29 | Covidien Lp | Minimizing imposed expiratory resistance of mechanical ventilator by optimizing exhalation valve control |
US9120571B2 (en) | 2012-05-25 | 2015-09-01 | B/E Aerospace, Inc. | Hybrid on-board generation of oxygen for aircraft passengers |
US9550570B2 (en) | 2012-05-25 | 2017-01-24 | B/E Aerospace, Inc. | On-board generation of oxygen for aircraft passengers |
US9550575B2 (en) | 2012-05-25 | 2017-01-24 | B/E Aerospace, Inc. | On-board generation of oxygen for aircraft pilots |
US10362967B2 (en) | 2012-07-09 | 2019-07-30 | Covidien Lp | Systems and methods for missed breath detection and indication |
US9027552B2 (en) | 2012-07-31 | 2015-05-12 | Covidien Lp | Ventilator-initiated prompt or setting regarding detection of asynchrony during ventilation |
US9375542B2 (en) | 2012-11-08 | 2016-06-28 | Covidien Lp | Systems and methods for monitoring, managing, and/or preventing fatigue during ventilation |
CN103893864B (en) * | 2012-12-26 | 2017-05-24 | 北京谊安医疗系统股份有限公司 | Turbine respirator pressure control ventilation method |
CN103893865B (en) * | 2012-12-26 | 2017-05-31 | 北京谊安医疗系统股份有限公司 | A kind of method of lung ventilator turbine volume controlled ventilation |
US9289573B2 (en) | 2012-12-28 | 2016-03-22 | Covidien Lp | Ventilator pressure oscillation filter |
US9492629B2 (en) | 2013-02-14 | 2016-11-15 | Covidien Lp | Methods and systems for ventilation with unknown exhalation flow and exhalation pressure |
USD731049S1 (en) | 2013-03-05 | 2015-06-02 | Covidien Lp | EVQ housing of an exhalation module |
USD736905S1 (en) | 2013-03-08 | 2015-08-18 | Covidien Lp | Exhalation module EVQ housing |
USD731065S1 (en) | 2013-03-08 | 2015-06-02 | Covidien Lp | EVQ pressure sensor filter of an exhalation module |
USD731048S1 (en) | 2013-03-08 | 2015-06-02 | Covidien Lp | EVQ diaphragm of an exhalation module |
USD693001S1 (en) | 2013-03-08 | 2013-11-05 | Covidien Lp | Neonate expiratory filter assembly of an exhalation module |
USD744095S1 (en) | 2013-03-08 | 2015-11-24 | Covidien Lp | Exhalation module EVQ internal flow sensor |
USD692556S1 (en) | 2013-03-08 | 2013-10-29 | Covidien Lp | Expiratory filter body of an exhalation module |
USD701601S1 (en) | 2013-03-08 | 2014-03-25 | Covidien Lp | Condensate vial of an exhalation module |
US9358355B2 (en) | 2013-03-11 | 2016-06-07 | Covidien Lp | Methods and systems for managing a patient move |
US9981096B2 (en) | 2013-03-13 | 2018-05-29 | Covidien Lp | Methods and systems for triggering with unknown inspiratory flow |
US9950135B2 (en) | 2013-03-15 | 2018-04-24 | Covidien Lp | Maintaining an exhalation valve sensor assembly |
US10064583B2 (en) | 2013-08-07 | 2018-09-04 | Covidien Lp | Detection of expiratory airflow limitation in ventilated patient |
US9675771B2 (en) | 2013-10-18 | 2017-06-13 | Covidien Lp | Methods and systems for leak estimation |
EP3104768B1 (en) | 2014-02-11 | 2023-07-26 | Cyberonics, Inc. | Systems for detecting and treating obstructive sleep apnea |
US9808591B2 (en) | 2014-08-15 | 2017-11-07 | Covidien Lp | Methods and systems for breath delivery synchronization |
US11433194B2 (en) | 2014-09-15 | 2022-09-06 | Mercury Enterprises, Inc. | Device for detecting air flow |
US10258759B2 (en) * | 2014-09-15 | 2019-04-16 | Mercury Enterprises, Inc. | Bi-level positive airway pressure device |
US9950129B2 (en) | 2014-10-27 | 2018-04-24 | Covidien Lp | Ventilation triggering using change-point detection |
US9925346B2 (en) | 2015-01-20 | 2018-03-27 | Covidien Lp | Systems and methods for ventilation with unknown exhalation flow |
USD775345S1 (en) | 2015-04-10 | 2016-12-27 | Covidien Lp | Ventilator console |
US10765822B2 (en) | 2016-04-18 | 2020-09-08 | Covidien Lp | Endotracheal tube extubation detection |
US9933445B1 (en) | 2016-05-16 | 2018-04-03 | Hound Labs, Inc. | System and method for target substance identification |
US10792449B2 (en) | 2017-10-03 | 2020-10-06 | Breathe Technologies, Inc. | Patient interface with integrated jet pump |
US10668239B2 (en) | 2017-11-14 | 2020-06-02 | Covidien Lp | Systems and methods for drive pressure spontaneous ventilation |
US11006875B2 (en) | 2018-03-30 | 2021-05-18 | Intel Corporation | Technologies for emotion prediction based on breathing patterns |
US11517691B2 (en) | 2018-09-07 | 2022-12-06 | Covidien Lp | Methods and systems for high pressure controlled ventilation |
US20200147333A1 (en) * | 2018-11-09 | 2020-05-14 | Hound Labs, Inc. | Breath sample systems for use with ventilators |
CN109681660B (en) * | 2018-12-27 | 2020-03-31 | 上海宝亚安全装备股份有限公司 | Switch valve for controlling on-off of power-on circuit of power air supply respirator |
US11896767B2 (en) | 2020-03-20 | 2024-02-13 | Covidien Lp | Model-driven system integration in medical ventilators |
US11933731B1 (en) | 2020-05-13 | 2024-03-19 | Hound Labs, Inc. | Systems and methods using Surface-Enhanced Raman Spectroscopy for detecting tetrahydrocannabinol |
US11806711B1 (en) | 2021-01-12 | 2023-11-07 | Hound Labs, Inc. | Systems, devices, and methods for fluidic processing of biological or chemical samples using flexible fluidic circuits |
Family Cites Families (53)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1482413A (en) * | 1924-02-05 | End plate fob | ||
US3028873A (en) * | 1956-11-19 | 1962-04-10 | Sierra Eng Co | Non-rebreathing valve |
US3500073A (en) * | 1966-09-15 | 1970-03-10 | Phonocopy Inc | Analog to binary signal processor |
US3696731A (en) * | 1971-03-29 | 1972-10-10 | Lear Siegler Inc | Air distributing apparatus |
US3795257A (en) * | 1972-03-27 | 1974-03-05 | Robertshaw Controls Co | Demand valve assembly for use with breathing or resuscitation equipment |
US3896800A (en) * | 1973-07-27 | 1975-07-29 | Airco Inc | Method and apparatus for triggering the inspiratory phase of a respirator |
US3952739A (en) * | 1974-10-21 | 1976-04-27 | Airco, Inc. | Fail safe system for a patient triggered respirator |
US3976064A (en) * | 1975-03-11 | 1976-08-24 | Wood William W | Intermittent mandatory assisted ventilation system for positive pressure breathing apparatus |
US4050458A (en) * | 1976-01-26 | 1977-09-27 | Puritan-Bennett Corporation | Respiration system with patient assist capability |
US4207884A (en) * | 1976-12-20 | 1980-06-17 | Max Isaacson | Pressure controlled breathing apparatus |
US4082093A (en) * | 1977-04-27 | 1978-04-04 | Bourns, Inc. | Compensator valve |
GB1583273A (en) * | 1977-05-06 | 1981-01-21 | Medishield Corp Ltd | Lung ventilators |
US4239039A (en) * | 1979-02-28 | 1980-12-16 | Thompson Harris A | Dual control valve for positive pressure artificial respiration apparatus |
US4381795A (en) * | 1981-03-02 | 1983-05-03 | Dayco Corporation | Diverter valve construction and method of making same |
US4393869A (en) * | 1981-06-22 | 1983-07-19 | Canadian Patents & Development Limited | Electronically controlled respirator |
US4448192A (en) * | 1982-03-05 | 1984-05-15 | Hewlett Packard Company | Medical ventilator device parametrically controlled for patient ventilation |
JPS598972A (en) * | 1982-07-07 | 1984-01-18 | 佐藤 暢 | Respiration synchronous type gas supply method and apparatus in open type respiratory system |
US4459982A (en) * | 1982-09-13 | 1984-07-17 | Bear Medical Systems, Inc. | Servo-controlled demand regulator for respiratory ventilator |
US4655213A (en) * | 1983-10-06 | 1987-04-07 | New York University | Method and apparatus for the treatment of obstructive sleep apnea |
JPS6099268A (en) * | 1983-11-04 | 1985-06-03 | シャープ株式会社 | Constant flow control system |
DE3401841A1 (en) * | 1984-01-20 | 1985-07-25 | Drägerwerk AG, 2400 Lübeck | VENTILATION SYSTEM AND OPERATING METHOD THEREFOR |
DE3422066A1 (en) * | 1984-06-14 | 1985-12-19 | Drägerwerk AG, 2400 Lübeck | VENTILATION SYSTEM AND CONTROLLABLE VALVE UNIT TO |
US4611591A (en) * | 1984-07-10 | 1986-09-16 | Sharp Kabushiki Kaisha | Expiration valve control for automatic respirator |
US4527557A (en) * | 1984-11-01 | 1985-07-09 | Bear Medical Systems, Inc. | Medical ventilator system |
JPS61131756A (en) * | 1984-11-30 | 1986-06-19 | 鳥取大学長 | Respiration tuning air sending type concentrated oxygen supply apparatus |
US4686975A (en) * | 1985-05-03 | 1987-08-18 | Applied Membrane Technology, Inc. | Electronic respirable gas delivery device |
FI81500C (en) * | 1985-05-23 | 1990-11-12 | Etelae Haemeen Keuhkovammayhdi | Respiratory Treatment Unit |
US5002050A (en) * | 1986-09-17 | 1991-03-26 | Mcginnis Gerald E | Medical gas flow control valve, system and method |
US4784130A (en) * | 1986-12-04 | 1988-11-15 | The John Bunn Company | Flow controller |
GB8704104D0 (en) * | 1987-02-21 | 1987-03-25 | Manitoba University Of | Respiratory system load apparatus |
US5199424A (en) * | 1987-06-26 | 1993-04-06 | Sullivan Colin E | Device for monitoring breathing during sleep and control of CPAP treatment that is patient controlled |
FR2624744B1 (en) * | 1987-12-18 | 1993-09-17 | Inst Nat Sante Rech Med | METHOD FOR REGULATING AN ARTIFICIAL VENTILATION DEVICE AND SUCH A DEVICE |
US5065756A (en) * | 1987-12-22 | 1991-11-19 | New York University | Method and apparatus for the treatment of obstructive sleep apnea |
US4915103A (en) * | 1987-12-23 | 1990-04-10 | N. Visveshwara, M.D., Inc. | Ventilation synchronizer |
GB2215615B (en) * | 1988-03-21 | 1991-12-18 | Sabre Safety Ltd | Breathing apparatus |
GB8812128D0 (en) * | 1988-05-23 | 1988-06-29 | Instr & Movements Ltd | Improvements in ventilators |
DE3822949A1 (en) * | 1988-07-07 | 1990-01-11 | Draegerwerk Ag | PNEUMATIC CONTROL VALVE |
US4846225A (en) * | 1988-09-19 | 1989-07-11 | Keystone International, Inc. | Transmission assembly for use with double block and bleed system |
EP0360885A1 (en) * | 1988-09-26 | 1990-04-04 | Siemens Aktiengesellschaft | Method for modifying the signal-to-noise ratio of proximity sensors, and arrangement for carrying out this method |
US5048515A (en) * | 1988-11-15 | 1991-09-17 | Sanso David W | Respiratory gas supply apparatus and method |
US5134995A (en) * | 1989-05-19 | 1992-08-04 | Puritan-Bennett Corporation | Inspiratory airway pressure system with admittance determining apparatus and method |
US5107831A (en) * | 1989-06-19 | 1992-04-28 | Bear Medical Systems, Inc. | Ventilator control system using sensed inspiratory flow rate |
GB8920499D0 (en) * | 1989-09-11 | 1989-10-25 | Micro Medical Ltd | Apparatus for measuring airway resistance |
US5148802B1 (en) * | 1989-09-22 | 1997-08-12 | Respironics Inc | Method and apparatus for maintaining airway patency to treat sleep apnea and other disorders |
US5239995A (en) * | 1989-09-22 | 1993-08-31 | Respironics, Inc. | Sleep apnea treatment apparatus |
US5103854A (en) * | 1990-01-22 | 1992-04-14 | Vernay Laboratories, Inc. | Low pressure check valve for artificial respiration devices |
US4986310A (en) * | 1990-01-22 | 1991-01-22 | Vernay Laboratories, Inc. | Low pressure check valve |
US5161525A (en) * | 1990-05-11 | 1992-11-10 | Puritan-Bennett Corporation | System and method for flow triggering of pressure supported ventilation |
US5117819A (en) * | 1990-09-10 | 1992-06-02 | Healthdyne, Inc. | Nasal positive pressure device |
US5099837A (en) * | 1990-09-28 | 1992-03-31 | Russel Sr Larry L | Inhalation-based control of medical gas |
DE4122069A1 (en) * | 1991-07-04 | 1993-01-07 | Draegerwerk Ag | METHOD FOR DETECTING A PATIENT'S BREATHING PHASES IN ASSISTANT VENTILATION METHODS |
US5226449A (en) * | 1992-11-06 | 1993-07-13 | Tri-Clover, Inc. | Manifolds and compound valves with removable valve assemblies |
US5438980A (en) * | 1993-01-12 | 1995-08-08 | Puritan-Bennett Corporation | Inhalation/exhalation respiratory phase detection circuit |
-
1993
- 1993-01-12 US US08/003,129 patent/US5438980A/en not_active Expired - Lifetime
- 1993-12-22 AU AU52628/93A patent/AU669237B2/en not_active Ceased
- 1993-12-27 DE DE69333268T patent/DE69333268T2/en not_active Expired - Lifetime
- 1993-12-27 DE DE0606687T patent/DE606687T1/en active Pending
- 1993-12-27 EP EP93250364A patent/EP0606687B1/en not_active Expired - Lifetime
-
1994
- 1994-01-05 CA CA002112884A patent/CA2112884C/en not_active Expired - Lifetime
- 1994-01-11 JP JP00116594A patent/JP3682986B2/en not_active Expired - Fee Related
-
1995
- 1995-09-18 US US08/529,670 patent/US5630411A/en not_active Expired - Lifetime
Also Published As
Publication number | Publication date |
---|---|
AU5262893A (en) | 1994-07-21 |
CA2112884A1 (en) | 1994-07-13 |
DE69333268D1 (en) | 2003-12-04 |
EP0606687B1 (en) | 2003-10-29 |
US5630411A (en) | 1997-05-20 |
AU669237B2 (en) | 1996-05-30 |
US5438980A (en) | 1995-08-08 |
JP3682986B2 (en) | 2005-08-17 |
EP0606687A2 (en) | 1994-07-20 |
DE69333268T2 (en) | 2004-08-12 |
EP0606687A3 (en) | 1994-10-19 |
JPH0747126A (en) | 1995-02-21 |
DE606687T1 (en) | 1995-06-14 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA2112884C (en) | Inhalation/exhalation respiratory phase detection circuit | |
AU636628B2 (en) | Inspiratory airway pressure system | |
US8567398B2 (en) | Pressure support system and method | |
US10183134B2 (en) | Insufflation/exsufflation airway clearance apparatus | |
CA2160509C (en) | Standby control for cpap apparatus | |
US5551419A (en) | Control for CPAP apparatus | |
US6467477B1 (en) | Breath-based control of a therapeutic treatment | |
US7134434B2 (en) | Pressure support system and method and a pressure control valve for use in such a system and method | |
US10166360B2 (en) | System and method for controlling flow during exhalation in a respiratory support system | |
EP0788805A2 (en) | Control for CPAP apparatus | |
JPH049060B2 (en) | ||
WO2002096342A2 (en) | Exhaust port assembly for a pressure support system | |
AU2002310048A1 (en) | Exhaust port assembly for a pressure support system | |
US20070227540A1 (en) | Control Valve for a Ventilator | |
AU662039B2 (en) | Inspiratory airway pressure system | |
WO2006130369A2 (en) | Method and system for non-invasive ventilatory support | |
AU712628B2 (en) | Control for CPAP apparatus | |
JP3247340B2 (en) | Respiratory synchronization type respiratory assist device | |
CA2714044C (en) | Exhaust port assembly for a pressure support system |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
MKEX | Expiry |
Effective date: 20140106 |