WO2001019440A1 - Patient-ventilator synchronization using dual phase sensors - Google Patents
Patient-ventilator synchronization using dual phase sensors Download PDFInfo
- Publication number
- WO2001019440A1 WO2001019440A1 PCT/AU2000/001123 AU0001123W WO0119440A1 WO 2001019440 A1 WO2001019440 A1 WO 2001019440A1 AU 0001123 W AU0001123 W AU 0001123W WO 0119440 A1 WO0119440 A1 WO 0119440A1
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- WO
- WIPO (PCT)
- Prior art keywords
- phase
- respiratory
- effort
- airflow
- signal
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Classifications
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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
-
- 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
- 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
- A61M16/0057—Pumps therefor
- A61M16/0066—Blowers or centrifugal pumps
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—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
- A61M2016/0036—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
- A61M2230/00—Measuring parameters of the user
- A61M2230/60—Muscle strain, i.e. measured on the user
Definitions
- This invention relates to a method and device for providing ventilatory assistance to a patient More specifically, the invention involves an improved method and device that provides ventilation in phase with a patient's respiratory efforts through the use of a respiratory effort sensor
- a ventilator provides air or oxygen-enriched air to a patient at pressures that are higher during inspiration and lower during expiration
- Bi-levei ventilators provide the simplest level of support These ventilators supply a mask pressure P(t) which is higher by an amplitude A from an initial pressure P 0 when respiratory airflow f(t) is inspiratory, f(t) > 0, than when respiratory airflow is expiratory, f(t) ⁇ 0
- Proportional assist ventilators represent an attempt to provide support more closely in phase with the patient s respiratory efforts
- Proportional assist ventilators provide mask pressure as follows
- One method of ensuring an adequate degree of ventilatory support is to use a servo ventilator, which adjusts the degree of support A to servo-control instantaneous ventilation V(t) to equal a target ventilation V TGT :
- V(t) 0.5 abs ( f(t) ) A MiN ⁇ A ⁇ A MAX .
- V(t) is one half the absolute value of the respiratory airflow
- G is the gain of the integral servo-controller
- a value of 0.3 cmH 2 0 per L/min error in ventilation per second being suitable
- a M , N and A MAX are limits set on the degree of support A for comfort and safety, 0.0 and 20.0 cmH 2 0 being generally suitable.
- AutoVPAP International Publication Number WO 98/12965
- the AutoVPAP apparatus provides an instantaneous mask pressure P(t) based upon a substantial fraction of the patient's airway resistance R, respiratory airflow f(t), an amplitude A,
- the AutoVPAP apparatus uses a respiratory airflow signal and its derivative as input data for a set of fuzzy logic rules that are associated with particular phases of respiration Using the results of the evaluations of the rules, a single phase value is derived and used as the instantaneous respiratory phase Thus, the degree of ventilatory support is varied in phase with the patient's respiration Moreover, as the calculation of A is based upon a target ventilation V TGT , a guaranteed level of ventilation is provided
- An objective of the present invention is to provide a method and apparatus to supply ventilatory assistance precisely in phase with a patient's spontaneous ventilatory efforts provided these efforts are adequate to maintain a specified target ventilation
- a further objective of the present invention is to provide a method and apparatus to guarantee at least a specified target ventilation, even in the event that the patient s efforts become irregular or cease
- the present invention involves an improved ventilator which delivers ventilatory support that is synchronized with the phase of a patient s respiratory efforts and guarantees a targeted minimum ventilation
- the device provides ventilatory support to a patient based in part upon a calculated instantaneous mask pressure using a general
- Substitute Sheet method similar to that of the previously described AutoVPAP system.
- the respiratory phase determination is improved by using data representing both respiratory airflow and respiratory effort.
- the device utilizes a respiratory airflow signal and preferably its rate of change.
- the degree of membership of the respiratory airflow signal in each of the fuzzy sets zero, positive, large positive, negative, and large negative is calculated using suitable membership functions.
- the degree of membership of the derivative of the respiratory airflow signal in each of the fuzzy sets steady, increasing, increasing fast, decreasing and decreasing fast is calculated using suitable membership functions.
- the degrees of membership in these classes are used in a set of fuzzy logic inference rules. Each fuzzy inference rule is associated with a particular phase of respiration.
- the inference rules relating to respiratory airflow are as follows:
- the device combines additional fuzzy inference rules based upon an effort signal from an effort sensor.
- the effort sensor is not dependent on measured
- Substitute Sheet airflow and as such is immune to errors associated with leak
- the effort signal and preferably its rate of change are used as input values for membership functions for the additional fuzzy inference rules that are also associated with particular phases
- the membership functions are used to calculate the degree of membership of the effort signal in each of the fuzzy sets zero, medium and large, and the degree of membership of its derivative in each of the fuzzy sets increasing moderately, increasing fast, decreasing moderately and decreasing fast
- the inference rules relating to respiratory effort are as follows
- phase values need not be these exact values, but can approximate them
- the effort sensor is a suprasternal notch sensor
- alternative embodiments of the invention may utilize other effort sensors including, for example, an esophageal pressure sensor or an electromyograph
- Fig 1 depicts the components of a servo-controlled ventilator with an effort sensor
- Fig 2 depicts the steps involved in determining the delivered pressure level, including use of the effort signal
- a servo-controlled ventilator useful for accomplishing the present invention is shown in Fig 1
- a blower 10 supplies air under pressure via delivery tube 12 to a mask 1 1
- Exhaust gas is vented via exhaust 13
- Mask flow is measured using pneumotachograph 14 and differential pressure transducer 15 to derive flow signal f(t)
- Mask pressure is measured at pressure tap 17 using pressure transducer 18
- Respiratory effort is measured by an effort sensor 22 to yield an effort signal E ss (t)
- Flow, effort and pressure signals are sent to microcontroller 16 which implements the processing shown in Fig 2 to derive a pressure request signal P(t)
- the actual measured pressure and pressure request signal P(t) are fed to motor servo 19 which controls blower motor 20 to produce the desired instantaneous mask pressure
- An example of this type of ventilator, without an effort sensor 22, is the subject of International Publication No WO 98/12965, which is also disclosed in related U S Application Serial No 08/935,785
- An additional example is
- a suprasternal notch sensor is used as the effort sensor 22 to generate the effort signal
- the sensor is more fully described in a commonly owned patent application entitled “Measurement of Respiratory Effort Using a Suprasternal Sensor," Application Serial No 09/396,031 filed on September 15, 1999
- the suprasternal notch sensor measures changes in the suprasternal notch Increasing inspiratory efforts cause the skin of the suprasternal notch to retract
- An optical sensor generates an electrical signal that is an increasing function of inspiratory effort derived by measuring changes in the depth of the skin of the suprasternal notch
- the effort signal is used to trigger a bilevel ventilator
- step 34 the system calculates the phase ⁇ in the respiratory cycle as a continuous variable using a set of fuzzy inference rules
- the fuzzy inference rules are based upon both respiratory airflow and respiratory effort
- Substitute Sheet ule 26 RO/AU The preferred rules with respect to respiratory airflow are those described above, rules 1-9, although many other inference rules can be developed based upon respiratory airflow.
- the fuzzy extents, or the degrees of truth, to which the airflow is in fuzzy sets zero, positive, large positive, negative, and large negative, and the 5-second low-pass filtered absolute value is small and large, are determined with suitable membership functions using the measured respiratory airflow f(t).
- the fuzzy extents to which the airflow is in fuzzy sets steady, increasing fast and decreasing fast are determined with suitable membership functions using the change in respiratory airflow df(t)/dt.
- the fuzzy extents to which the phase is a member of the fuzzy sets expiratory and inspiratory is determined by membership functions using a previously calculated instantaneous phase. This approach using respiratory airflow to determine phase is that disclosed in International Publication Nos. WO 98/12965 and WO 99/61088.
- Rules 1-4 estimate the phase directly from the instantaneous respiratory airflow.
- Rule 5 permits an expiratory pause, whose length may be long if the patient has recently been breathing adequately, and short or zero if the patient is not breathing.
- Rules 6-7 provide for quick resynchronization in the event that the patient breathes irregularly.
- Rule 8 provides the equivalent of a timed backup, in which, to the extent that the patient has stopped breathing or is not adequately breathing, the ventilator will cycle at a suitable fixed rate.
- Rule 9 provides that to the extent that the patient is breathing adequately, the ventilator will tend to track the patient's recent average respiratory rate. This is particularly appropriate for patients with cardiac failure and Cheyne-Stokes breathing, whose respiratory rates tend to be extremely steady despite rhythmic changes in amplitude.
- An effect of the changing degree of activation of rules 8 and 9 is that, to the fuzzy extent that the instantaneous ventilation equals or exceeds the target ventilation, ventilatory support will be provided in phase with the patient's own respiratory efforts, and to the extent that the instantaneous ventilation is less than the target ventilation, ventilatory support will be provided at a pre-set rate.
- the weighting of rules 1 -6 can be made proportional to the fuzzy extent that the instantaneous ventilation is large compared with the target ventilation, thereby reinforcing the behavior described in the previous paragraph.
- weighting of rules 1-6 and also of rule 9 can be made smaller and the weighting of rule 8 can be made larger, if the leak is large or if there is a sudden
- ventilatory support will be provided as described in the preceding paragraphs, but to the extent that the respiratory airflow signal is of poor quality and it is difficult to synchronize reliably with the patient's efforts, or to know if the patient's efforts are adequate, ventilatory support will be provided in an orderly manner at a predetermined fixed rate.
- the Fuzzy Phase Calculation of step 34 also involves fuzzy inference rules relating to respiratory effort.
- the invention takes the effort signal E ss (t) from the effort sensor 22 and processes additional fuzzy inference rules.
- the maximum activation will be at a phase shortly after the actual moment of start of inspiration, say 0.05 revolutions, and this is the best phase to associate with the rule.
- the more features that are identified and assigned a rule and a phase, the smoother will be the resultant determination of phase.
- the illustrative additional fuzzy inference rules relating to the effort signal E ss (t) from the suprasternal effort sensor and the rate of change in the signal, dE ss (t)/dt, are rules 10- 13 provided above.
- the fuzzy extents to which the effort signal is in fuzzy sets zero, medium and large are calculated with appropriate membership functions using E ss (t).
- the fuzzy extents to which the effort signal is in fuzzy sets increasing moderately, increasing fast, decreasing moderately or decreasing fast are determined with appropriate membership functions using the rate of change of the effort signal, dE ss (t)/dt.
- the effort signal is normalized for amplitude prior to calculation of degrees of membership, for example, by dividing by the amplitude of the effort signal calculated over a long period compared with a breath, for example, 10-30 seconds.
- each of the rules in the combined set of fuzzy inference rules is evaluated to determine a degree of activation G(n) by using a standard fuzzy inference method
- a standard fuzzy inference method For example, with respect to rule 12, using one such method assuming a unit weighting of rules, if (a) the degree of truth for the membership function "the effort signal is large” evaluates to 0 6 and (b) the degree of truth for the membership function "the effort signal is decreasing fast" evaluates to 0 4, and a fuzzy logic "AND" operator is applied, then the degree of activation for G(12) would be 0 4
- each of the 13 fuzzy inference rules associates a particular rule with a particular phase ⁇ (n)
- a single value representing the instantaneous respiratory phase ⁇ is calculated in a defuzzification step using the formula
- phase ⁇ is then used in step 36 of Fig 2 to derive a value from the smooth pressure waveform template ⁇ ( ⁇ )
- Step 38 labeled "Amplitude Calculation,” involves a calculation of an instantaneous amplitude of pressure support A, chosen to servo-control instantaneous ventilation to, on average, equal a target V TGT , by the following formula
- the system calculates the desired degree of ventilatory support P(t) from the calculated amplitude A a substantial fraction of the patient's airway resistance R, respiratory airflow f(t), and the smooth pressure waveform template ⁇ ( ⁇ )
- the effort sensor is an accessory that can be added or removed at will from a ventilator such as an AutoVPAP system in order to achieve improved synchronization with the patient. If the effort sensor falls off the patient, fails, is electrically unplugged or is otherwise removed, then rules (10) to (13) will have no effect on the phase determination or, in other words, the rules will have no degree of activation. In this event, the device will behave as a simple servo-controlled ventilator such as the AutoVPAP device. The patient will continue to be ventilated, with ventilatory support provided approximately in phase with respiratory airflow and therefore approximately in phase with respiratory effort. Thus, the degree of support will be sufficient to guarantee that instantaneous ventilation on average equals or exceeds the target ventilation, but the precise timing information and improved immunity to the effects of leaks will be lost.
- a ventilator such as an AutoVPAP system in order to achieve improved synchronization with the patient.
- effort signals from other sensors may also be utilized.
- Other forms of effort signal include, for example, an effort signal derived from esophageal pressure generated by a pressure transducer implanted in the chest that sends a signal via telemetry.
- an electromyogram signal from an electromyograph could be used without requiring any modification to the invention.
- multiple effort sensors can be utilized simply with the addition of extra fuzzy inference rules relating to the additional effort sensors.
- one embodiment of the invention might utilize a set of rules to determine phase in which some of the rules determine phase based solely upon the magnitude of the respiratory airflow and the rate of change of an effort signal. Alternatively, some rules may determine phase based upon the magnitude of the effort signal and the rate of change of respiratory airflow. Numerous modifications, in addition to the illustrative embodiments of the invention discussed herein may be made and other arrangements may be devised without departing from the spirit and scope of the invention.
Abstract
Description
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Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AU74997/00A AU778469B2 (en) | 1999-09-15 | 2000-09-15 | Patient-ventilator synchronization using dual phase sensors |
JP2001523067A JP4667693B2 (en) | 1999-09-15 | 2000-09-15 | Synchronizing patient and ventilator using two phase sensors |
EP00963813A EP1229956B1 (en) | 1999-09-15 | 2000-09-15 | Patient-ventilator synchronization using dual phase sensors |
DE60032929T DE60032929T2 (en) | 1999-09-15 | 2000-09-15 | SYNCHRONIZING A VENTILATION DEVICE THROUGH DOUBLE PHASE SENSORS |
AU2004229074A AU2004229074B2 (en) | 1999-09-15 | 2004-11-12 | Patient-Ventilator Synchronization Using Dual Phase Sensors |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US15419699P | 1999-09-15 | 1999-09-15 | |
US60/154,196 | 1999-09-15 |
Publications (1)
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WO2001019440A1 true WO2001019440A1 (en) | 2001-03-22 |
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Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
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PCT/AU2000/001123 WO2001019440A1 (en) | 1999-09-15 | 2000-09-15 | Patient-ventilator synchronization using dual phase sensors |
Country Status (6)
Country | Link |
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US (1) | US7934499B2 (en) |
EP (1) | EP1229956B1 (en) |
JP (2) | JP4667693B2 (en) |
AU (2) | AU778469B2 (en) |
DE (2) | DE60043362D1 (en) |
WO (1) | WO2001019440A1 (en) |
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Also Published As
Publication number | Publication date |
---|---|
DE60032929T2 (en) | 2007-10-25 |
EP1229956A1 (en) | 2002-08-14 |
EP1229956A4 (en) | 2004-12-15 |
US20060102180A1 (en) | 2006-05-18 |
AU2004229074A1 (en) | 2004-12-09 |
EP1229956B1 (en) | 2007-01-10 |
AU2004229074B2 (en) | 2008-09-04 |
JP2010246952A (en) | 2010-11-04 |
AU7499700A (en) | 2001-04-17 |
JP4667693B2 (en) | 2011-04-13 |
DE60043362D1 (en) | 2009-12-31 |
JP2003509134A (en) | 2003-03-11 |
AU778469B2 (en) | 2004-12-09 |
DE60032929D1 (en) | 2007-02-22 |
US7934499B2 (en) | 2011-05-03 |
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