US20050039748A1 - Device and process for supplying respiratory gas under pressure or volumetrically - Google Patents

Device and process for supplying respiratory gas under pressure or volumetrically Download PDF

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Publication number
US20050039748A1
US20050039748A1 US10/899,022 US89902204A US2005039748A1 US 20050039748 A1 US20050039748 A1 US 20050039748A1 US 89902204 A US89902204 A US 89902204A US 2005039748 A1 US2005039748 A1 US 2005039748A1
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pressure
expiration
circuit
valve
inspiration
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US10/899,022
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Claude Andrieux
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Airox SAS
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Airox SAS
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Assigned to AIROX reassignment AIROX ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: ANDRIEUX, CLAUDE
Publication of US20050039748A1 publication Critical patent/US20050039748A1/en
Priority to US11/781,013 priority Critical patent/US7717113B2/en
Priority to US12/752,501 priority patent/US8800557B2/en
Abandoned legal-status Critical Current

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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
    • A61M16/10—Preparation of respiratory gases or vapours
    • 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
    • A61M16/20—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
    • 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
    • A61M16/206—Capsule valves, e.g. mushroom, membrane valves
    • 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
    • A61M16/208—Non-controlled one-way valves, e.g. exhalation, check, pop-off non-rebreathing valves
    • 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
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/105—Filters
    • A61M16/106—Filters in a path
    • A61M16/107—Filters in a path in the inspiratory path
    • 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
    • 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
    • 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
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/42—Reducing noise

Definitions

  • the present invention relates to a device and process for supplying respiratory gas.
  • Devices for supplying respiratory gas are used particularly in the treatment of respiratory ailments of adult or infant patients.
  • Such devices are adapted to supply a quantity of air, if desired with added oxygen, either in the form of a quantified breathable volume, or in the form of a first predetermined pressure called inspiration pressure and a second predetermined pressure called expiration pressure.
  • WO 00/24447 relates to a device for supplying respiratory gas provided with a compressor delivering a flow of gas under pressure to a patient through a downstream accumulator/silencer and a flow rate regulating valve. According to this document, the surplus of unneeded gas is returned to an upstream filter/accumulator through a bypass valve so as to limit the loss of respiratory gas.
  • FR 2 663 547 A1 relates to apparatus for continuously providing an overpressure of respiratory gas; this apparatus using a high speed turbine supplying gas under constant predetermined pressure regulated by measuring the pressure at the respiratory mask of the patient.
  • This apparatus is passive in that the pressure is maintained continuously, the expiration phases being possible thanks to a calibrated loss at the respiratory mask of the patient.
  • FR 2 822 384 A1 in the name of the applicant relates to a mixed pulmonary ventilator provided with a flow generator, the circulation means permitting re-injecting the flow upstream of the generator during an expiration phase of the patient, the circulation means comprising particularly a regulating valve comprising two flaps actuated by the same actuator permitting several modes of regulation and an optimization of the flow as a function of the inspiration and expiration phases.
  • the speed of rotation of the generator is maintained constant, the pressure in the patient circuit being controlled by the two flaps which permit return of the gas to the generator particularly during the expiration phases.
  • the present invention seeks to provide a device for supplying respiratory gas, that is improved in that its operation uses an automatic control of the turbine for the inspiration and expiration phases and does not use a return system for gas upstream of the turbine, thereby simplifying the system, whilst permitting operation with a sealed circuit at the respiratory mask or of the intubation device of the patient during the inspiration phases and the loss during the expiration phases.
  • the present invention relates to a device for supplying respiratory gas to a patient according to respiratory cycles, comprising a gas for a generator, a circuit for bringing the gaseous flow to a respiratory mask or intubation device of the patient, means for measuring the pressure and/or for measuring the gaseous flow rate, means for computing the parameters of pressure and/or flow rate and control means of the speed of rotation of the generator, in which device the measuring means act on the speed control means through computer means so as automatically to control the speed of rotation of the turbine as a function of the inspiration and expiration phases as a function of patient pressure signals and/or inspiration flow rate signals.
  • the pressure measuring means can particularly comprise a patient pressure sensor and/or an expiration valve pressure sensor.
  • the flow rate measuring means can particularly comprise an inspiration flow rate sensor disposed adjacent the outlet of the generator.
  • the flow rate measuring means can comprise an expiration flow rate sensor in a patient return circuit.
  • the device can comprise a passive member for generating a pressure drop in the supply circuit.
  • This passive member can particularly be a non-return flap if desired associated with a passive flap for admission of external air downstream of the non-return flap in the supply circuit.
  • the device comprises an expiration circuit provided with an expiration valve and a proportional electro-valve for controlling said expiration valve by application of a counter-pressure.
  • the invention relates moreover to a process for providing a respiratory gas according to respiratory cycles, comprising inspiration and expiration phases, according to which said measurement means and said computing means act on said speed control means so as automatically to control the speed of rotation of the turbine as a function of the pressure and/or volume standards, of the detection of the inspiration and expiration phases, of patient pressure signals and/or inspiration flow rate signals, the supply of the respiratory gas taking place as to pressure or as to volume.
  • the process can preferably comprise phases of pressure increase with pressure increase slopes effected by acceleration of the turbine.
  • transition between an inspiration phase and an expiration phase can be effected by controlled deceleration of the turbine.
  • the process can comprise, during expiration phases, a control of an expiration valve with a pressure regulating member of the first circuit, via a proportional electro-valve which is part of a second circuit, the valve being a part of a third circuit connected to the mask or to the intubation device.
  • the computing means and the control means of the speed of rotation of the generator can adapt the speed of the turbine as a function of an expiration pressure threshold beyond a regulated loss by the expiration valve so as to create a rinsing flow rate in the first circuit.
  • an expiration valve which is a part of a third circuit connected to the mask or to the intubation device, can be controlled for following the pressure through a proportional electro-valve and a second circuit.
  • the process can comprise a measurement of expiration flow rate and a measurement of inspiration flow rate.
  • FIG. 1 is a schematic view of a device for supplying respiratory gas according to the invention.
  • the device 1 for supplying respiratory gas or ventilation device comprises a generator 2 of gaseous flow provided with a turbine 2 a of low inertia and high rated speed.
  • This gaseous flow generator is disposed in a chamber 20 , preceded by a filter 21 for ambient air inlet, by an upstream and downstream sound deadening means 22 and 23 .
  • the turbine 2 a is for example a turbine with a maximum speed of rotation of the order of 50,000 rpm, adapted to supply a pressure of 70 millibar above ambient and a flow rate of the order of 200 l/min.
  • the air flow generator thus comprises a micro-turbine with low inertia, driven by an electric motor, controlled by a computer or a computer means 9 so as to provide a wide range of flow rates and pressures.
  • the generator is connected to a first circuit 3 called a circuit for supplying gaseous flow toward a respiratory mask 4 or a intubation device (not shown) of the patient.
  • the generator is controlled by control means 10 in the form of an electronic control card connected to a supply 24 and to computer means 9 in the form of an electronic card with a microprocessor provided with control software and connected to a control interface 25 with a screen and a keyboard.
  • the computer means are connected to means 5 , 6 , 7 , 8 for measuring the pressure and/or for measuring the flow rate of the gaseous flow in the form of sensors.
  • the sensor 6 is a pressure sensor connected to a first circuit 3 which is a circuit for supplying gas to the mask 4 or intubation device of the patient.
  • a sensor 6 is disposed in the apparatus 1 and connected to the mask 4 or to the intubation device via a tube 6 a.
  • the sensor 5 is a pressure sensor connected to a second circuit 16 comprising a proportional electro-valve 15 whose operation will be described later.
  • the sensor 7 is an inspiration flow rate sensor disposed in the first circuit, in a laminator 26 controlling the flow of gas leaving the generator.
  • An expiration flow rate sensor 8 in the third circuit 11 called patient return circuit, completes the measurement means.
  • the computation means 9 controls the members such as the generator and the proportional electro-valve 15 as a function of standards entered into the interface 25 as a function of the ventilation programs and as a function of the pressure and/or flow rate parameters from the sensors.
  • the measuring means 5 , 6 , 7 , 8 , the computing means 9 and the speed control means 10 coact in the first instance automatically to control the speed of rotation of the turbine 2 a as a function of the inspiration and expiration phases and as a function of the patient pressure signals and/or inspiration flow rate signals.
  • the device according to FIG. 1 comprises a passive member 12 for generating a pressure drop in the supply circuit in the form of a non-return flap 12 mounted in the first circuit 3 . Thanks to this member, the pressure on the generator side is always slightly greater than the pressure in the circuit 3 on the mask supply side or intubation device, which permits among other things a better regulation of the operation of the device.
  • the circuit 3 Downstream of this non-return valve 12 , the circuit 3 comprises a passive flap 13 for the admission of external air. This flap permits limiting the inspiration force of the patient by spontaneous respiration through the machine when the latter is not in operation.
  • a third circuit 11 On the mask side 4 or the intubation device after the circuit 3 for supplying gas, is located a third circuit 11 called an expiration circuit.
  • This expiration circuit comprises an expiration valve 14 with a membrane permitting opening a passage either directly to the exterior or through tubing 11 a toward a laminator 27 and an air outlet 28 .
  • the second circuit 16 provided with proportional electro-valve 15 of the three-way type.
  • This electro-valve 15 receives along a first path a pressure outlet of the generator, comprises a second path to vacuum and is connected by a third path to the valve 14 .
  • the electro-valve permits controlling the valve 14 by applying a counter-pressure which closes the valve or limits its opening such that the expiration pressure will remain higher than the pressure of the second circuit 16 .
  • the electro-valve is controlled such that the pressure of the generator will be blocked, the second path of the free air being placed in communication with the third path.
  • a controlled expiration device is constructed about the expiration valve 14 controlled by the electro-valve valve 15 connected to the flow generator, this electro-valve valve 15 permitting sending a portion of the generated flow to the expiration valve so as to oppose its opening.
  • the proportional electro-valve 15 is controlled by control means coupled to the computation means 9 and according to the example disposed on the card receiving the computing means 9 .
  • This device thus permits in operation, the control of the speed of the turbine 2 a and the control of the expiration valve through the electro-valve to provide several modes of operation and particularly modes of volumetric operation.
  • several modes of operation are sought and particularly modes of operation with inspiration and expiration pressure standards or modes for which a volume of air called a target volume is predetermined, or mixed modes.
  • the operation of the apparatus is based on a system of self-adaptive control in a closed loop, of the speed of the flow generator.
  • This flow generator is associated a controlled expiration device, without a member for regulation of the supplemental principal flow.
  • the detection of an increasing slope of pressure can be translated by a level of acceleration of the turbine 2 a and the detection of the transition between the inspiration phase and the expiration phase can be translated by a deceleration of the turbine 2 a.
  • This control is effected by inspiration pressure or flow rate signals and according to control laws, based on proportional and integral coefficients, which differ according to the modes of ventilation, the adjustments of the pressure or flow rate and in particular the phases of the respiratory cycle.
  • the operation of the device and the associated ventilation process will be explained for example in the case of a mode in which an inspiration pressure Pi, an expiration pressure Pe as well as a form of obtaining the inspiration pressure based on the time of pressure increase, are fixed.
  • the time of insufflation is here dependent on a level of triggering the expiration adjusted on the basis of the measurement of a drop in flow rate measured in the inspiration detector 7 , after obtaining a maximum insufflation flow rate available for the patient.
  • a limiting parameter for the time of insufflation is the minimum threshold corresponding to the slope of pressure measured; another parameter is a maximum threshold of safety for the insufflation time which corresponds to the last inspiration time carried out or at most to three seconds.
  • Other safety parameters can be taken into account such as a safety frequency.
  • the objective of the insufflation phase is the establishment of a pressure level Pi with a variable time of increase and a holding time depending on the behavior of the associated flow rate.
  • the objective of the expiration phase is to maintain a pressure level Pe up to the beginning of the following inspiration phase, but also sufficiently to rinse the circuit so as to evacuate the residual expired gases.
  • the phases of pressure increase with increased slopes of pressure are carried out by an acceleration of the turbine 2 a.
  • the pressure is controlled in the inspiration pressure sensor 6 .
  • the computation means control the expiration valve 14 , which is part of the third circuit 11 connected to the mask 4 or to the intubation device, via the proportional electro-valve 15 and the second circuit 16 , according to pressure.
  • the transition between an inspiration phase and an expiration phase is effected itself by a controlled deceleration of the turbine 2 a and the expiration valve 14 , which is part of the third circuit 11 connected to the mask 4 or to the intubation device, is controlled, through the proportional electro-valve 15 and the second circuit 16 , with a pressure regulation member of the first circuit 3 .
  • the computation means and the means for controlling the speed of rotation of the generator adapt the speed of the turbine 2 as a function of an expiration pressure threshold beyond a loss regulated by the expiration valve 14 so as to create the rinsing flow rate of the first circuit.
  • the non-return clapet system 12 and the spontaneous respiration clapet 13 permit balancing the rinsing pressure which is maintained sufficiently low to limit the phenomenon of expiration braking without being canceled to avoid all heating of the turbine 2 a.
  • the objective of the insufflation phase is the distribution of a current volume Vt with a suitable flow rate shape and during a time fixed by the frequency levels and the ratio of cycling regulated by the interface 25 .
  • the operator enters by the interface means a target volume standard into the computation means 9 which, as a function of this parameter and other parameters entered by the interface such as the frequency of minimum cycle and/or safety, cycling ratio, high pressure threshold, will permanently adjust the insufflation pressure between a low pressure threshold and a maximum pressure threshold so as to maintain the current volume inhaled by the patient as nearly as possible to a predefined target volume, namely for example between target volume Vt and target volume Vt+20%.
  • the target volume mode it is particularly necessary to be able at the same time to adjust precisely the pressure by pressure steps between the cycles.
  • the steps between cycles are defined between 0.5 millibar and 2 millibars so as to react immediately to the detection of an unbalance without having a strong reaction that would be uncomfortable to the patient.
  • This pressure adjustment is made according to the invention without a regulator device such as the generator but by controlling the speed of the turbine 2 a of the generator 2 as a function of the pressure measurements of the sensor 6 of the pressure of the patient and by causing to operate the expiration circuit comprising the expiration valve 14 following through the proportional electro-valve 15 in which, in this configuration, the flow generator is connected to the second circuit, the non-return flap 12 of the first circuit 3 permitting preserving a pressure slightly greater in the second circuit relative to the first circuit.
  • the device permits providing a respiratory gas according to respiratory cycles comprising phases of inspiration and expiration, the measuring means 5 , 6 , 7 , 8 and the computation means 9 acting on the speed control means 10 so as automatically to control the speed of rotation of the turbine 2 as a function of the pressure and/or volume standards, of the detection of inspiration and expiration phases, of patient pressure signals and/or inspiration flow rate signals.
  • the expiration valve 14 is controlled by the pressure during the inspiration phase and by a regulating member during the expiration phase.
  • the device according to the invention thus permits ventilating a patient by pressure or volume with a patient circuit provided with an expiration device controlled by a simple control of the speed of the turbine.

Abstract

A device for supplying respiratory gas to a patient according to respiratory cycles, includes a gaseous flow rate generator provided with a turbine with low inertia and high nominal speed, a first supply circuit for the gaseous flow toward a respiratory mask or an intubation elements of the patient, elements for measuring pressure and/or measuring flow rate of the gaseous flow, the computation elements for parameters of pressure and/or flow rate, and elements for controlling the speed of rotation of the generator. The measuring elements, the computation elements and the speed control elements coact automatically to control the speed of rotation of the turbine as a function of the inspiration and expiration phases and as a function of patient pressure signals and/or inspiration flow rate signals.

Description

  • The present invention relates to a device and process for supplying respiratory gas.
  • Devices for supplying respiratory gas are used particularly in the treatment of respiratory ailments of adult or infant patients.
  • Such devices are adapted to supply a quantity of air, if desired with added oxygen, either in the form of a quantified breathable volume, or in the form of a first predetermined pressure called inspiration pressure and a second predetermined pressure called expiration pressure.
  • WO 00/24447 relates to a device for supplying respiratory gas provided with a compressor delivering a flow of gas under pressure to a patient through a downstream accumulator/silencer and a flow rate regulating valve. According to this document, the surplus of unneeded gas is returned to an upstream filter/accumulator through a bypass valve so as to limit the loss of respiratory gas.
  • FR 2 663 547 A1 relates to apparatus for continuously providing an overpressure of respiratory gas; this apparatus using a high speed turbine supplying gas under constant predetermined pressure regulated by measuring the pressure at the respiratory mask of the patient. This apparatus is passive in that the pressure is maintained continuously, the expiration phases being possible thanks to a calibrated loss at the respiratory mask of the patient.
  • FR 2 822 384 A1 in the name of the applicant relates to a mixed pulmonary ventilator provided with a flow generator, the circulation means permitting re-injecting the flow upstream of the generator during an expiration phase of the patient, the circulation means comprising particularly a regulating valve comprising two flaps actuated by the same actuator permitting several modes of regulation and an optimization of the flow as a function of the inspiration and expiration phases. According to this document, the speed of rotation of the generator is maintained constant, the pressure in the patient circuit being controlled by the two flaps which permit return of the gas to the generator particularly during the expiration phases.
  • It remains that the circuits and systems necessary to provide and to regulate the levels of pressure and/or volumetric quantities of respiratory gas, are complicated and cumbersome, the control of the flaps and valves being sensitive.
  • The present invention seeks to provide a device for supplying respiratory gas, that is improved in that its operation uses an automatic control of the turbine for the inspiration and expiration phases and does not use a return system for gas upstream of the turbine, thereby simplifying the system, whilst permitting operation with a sealed circuit at the respiratory mask or of the intubation device of the patient during the inspiration phases and the loss during the expiration phases.
  • To this end, the present invention relates to a device for supplying respiratory gas to a patient according to respiratory cycles, comprising a gas for a generator, a circuit for bringing the gaseous flow to a respiratory mask or intubation device of the patient, means for measuring the pressure and/or for measuring the gaseous flow rate, means for computing the parameters of pressure and/or flow rate and control means of the speed of rotation of the generator, in which device the measuring means act on the speed control means through computer means so as automatically to control the speed of rotation of the turbine as a function of the inspiration and expiration phases as a function of patient pressure signals and/or inspiration flow rate signals.
  • The pressure measuring means can particularly comprise a patient pressure sensor and/or an expiration valve pressure sensor.
  • The flow rate measuring means can particularly comprise an inspiration flow rate sensor disposed adjacent the outlet of the generator.
  • The flow rate measuring means can comprise an expiration flow rate sensor in a patient return circuit.
  • In a particular embodiment, the device can comprise a passive member for generating a pressure drop in the supply circuit. This passive member can particularly be a non-return flap if desired associated with a passive flap for admission of external air downstream of the non-return flap in the supply circuit.
  • According to a particular embodiment of the invention, the device comprises an expiration circuit provided with an expiration valve and a proportional electro-valve for controlling said expiration valve by application of a counter-pressure.
  • The invention relates moreover to a process for providing a respiratory gas according to respiratory cycles, comprising inspiration and expiration phases, according to which said measurement means and said computing means act on said speed control means so as automatically to control the speed of rotation of the turbine as a function of the pressure and/or volume standards, of the detection of the inspiration and expiration phases, of patient pressure signals and/or inspiration flow rate signals, the supply of the respiratory gas taking place as to pressure or as to volume.
  • The process can preferably comprise phases of pressure increase with pressure increase slopes effected by acceleration of the turbine.
  • More particularly, the transition between an inspiration phase and an expiration phase can be effected by controlled deceleration of the turbine.
  • The process can comprise, during expiration phases, a control of an expiration valve with a pressure regulating member of the first circuit, via a proportional electro-valve which is part of a second circuit, the valve being a part of a third circuit connected to the mask or to the intubation device.
  • Preferably, the computing means and the control means of the speed of rotation of the generator can adapt the speed of the turbine as a function of an expiration pressure threshold beyond a regulated loss by the expiration valve so as to create a rinsing flow rate in the first circuit.
  • More particularly, during insufflation phases corresponding to the inspiration phases, an expiration valve, which is a part of a third circuit connected to the mask or to the intubation device, can be controlled for following the pressure through a proportional electro-valve and a second circuit.
  • In a particular embodiment, the process can comprise a measurement of expiration flow rate and a measurement of inspiration flow rate.
  • Other advantages and characteristics of the invention will become apparent from a reading of the description which follows, of a non-limiting example of the invention, with reference to FIG. 1, which is a schematic view of a device for supplying respiratory gas according to the invention.
  • The device 1 for supplying respiratory gas or ventilation device according to FIG. 1, comprises a generator 2 of gaseous flow provided with a turbine 2 a of low inertia and high rated speed. This gaseous flow generator is disposed in a chamber 20, preceded by a filter 21 for ambient air inlet, by an upstream and downstream sound deadening means 22 and 23. The turbine 2a is for example a turbine with a maximum speed of rotation of the order of 50,000 rpm, adapted to supply a pressure of 70 millibar above ambient and a flow rate of the order of 200 l/min.
  • The air flow generator, thus comprises a micro-turbine with low inertia, driven by an electric motor, controlled by a computer or a computer means 9 so as to provide a wide range of flow rates and pressures.
  • At the outlet of the chamber 20, the generator is connected to a first circuit 3 called a circuit for supplying gaseous flow toward a respiratory mask 4 or a intubation device (not shown) of the patient.
  • The generator is controlled by control means 10 in the form of an electronic control card connected to a supply 24 and to computer means 9 in the form of an electronic card with a microprocessor provided with control software and connected to a control interface 25 with a screen and a keyboard.
  • So as to control the operation of the device and to cause it to operate, the computer means are connected to means 5, 6, 7, 8 for measuring the pressure and/or for measuring the flow rate of the gaseous flow in the form of sensors.
  • The sensor 6 is a pressure sensor connected to a first circuit 3 which is a circuit for supplying gas to the mask 4 or intubation device of the patient.
  • According to the example, a sensor 6 is disposed in the apparatus 1 and connected to the mask 4 or to the intubation device via a tube 6 a.
  • The sensor 5 is a pressure sensor connected to a second circuit 16 comprising a proportional electro-valve 15 whose operation will be described later.
  • The sensor 7 is an inspiration flow rate sensor disposed in the first circuit, in a laminator 26 controlling the flow of gas leaving the generator.
  • An expiration flow rate sensor 8, in the third circuit 11 called patient return circuit, completes the measurement means.
  • The computation means 9 controls the members such as the generator and the proportional electro-valve 15 as a function of standards entered into the interface 25 as a function of the ventilation programs and as a function of the pressure and/or flow rate parameters from the sensors.
  • According to the invention, the measuring means 5, 6, 7, 8, the computing means 9 and the speed control means 10 coact in the first instance automatically to control the speed of rotation of the turbine 2 a as a function of the inspiration and expiration phases and as a function of the patient pressure signals and/or inspiration flow rate signals.
  • So as to regulate the output flow of the generator, the device according to FIG. 1 comprises a passive member 12 for generating a pressure drop in the supply circuit in the form of a non-return flap 12 mounted in the first circuit 3. Thanks to this member, the pressure on the generator side is always slightly greater than the pressure in the circuit 3 on the mask supply side or intubation device, which permits among other things a better regulation of the operation of the device.
  • Downstream of this non-return valve 12, the circuit 3 comprises a passive flap 13 for the admission of external air. This flap permits limiting the inspiration force of the patient by spontaneous respiration through the machine when the latter is not in operation.
  • On the mask side 4 or the intubation device after the circuit 3 for supplying gas, is located a third circuit 11 called an expiration circuit. This expiration circuit comprises an expiration valve 14 with a membrane permitting opening a passage either directly to the exterior or through tubing 11a toward a laminator 27 and an air outlet 28.
  • To the valve 14 is connected the second circuit 16 provided with proportional electro-valve 15 of the three-way type. This electro-valve 15 receives along a first path a pressure outlet of the generator, comprises a second path to vacuum and is connected by a third path to the valve 14.
  • The electro-valve permits controlling the valve 14 by applying a counter-pressure which closes the valve or limits its opening such that the expiration pressure will remain higher than the pressure of the second circuit 16. To release the valve 14, the electro-valve is controlled such that the pressure of the generator will be blocked, the second path of the free air being placed in communication with the third path.
  • Thus a controlled expiration device is constructed about the expiration valve 14 controlled by the electro-valve valve 15 connected to the flow generator, this electro-valve valve 15 permitting sending a portion of the generated flow to the expiration valve so as to oppose its opening.
  • The proportional electro-valve 15 is controlled by control means coupled to the computation means 9 and according to the example disposed on the card receiving the computing means 9.
  • This device thus permits in operation, the control of the speed of the turbine 2 a and the control of the expiration valve through the electro-valve to provide several modes of operation and particularly modes of volumetric operation. Thus several modes of operation are sought and particularly modes of operation with inspiration and expiration pressure standards or modes for which a volume of air called a target volume is predetermined, or mixed modes.
  • The operation of the apparatus is based on a system of self-adaptive control in a closed loop, of the speed of the flow generator. With this flow generator is associated a controlled expiration device, without a member for regulation of the supplemental principal flow.
  • In particular, the detection of an increasing slope of pressure can be translated by a level of acceleration of the turbine 2 a and the detection of the transition between the inspiration phase and the expiration phase can be translated by a deceleration of the turbine 2 a.
  • This control is effected by inspiration pressure or flow rate signals and according to control laws, based on proportional and integral coefficients, which differ according to the modes of ventilation, the adjustments of the pressure or flow rate and in particular the phases of the respiratory cycle.
  • The operation of the device and the associated ventilation process will be explained for example in the case of a mode in which an inspiration pressure Pi, an expiration pressure Pe as well as a form of obtaining the inspiration pressure based on the time of pressure increase, are fixed. The time of insufflation is here dependent on a level of triggering the expiration adjusted on the basis of the measurement of a drop in flow rate measured in the inspiration detector 7, after obtaining a maximum insufflation flow rate available for the patient.
  • A limiting parameter for the time of insufflation is the minimum threshold corresponding to the slope of pressure measured; another parameter is a maximum threshold of safety for the insufflation time which corresponds to the last inspiration time carried out or at most to three seconds. Other safety parameters can be taken into account such as a safety frequency.
  • According to this embodiment, the objective of the insufflation phase is the establishment of a pressure level Pi with a variable time of increase and a holding time depending on the behavior of the associated flow rate.
  • The objective of the expiration phase is to maintain a pressure level Pe up to the beginning of the following inspiration phase, but also sufficiently to rinse the circuit so as to evacuate the residual expired gases.
  • To carry out inspiration cycles, the phases of pressure increase with increased slopes of pressure are carried out by an acceleration of the turbine 2 a. The pressure is controlled in the inspiration pressure sensor 6.
  • During the insufflation phase corresponding to the inspiration phase, the computation means control the expiration valve 14, which is part of the third circuit 11 connected to the mask 4 or to the intubation device, via the proportional electro-valve 15 and the second circuit 16, according to pressure.
  • The transition between an inspiration phase and an expiration phase is effected itself by a controlled deceleration of the turbine 2 a and the expiration valve 14, which is part of the third circuit 11 connected to the mask 4 or to the intubation device, is controlled, through the proportional electro-valve 15 and the second circuit 16, with a pressure regulation member of the first circuit 3.
  • During the expiration phase, the computation means and the means for controlling the speed of rotation of the generator adapt the speed of the turbine 2 as a function of an expiration pressure threshold beyond a loss regulated by the expiration valve 14 so as to create the rinsing flow rate of the first circuit.
  • The non-return clapet system 12 and the spontaneous respiration clapet 13 permit balancing the rinsing pressure which is maintained sufficiently low to limit the phenomenon of expiration braking without being canceled to avoid all heating of the turbine 2 a.
  • In the case of ventilation for which a current volume as well as a frequency and a cycling ratio are fixed, the objective of the insufflation phase is the distribution of a current volume Vt with a suitable flow rate shape and during a time fixed by the frequency levels and the ratio of cycling regulated by the interface 25.
  • In this case, during insufflation, the patient current comprising the circuit 3, the mask 4 or intubation device is maintained sealed, against parasitic loss by the closing of the valve 14 controlled by the electro-valve 15. As a result, there is an increase in pressure of the circuit 3 and of the pulmonary system of the patient depending on the characteristics of the patient. In the case of exceeding the objective of maximum pressure measured with the pressure sensor 6, it is possible to cause the pressure in the control circuit 16 of the valve 14 by a command of the electro-valve 15 and to pass immediately into the expiration phase.
  • In the case of a target volume mode, the operator enters by the interface means a target volume standard into the computation means 9 which, as a function of this parameter and other parameters entered by the interface such as the frequency of minimum cycle and/or safety, cycling ratio, high pressure threshold, will permanently adjust the insufflation pressure between a low pressure threshold and a maximum pressure threshold so as to maintain the current volume inhaled by the patient as nearly as possible to a predefined target volume, namely for example between target volume Vt and target volume Vt+20%.
  • According to the target volume mode, it is particularly necessary to be able at the same time to adjust precisely the pressure by pressure steps between the cycles. For example, for a pressure standard of the order of 20 millibars, the steps between cycles are defined between 0.5 millibar and 2 millibars so as to react immediately to the detection of an unbalance without having a strong reaction that would be uncomfortable to the patient.
  • This pressure adjustment is made according to the invention without a regulator device such as the generator but by controlling the speed of the turbine 2 a of the generator 2 as a function of the pressure measurements of the sensor 6 of the pressure of the patient and by causing to operate the expiration circuit comprising the expiration valve 14 following through the proportional electro-valve 15 in which, in this configuration, the flow generator is connected to the second circuit, the non-return flap 12 of the first circuit 3 permitting preserving a pressure slightly greater in the second circuit relative to the first circuit.
  • Thus the device permits providing a respiratory gas according to respiratory cycles comprising phases of inspiration and expiration, the measuring means 5, 6, 7, 8 and the computation means 9 acting on the speed control means 10 so as automatically to control the speed of rotation of the turbine 2 as a function of the pressure and/or volume standards, of the detection of inspiration and expiration phases, of patient pressure signals and/or inspiration flow rate signals.
  • With the device of the invention, the expiration valve 14 is controlled by the pressure during the inspiration phase and by a regulating member during the expiration phase.
  • The device according to the invention thus permits ventilating a patient by pressure or volume with a patient circuit provided with an expiration device controlled by a simple control of the speed of the turbine.

Claims (20)

1. Device (1) for supplying respiratory gas to a patient according to respiratory cycles, comprising a gas flow generator (2) provided with a turbine (2 a) with low inertia and high nominal speed, a first circuit (3) called a circuit for supplying a gaseous flow to a respiratory mask (4) or to an intubation means of the patient, means (5, 6, 7, 8) for measuring the pressure and/or flow rate of the gaseous flow, means (9) for computing parameters of pressure and/or flow rates and means (10) for controlling speed of rotation of the generator, characterized in that the measuring means (5, 6, 7, 8), the computation means (9) and the means (10) for controlling the speed coact automatically to control the speed of rotation of the turbine (2 a) as a function of the inspiration and expiration phases and as a function of the patient pressure signals and/or inspiration flow rate signals.
2. Device according to claim 1, characterized in that the pressure measuring means comprise a sensor (6) of patient pressure and/or a sensor (7) of expiration valve pressure.
3. Device according to claim 1, characterized din that the flow rate measuring means comprise a sensor (7) of inspiration flow rate disposed adjacent the outlet of the generator (2).
4. Device according to claim 1, characterized in that it comprises a passive member (12) for generation of a pressure drop in the supply circuit.
5. Device according to claim 4, characterized in that this passive member (12) is a non-return flap if desired associated with a passive flap (13) for the addition of external air downstream of the non-return flap in the supply circuit (3).
6. Device according to claim 1, characterized in that it comprises a second circuit (16) comprising a proportional electro-valve (15), for controlling an expiration valve (14) that is part of a third circuit (11) by application of a counter-pressure to this valve (14), control means of said proportional electro-valve (15) being coupled to the computation means (9).
7. Device according to claim 1, characterized in that the means for measuring flow rate comprise an expiration flow rate sensor (8) in the third circuit (11) so-called patient return circuit.
8. Process for supplying a respiratory gas according to respiratory cycles, comprising inspiration and expiration phases, by means of a device according to claim 1, characterized in that the measuring means (5, 6, 7, 8) and the computation means (9) act on the speed control means (10) so as automatically to control the speed of rotation of the turbine (2 a) as a function of pressure and/or volume standards, of the detection of the inspiration and expiration phases, of patient pressure signals and/or inspiration flow rate signals, the supplying of the respiratory gas taking place as to pressure and/or as to volume.
9. Process according to claim 8, characterized in that it comprises phases of pressure increase with increase slopes of pressure produced by acceleration of the turbine (2 a).
10. Process according to claim 8, characterized in that the transition between an inspiration phase and an expiration phase is carried out by controlled deceleration of the turbine (2 a).
11. Process according to claim 8, characterized in that during expiration phases, an expiration valve (14) which is part of a third circuit (11) connected to the mask (4) or to the incubation device, is controlled, via a proportional electro-valve (15) and a second circuit (16), by a regulation member of the pressure in the first circuit (3).
12. Process according to claim 11, characterized in that the computation means and the control means of the speed of rotation of the generator adapt the speed of the turbine (2 a) as a function of a threshold of this expiration pressure beyond a regulated loss, by the expiration valve (14), so as to create a rinsing flow rate in the first circuit.
13. Process according to claim 8, characterized in that during phases of insufflation corresponding to the inspiration phases, an expiration valve (14), which is part of a third circuit (11) connected to the mask (4) or to the intubation device, is controlled via a proportional electro-valve (15) and by a second circuit (16), according to pressure.
14. Process according to claim 8, characterized in that it comprises a measurement of expiration flow rate and a measurement of inspiration flow rate.
15. Device (1) for providing a respiratory gas to a patient according to respiratory cycles, comprising a gas flow generator (2) provided with a turbine (2 a) for flow inertia and high nominal speed, a first circuit (3) called a circuit for supplying gaseous flow toward a respiratory mask (4) or an intubation means of the patient, means (5, 6, 7, 8) for measuring pressure and/or of flow rate of the gaseous flow, computation means (9) of parameters of pressure and/or flow rate, and means (10) for controlling the speed of rotation of the generator, characterized in that the measuring means (5, 6, 7, 8), the computation means (9) and the speed control means (10) coact automatically to control the speed of rotation of the turbine (2 a) as a function of the inspiration and expiration phases and as a function of the patient pressure signals and/or inspiration flow rate signals, and in that the control system of the generator carries out phases of pressure increase with increasing slopes of pressure by means of acceleration of the turbine (2 a), the supply of respiratory gas taking place according to pressure or according to volume.
16. Device according to claim 15, characterized in that the control system of the generator carries out the transition between an inspiration phase and an expiration phase by means of controlled deceleration of the turbine (2 a).
17. Device according to claim 15, characterized in that the control system of the generator comprises means permanently adjusting the insufflation pressure between a low pressure threshold and a maximum pressure threshold so as to maintain the inspiration current volume as near as possible to a predetermined target volume.
18. Device according to claim 15, characterized in that it comprises a proportional electro-valve (15), a second circuit (16) and an expiration valve (14), the proportional electro-valve (15) and the second circuit (16) being arranged to control the expiration valve (14) with a pressure regulating member of the first circuit (3) during expiration phases.
19. Device according to claim 15, characterized in that computation means and the means for controlling the speed of rotation of the generator are arranged to adapt the speed of the turbine (2 a) as a function of an expiration pressure threshold beyond a loss regulated by an expiration valve (14) so as to create a rinsing flow rate in the first circuit during expiration phases.
20. Device according to claim 18, characterized in that the proportional electro-valve (15) and the second circuit (16) are arranged to control the expiration valve (14) according to pressure during insufflation phases corresponding to the inspiration phases.
US10/899,022 2003-07-29 2004-07-27 Device and process for supplying respiratory gas under pressure or volumetrically Abandoned US20050039748A1 (en)

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US12/752,501 US8800557B2 (en) 2003-07-29 2010-04-01 System and process for supplying respiratory gas under pressure or volumetrically

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FR0309347A FR2858236B1 (en) 2003-07-29 2003-07-29 DEVICE AND METHOD FOR SUPPLYING RESPIRATORY GAS IN PRESSURE OR VOLUME

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US20080011300A1 (en) 2008-01-17
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US8800557B2 (en) 2014-08-12
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FR2858236A1 (en) 2005-02-04
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ATE390161T1 (en) 2008-04-15
ES2301937T3 (en) 2008-07-01
US20100186744A1 (en) 2010-07-29

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