US20130327331A1 - Pressure controlled breathing aid - Google Patents
Pressure controlled breathing aid Download PDFInfo
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- US20130327331A1 US20130327331A1 US13/967,214 US201313967214A US2013327331A1 US 20130327331 A1 US20130327331 A1 US 20130327331A1 US 201313967214 A US201313967214 A US 201313967214A US 2013327331 A1 US2013327331 A1 US 2013327331A1
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- patient
- volume
- pressure
- target gas
- gas pressure
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- 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
-
- 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
- A61M16/0051—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes with alarm 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
- A61M16/0057—Pumps therefor
- A61M16/0066—Blowers or centrifugal pumps
- A61M16/0069—Blowers or centrifugal pumps the speed thereof being controlled by respiratory parameters, e.g. by inhalation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes operated by electrical means
- A61M16/022—Control means therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
- A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
- A61M2016/0036—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the breathing tube and used in both inspiratory and expiratory phase
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
- A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
- A61M2016/0039—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the inspiratory circuit
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
- A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
- A61M2016/0042—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the expiratory circuit
Abstract
The ventilation module (8) regulates the inspiratory pressure (P) according to an inspiratory pressure order (AI). A control module (9) compares the breathed volume at each cycle (VTI) with a minimum volume order (VRImini) and varies the pressure order (AI) in the direction tending to maintain the breathed volume (VTI) just over the minimum (VTImini), but keeping the pressure order (AI) within the interval comprised between the two extreme values (AImini, AImaxi). Utilization to combine the advantages of the pressure mode ventilation with those of the volumetric ventilation.
Description
- This application is a Continuation of U.S. application Ser. No. 11/066,797, filed Feb. 25, 2005, which is a Continuation of U.S. application Ser. No. 09/307,511, filed May 7, 1999, now U.S. Pat. No. 6,866,040, which is a Continuation of U.S. application Ser. No. 08/793,956, filed Mar. 12, 1997, now U.S. Pat. No. 5,921,238, which claims priority to International Application No. PCT/FR95/01158, filed Sep. 11, 1995, which claims priority to French Patent Application No. 94 10839, filed on Sep. 12, 1994, now French Patent No. 2724322 B1. The contents of these applications are incorporated herein in their entirety by this reference.
- The present disclosure relates to a pressure-controlled breathing aid.
- Breathing aid devices—or ventilation devices—currently used in mechanical ventilation can be divided into two main groups, namely volumetric devices characterized by the supply of a specified volume in each respiratory cycle, and pressure-controlled devices characterized by the provision of a specified pressure in each respiratory cycle.
- Volumetric devices have the advantage of guaranteeing a specified breathed volume, but they have major disadvantages. In particular, they expose the patient to risks of barotrauma as they tend to apply pressure which increases at the end of insufflation. Furthermore, the patient risks not being matched to the device in the sense that the respiratory reflexes of the patient can appear at different times from those at which the volumes imposed by the device finish being supplied.
- On the contrary, pressure-controlled devices allow better synchronization of the patient with the device and avoid the risk of barotrauma since the maximum pressure supplied is known in advance. On the other hand, the volume supplied to the patient in each cycle and the breathed volume are not guaranteed.
- The purpose of the present invention is to propose a breathing aid device which combines the advantages of both of the known ventilation modes discussed above.
- According to the invention, the pressure mode breathing aid device, comprising means for supplying breathable gas to an inspiratory branch of a patient circuit at an inspiratory pressure, is characterized by:
- means of measuring the breathed volume,
- means of comparing the breathed volume with a command, and
- regulation means to increase the inspiratory pressure in the case of a breathed volume lower than the command, and to reduce the inspiratory pressure in the case of a breathed volume higher than the command.
- Thus, the pressure is adjusted in a direction tending to provide the predetermined volume applied as a command. In this way a volume is guaranteed without taking the risk of increasing the pressure in an uncontrolled manner, nor of creating the particular risk of mismatch between the breathing timing of the patient and that of the device. In particular, the invention is perfectly compatible with devices of the type described in FR-A-2 695 830 in which the device detects the respiratory reflexes of the patient in order to change from inspiratory phases to expiratory phases and vice-versa.
- In order to prevent any risk of barotrauma, it is advantageous to provide means of setting a maximum predetermined pressure which the pressure applied to the patient will not be able to exceed even if the volume supplied is insufficient.
- It is also advantageous to provide a signalling device or other alarm detecting the simultaneous occurrence of insufficient volume and the setting of the pressure at its maximum predetermined value, in order to signal this situation of the device's inability to provide the breathed volume set as a command.
- In the framework of the present invention, the expression “breathed volume” is used to denote both the volume of the breathable gas inspired or expired per unit time and the volume or quantity of gas inspired or expired per breathing cycle.
- Preferably, the adjustment means apply to the inspiratory pressure a pressure variation which is equal in percentage to the difference between the inspiratory volume and the command.
- However, in the case where an extreme value of pressure is predetermined and if the application of such a variation would result in exceeding the extreme value, the new inspiratory pressure is made equal to the extreme value of the pressure.
- Other features and advantageous of the invention will furthermore emerge from the following description relating to non-limitative examples.
- In the accompanying drawings:
-
FIG. 1 is a block diagram of a first embodiment of the device according to the invention; -
FIG. 2 is an operational flowchart of the regulating means of the device ofFIG. 1 ; and -
FIGS. 3 and 4 are two block diagrams similar toFIG. 1 but relating to two embodiments of the device according invention. - In the example shown in
FIG. 1 , the breathing aid device comprises apatient circuit 1 which itself comprises apatient connection 2, namely a facial or nasal mask, or an intubation or tracheotomy tube, connected to aninspiratory branch 3 and to anexpiratory branch 4 by the intermediary of abidirectional branch 5. Theexpiratory branch 4 comprises anexpiration device 6 which, in a way which is not shown, comprises an expiration valve and means of controlling this valve. The expiration valve is closed during the inspiratory phases of the patient's breathing. During the expiratory phases of the patient's breathing, the expiration valve can either be open so that the patient expires at atmospheric pressure, or it can operate like a discharge valve to oblige the patient to expire at a certain predetermined excess pressure. - The
inspiratory branch 3 is connected, at its end furthest from themask 2, to aunit 8 for ventilation through inspiratory aid which comprises means, such as an adjustable speed motor-turbine set, for supplying breathable gas through theinspiratory branch 3 at an adjustable pressure, in the direction of themask 2, means of detecting the patient's respiratory reflexes, for example from instantaneous flow rate variations, and means of controlling the expiration valve of the expiration means 6 and an inspiration valve placed in theinspiratory branch 3 in order to open the inspiration valve and to close the expiration valve during the inspiratory phase, and to close the inspiration valve and to release the expiration valve during the expiratory phases. Thus, in the inspiratory phase, the patient is connected in a gas-tight manner with theinspiratory branch 3, and the volume flowing in theinspiratory branch 3 corresponds to the volume of gas inspired. And during the expiratory phases, the patient is connected in a gas-tight manner with theexpiratory branch 4 and the volume flowing in theexpiratory branch 4 corresponds to the volume of gas expired. - Such inspiratory aid devices, or inspiratory aid devices of the same kind are described in the prior art, in particular in FR-A-2 695 830.
- The
ventilation unit 8 can comprise pressure control means by means of which the pressure P detected in theinspiratory branch 3 by adetector 10 is compared with a pressure command AI in order to adjust, for example, the speed of rotation of the motor-turbine set in the direction tending to make the pressure P equal to the command AI. - According to the invention, the breathing aid device comprises means 11 of regulating the patient's breathed volume. The regulating means 11 comprise a
control unit 9 for controlling the pressure command AI which theventilation unit 8 must apply to theinspiratory branch 3 during the inspiratory phases. - The regulating means 11 furthermore comprise a
unit 12 for measuring the volume VTI inspired by the patient during each breathing cycle. Theunit 12 provides thecontrol unit 9 with a signal indicative of the volume VTI. Thecontrol unit 9 comprises aninput 13 for receiving the signal VTI, and threeinputs - In general, the
control unit 9 compares the measured volume VTI with the command VTImini and adjusts the pressure command AI in the direction tending to bring the measured volume VTI towards the command VTImini, without however causing the command AI to move outside of the range included between the two extreme values AImini and AImaxi. Within this range, thecontrol unit 9 tends to increase the command AI when the measured volume VTI is lower than the command VTImini, and to reduce the pressure command AI in the opposite case. - When starting up the device, the commands VTImini and AImini are chosen such that the breathed volume VTI is established at a value higher than VTImini when the pressure command AI is equal to AImini. Thus, if the patient breathes as expected, the pressure command AI stabilises at AImini with a breathed volume above the minimum command VTImini. It is only in the event of a breathing anomaly or incident, for example a partial obstruction of the breathing channels, that the measured breathed volume VTI is likely to become lower than VTImini, thus causing an increase in the command AI generated by the
control unit 9. When the breathing becomes normal again, the breathed volume again becomes higher than the command VTImini, such that thecontrol unit 9 returns the pressure command AI more or less rapidly to the value AImini. - The flowchart used by the
control unit 9 will now be described in greater detail with reference toFIG. 2 . At the start, AI is made to equal to AImini (step 18). - Then, at the end of each breathing cycle, or during each expiratory phase, the measurement VTI of the volume inspired during the preceding inspiratory phase is acquired (step 19) and is then compared with the command VTImini by the
test 21. If the measured volume VTI is greater than or equal to VTImini, in other words if the volume inspired by the patient is satisfactory, a test 22 determines if the pressure command AI is or is not greater than the minimum AImini. If the pressure command is equal to the minimum, the conditions are therefore ideal (volume at least equal to the minimum, minimum pressure) and the sequence therefore returns directly tostep 19 for acquiring the next inspired volume measurement. In the opposite case, advantage will be taken of the fact that the inspired volume is satisfactory in order to attempt to reduce the pressure command by astep 23 in which there is applied to the pressure command AI, expressed in relative value, a variation equal in percentage and opposite in sign to the difference between the measured inspired volume VTI and the command VTImini. The formula is such that, in the particular case in which the measured volume VTI is equal to VTImini, no modification is applied to the pressure command AI (0% variation). - Returning now to the
test 21 on the measured volume VTI, if the latter is lower than the command VTImini, an attempt will be made to increase the pressure command AI in order to assist the patient more. But prior to this, by atest 24, it will be checked that the pressure command AI has not already reached the maximum AImaxi. If the answer is yes, an alarm is triggered (step 26) to indicate the necessity of an urgent intervention. - On the other hand, if the pressure command AI is not yet equal to AImaxi, the sequence returns as before to step 23 in which there will be applied to the command AI a variation equal in percentage and opposite in sign to the difference between the measured volume VTI and the command VTImini.
- Before actually applying the command AI, reduced or increased such as it has been computed in
step 23, to the input of theventilation unit 8, it will firstly be checked, by a test 27, that the new computed AI value does not exceed the maximum AImaxi and, by atest 28, that it is not less than the minimum AImini. - If the new AI value has gone beyond one or other of these extreme values, the command AI which will be applied to the
ventilation unit 8 will be equal to the extreme value in question (steps 29 and 31). - The example shown in
FIG. 3 will only be described where it differs with respect to the example shown inFIG. 1 . - In the example of
FIG. 3 , the breathed volume is no longer measured by means of the volume inspired in each cycle but by means of the volume VTE expired in each cycle. For this purpose, theVTI measuring unit 12 in theinspiratory branch 3 has been eliminated and it has been replaced by aVTE measuring unit 32 in theexpiratory branch 4, which sends the measured VTE, indicated at 33, to thecontrol unit 9. - The minimum breathed volume command applied to the
control unit 9 is therefore the command VTEmini for the volume expired per cycle, in order to be able to be compared directly with the measured VTE 33 provided by theunit 32. - It can be advantageous to select, case by case, measurement of the inspired volume or measurement of the expired volume. This is the solution proposed by the embodiment shown in
FIG. 4 , which will be described only where it differs with respect to the example shown inFIG. 1 . - The measuring
unit 42 is this time installed in thebidirectional branch 5 of thepatient circuit 1 and it comprises means 43 of selecting the direction of flow in which the volume is to be measured. In accordance with this selection, theunit 42 provides, by choice, a measurement of VTI or of VTE, indicated at 44. In accordance with the operating mode of the measuringunit 42, thecontrol unit 9 interprets the input applied at 14 as an inspired volume command or as an expired volume command. There is no longer any measuring unit in theinspiratory branch 3 nor in theexpiratory branch 4. - In all of the described embodiments, the speed of execution of the flowchart in
FIG. 2 is sufficient for the measurement carried out in each breathing cycle to make it possible to correct the pressure applied during the following inspiratory phase. When the measurement is based on the expired volume, it is however possible that the pressure correction will occur only during, and not from the start, of the following inspiratory phase. - The invention is applicable to all ventilators capable of measuring the volumes delivered and of automatically controlling the value of the insufflation pressure.
- The invention is applicable to all methods of ventilation using pressure control, and in particular to “inspiratory aid” and “controlled pressure” methods. Inspiratory aid is a method consisting in maintaining a substantially constant pressure in the patient circuit during the insufflation, the patient initiating the start and end of the insufflation by his respiratory reflexes. The controlled pressure method is identical to the inspiratory aid method except that the patient does not initiate the end of the insufflation, the latter being determined by a fixed time.
- It would also be conceivable for the control unit, instead of adjusting the pressure command AI applied to the ventilation unit, to adjust, for example, the speed of rotation of the motor turbine set, or the electrical power supplied to it. It would then be possible to avoid abnormal pressures in the
inspiratory branch 3 by comparing the pressure in theinspiratory branch 3 with limits such as AImini and AImaxi, and by initiating a corrective modification of the speed or of the power of the motor turbine set in the case of exceeding, or of risk of exceeding such limits.
Claims (17)
1. (canceled)
2. A method for controlling a breathing aid apparatus, while providing breathing aid to a patient at a target gas pressure, the method comprising:
determining a breathed volume of the patient;
comparing the determined breathed volume with a predetermined volume threshold;
resetting the target gas pressure based at least on the determined breathed volume of the patient and a minimum pressure threshold, by increasing the target gas pressure if the determined breathed volume is lower than the predetermined volume threshold and by decreasing the target gas pressure to at most the minimum pressure threshold if the determined breathed volume is higher than the predetermined volume threshold; and
delivering the reset target gas pressure to the patient.
3. A method according to claim 2 , wherein the step of resetting the target gas pressure is further based on a maximum pressure threshold, by increasing the target gas pressure to at most the maximum pressure threshold if the determined breathed volume is lower than the predetermined volume threshold.
4. A method according to claim 2 , wherein the determined breathed volume for the patient comprises a volume inspired by the patient.
5. A method according to claim 2 , wherein the determined breathed volume for the patient comprises a volume expired by the patient.
6. A method for controlling a breathing aid apparatus while providing breathing aid to a patient, the method comprising:
delivering a first target gas pressure to a patient;
determining an actual breathed volume for the patient during the step of delivering the first target gas pressure to the patient;
setting a second target gas pressure based on both the determined breathed volume and a preset threshold volume, wherein the second target gas pressure is higher than the first target gas pressure if the actual breathed volume is lower than the preset threshold volume and the second target gas pressure is lower than the second target gas pressure if the actual breathed volume is higher than the preset threshold volume;
comparing the second target gas pressure to a minimum pressure threshold; and
delivering gas to the patient according to the second target gas pressure and the step of comparing the second target gas pressure to the minimum pressure threshold.
7. A method according to claim 6 ,
wherein the comparing step further comprises determining that the second target gas pressure is greater than the minimum pressure threshold; and
wherein the step of delivering gas to the patient according to the second target gas pressure and the comparing step further comprises delivering the second target gas pressure to the patient.
8. A method according to claim 6 ,
wherein the comparing step further comprises determining that the second target gas pressure is less than the minimum pressure threshold; and
wherein the step of delivering gas to the patient according to the second target gas pressure and the comparing step further comprises delivering the minimum pressure threshold to the patient.
9. A method according to claim 6 ,
wherein the comparing step further comprises comparing the second target gas pressure to a maximum pressure threshold.
10. A method according to claim 9 ,
wherein the comparing step further comprises determining that the second target gas pressure is less than the maximum pressure threshold; and
wherein the step of delivering gas to the patient according to the second target gas pressure and the comparing step further comprises delivering the second target gas pressure to the patient.
11. A method according to claim 9 ,
wherein the comparing step further comprises determining that the second target gas pressure is greater than the maximum pressure threshold; and
wherein the step of delivering gas to the patient according to the second target gas pressure and the comparing step further comprises delivering the maximum pressure threshold to the patient.
12. A method according to claim 6 , wherein the actual breathed volume for the patient comprises to volume inspired by the patient.
13. A method according to claim 6 , wherein the actual breathed volume for the patient comprises a volume expired by the patient.
14. A breathing aid device, comprising:
a patient connection;
an inspiratory branch in fluid communication with said patient connection, said inspiratory branch including an inspiration valve;
an expiratory branch in fluid communication with said patient connection and said inspiratory branch, said expiratory branch including an expiration valve;
a pressure detector operatively connected to said inspiratory branch;
a source of breathable gas at an adjustable pressure in fluid communication with said inspiratory branch;
a valve controller for controlling the inspiration valve and the expiration valve during expiration and during inspiration;
a pressure controller for adjusting a pressure of the source of breathable gas based on a pressure command;
a control unit for providing the pressure command to said pressure controller; and
a measuring unit for providing a signal to the control unit indicative of a measured volume of breathable gas detected per breathing cycle to the patient connection based at least on the pressure detected by the pressure detector,
wherein the control unit compares the measured volume from the measuring unit with a preset threshold volume and adjusts the pressure command in a direction tending to bring the signal from said measuring unit toward the preset threshold volume, and
wherein the control unit maintains the pressure command above a set minimum pressure threshold.
15. The breathing aid device of claim 14 , wherein the control unit maintains the pressure command below a set maximum pressure threshold.
16. The breathing aid device of claim 14 , wherein the measured volume for the patient comprises a volume inspired by the patient.
17. The breathing aid device of claim 14 , wherein the measured volume for the patient comprises a volume expired by the patient.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
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US13/967,214 US20130327331A1 (en) | 1994-09-12 | 2013-08-14 | Pressure controlled breathing aid |
Applications Claiming Priority (7)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
FR9410839 | 1994-09-12 | ||
FR9410839A FR2724322A1 (en) | 1994-09-12 | 1994-09-12 | PRESSURE CONTROLLED BREATHING AID |
US08/793,956 US5921238A (en) | 1994-09-12 | 1995-09-11 | Pressure-controlled breathing aid |
US09/307,511 US6866040B1 (en) | 1994-09-12 | 1999-05-07 | Pressure-controlled breathing aid |
US11/066,797 US20050139212A1 (en) | 1994-09-12 | 2005-02-25 | Pressure-controlled breathing aid |
US12/140,095 US8573206B2 (en) | 1994-09-12 | 2008-06-16 | Pressure-controlled breathing aid |
US13/967,214 US20130327331A1 (en) | 1994-09-12 | 2013-08-14 | Pressure controlled breathing aid |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
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US12/140,095 Continuation US8573206B2 (en) | 1994-09-12 | 2008-06-16 | Pressure-controlled breathing aid |
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US20130327331A1 true US20130327331A1 (en) | 2013-12-12 |
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US09/307,511 Expired - Lifetime US6866040B1 (en) | 1994-09-12 | 1999-05-07 | Pressure-controlled breathing aid |
US11/066,797 Abandoned US20050139212A1 (en) | 1994-09-12 | 2005-02-25 | Pressure-controlled breathing aid |
US12/140,095 Expired - Lifetime US8573206B2 (en) | 1994-09-12 | 2008-06-16 | Pressure-controlled breathing aid |
US13/967,214 Abandoned US20130327331A1 (en) | 1994-09-12 | 2013-08-14 | Pressure controlled breathing aid |
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US09/307,511 Expired - Lifetime US6866040B1 (en) | 1994-09-12 | 1999-05-07 | Pressure-controlled breathing aid |
US11/066,797 Abandoned US20050139212A1 (en) | 1994-09-12 | 2005-02-25 | Pressure-controlled breathing aid |
US12/140,095 Expired - Lifetime US8573206B2 (en) | 1994-09-12 | 2008-06-16 | Pressure-controlled breathing aid |
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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 |
US6866040B1 (en) * | 1994-09-12 | 2005-03-15 | Nellcor Puritan Bennett France Developpement | Pressure-controlled breathing aid |
US6024089A (en) | 1997-03-14 | 2000-02-15 | Nelcor Puritan Bennett Incorporated | System and method for setting and displaying ventilator alarms |
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 |
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Also Published As
Publication number | Publication date |
---|---|
US20050139212A1 (en) | 2005-06-30 |
US20100024820A1 (en) | 2010-02-04 |
US8573206B2 (en) | 2013-11-05 |
US6866040B1 (en) | 2005-03-15 |
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