VARIABLE FREQUENCY JET VENTILATION SYSTEM

Abstract: Respiration therapy apparatus includes a valve (22) for generating pulses of inhalation gas for delivery to a patient. A chamber (52) permits inhalation gas pulses to be generated by entraining humidified low pressure gas with the pulses of high pressure entrainment gas. Control means (12) are provided so that the pulses of entrainment gas may be of variable frequency, duration and duty cycle by modulating the flow of a highly pressured gas with a solenoid operating the valve (22).

Description: The invention relates to high frequency jet ventilators for supplying gas to facilitate and support human respiration. Background Art Patent Specification EP-A-149722 (=US-A-4617924) describes apparatus for artificial respiration. Breathing gas is supplied to the mouth of a patient through a nozzle in a gas supply device. Flush gas is fed to one side of the supply device, and a CO₂-analyzer and a flow meter are connected in an outlet line to the opposite side of the supply device. A high frequency controller interrupts the supply of breathing gas and a flush gas for a measuring interval in which exhaled gas is directed through the analyzer. The use of high frequency jet ventilation has proven to be beneficial in the treatment of certain respiratory conditions. In high frequency ventilation, rather than moving gas in bulk into the gas exchanging areas of the lungs, ventilation is achieved by enhancing the mass transfer processes in the lungs through high frequency oscillation of the supplied gas. The Invention In a ventilator according to the invention as defined by claim 1, a nozzle introduces high velocity gas pulses into an entrainment module along a chamber towards an outlet for connection to the mouth of a patient. This makes it possible to supply the necessary tidal volume of breathing gas in conjunction with high pulsation frequency having regard to the response times of mechanism employed for generating the gas pulses. Reliability, ease of maintenance, susceptibility to sterilization, and portability are further possible characteristics of the ventilator. Ventilation at supraphysiologic rates may be enhanced, and patient discomfort and the possibility of causing or aggravating trauma reduced. The breathing gas will be at relatively low pressure, customarily humidified, supplied continuously to an inlet port from a first gas source to establish a bias flow. The nozzle may extend into the entrainment chamber in a direction which is generally axially aligned with a gas outlet. The nozzle is in fluid communication with a source of relatively highly pressurized gas pulses, and serves to inject a series of high velocity pressurized gas pulses into the entrainment chamber for traversal thereof in a generally axial direction toward the patient. The breathing gas inlet and vent port are generally arranged coaxially across the entrainment chamber. One high pressure pulse is generally injected during the inspirator phase of each cycle of the ventilator. A high velocity pulse from the nozzle entrains a relatively large amount of the low pressure gas from the bias flow in the entrainment chamber to produce an inhalation pulse. During each expiratory phase, between the injection of successive pulses from the nozzle, gases in the entrainment chamber, including CO₂ exhaled by the patient which flows into the chamber via the supply outlet, are discharged through the vent port. The interior shape of the pulse injection nozzle is either convergent or convergent-divergent to increase the quantity of gas from the bias flow which is entrained. A conduit couples the source of high pressure ventilation gas to the nozzle. A valve is interposed in this conduit to selectively interrupt the flow of pressurized gas to generate the high pressure gas pulses. The valve is actuated by a solenoid which drives the valve from a closed to a fully open position. An electronic control circuit provides signals which control the operation of the solenoid. These command signals have a frequency, pulse width and duty cycle which may be selected to provide the optimum ventilation program for the patient to be treated. The command signals have a generally stepped waveform which includes an initial overdrive voltage of predetermined duration. The overdrive voltage functions to reduce the time interval for the solenoid to change the state of the valve whereby the time required for the valve to switch from the fully closed to the fully open condition is minimized. The entrainment consists of subjecting the bias flow to the effect of high velocity pulses of gas derived from a high pressure source of entrainment gas. Control can be exercised over the entrainment gas to vary the frequency, duration and width of the gas pulses to satisfy the requirements of the treatment being performed. Means for periodically interrupting the primary gas flow can be provided in the form at a normally closed solenoid actuated valve. Solenoid control voltage pulses can be generated having first and second voltage magnitude levels (V₁,V₃). These voltage levels may have an initial magnitude in excess of the rated voltage of the solenoid, and a second contiguous magnitude less than the said rated voltage and sufficient to hold the solenoid in the actuated state. The voltage pulses are applied to the valve solenoid to cause the generation of gas pulses. The frequency or the duty cycle of the pulses can be varied as a function of the required therapy. The width of the pulses can also be varied as a function of the required therapy. DRAWINGS Figure 1 is a functional block diagram of a multi-frequency jet ventilator in accordance with the invention; Figure 2 is an enlarged fragmentary sectional view of a preferred embodiment of an entrainment module of the multi-frequency jet ventilator of Figure 1; Figure 3 is a functional block diagram, of the control module of the multi-frequency jet ventilator of Figure 1; Figures 4a, 4b and 4c are graphical illustrations of gas pulse trains provided to the entrainment module of Figure 2 in response to the control signals generated by the control module of Figure 3; and Figure 5 is a waveform diagram of a control voltage generated by the control module of Figure 3. Best Mode With reference to the drawings, wherein like numerals represent like parts throughout the several figures, a ventilator 10 (Figure 1) may be selectively employed at conventional ventilation frequencies or may be utilized as a high frequency jet ventilator. The ventilator 10 preferably has a range of operational frequencies of from 4 breaths/minute (1/15 Hz) to 3000 breaths/minute (50 Hz) and an inspiratory time, i.e. , a duty cycle, in the range of 5% to 95% as will be more fully described below. The ventilator 10 will supply respiratory gas to a patient via either a cuffed or uncuffed endotracheal tube (not illustrated) and is adaptable for ventilating with air, air/oxygen, helium/oxygen or other suitable gas or combination of gases. The ventilator 10 has a compact, lightweight construction and may be either battery or line current powered. The ventilator 10 is an integrated modular system which generally comprises a control unit 12, a high pressure gas supply unit 14, a low pressure gas supply unit 15 and an entrainment module 16. The control unit 12 comprises the electronic ontrols, safety system and the electrical power supply for the ventilator. The high pressure gas supply unit 14 comprises a source of high pressure gas, a gas pressure regulation system and a valve subassembly for producing controlled pulses of the gas derived from the high pressure source. The low pressure gas supply unit 15 comprises a source of low pressure gas and a humidification system for the gas. The entrainment module 16 produces, from the pulses of high pressure gas and the humidified low pressure gas, the required output of the ventilator. The gas flow lines are designated by heavy lines and the electrical interconnections are designated by thin lines in Figure 1. The control unit 12 is connected to the supply unit 14 via conventional separable electrical connectors. The gas supply units 14 and 15 and entrainment module 16 are interconnected by standard flexible hoses. The above-mentioned modular units and their sub-units may be easily connected and disconnected. The modular construction thus facilitates maintenance of the ventilator and also provides a ventilator which, to the extent required, may be easily disinfected and sterilized as will be more fully apparent from the discussion below. With reference to Figure 1, the control unit 12 comprises an electronic control module 20 which generates control pulses for operating a solenoid actuated valve 22 in supply unit 14. The control module 20 also provides input signals to an electronic safety module 24. The safety module 24, in the manner to be described below, controls an electrically operated shutoff valve 26 in the primary, i.e., high pressure gas supply line and is also connected to an alarm system 28. A source of pressurized gas 30, which is typically in the form of plural tanks containing compressed dry air, oxygen/nitrogen, or oxygen/helium, is coupled via the shutoff valve 26 and an adjustable pressure regulator 32 to an accumulator 34. The pressurized gas which appears at the output port of accumulator 34 has a regulated substantially constant pressure in the range of between 34485 Pascal and 1724250 Pascal (5 psi and 250 psi). The pressurized gas flows from the accumulator 34 via a flow sensor 36 and valve 22 to the entrainment module 16. The flow sensor 36 provides an information bearing input signal to the safety module 24 whereby the nature of the gas flow to the entrainment module 16 derived from the high pressure source 30 may be continuously monitored to provide a means for actuating the alarm 28 in the event that the aforementioned gas flow is not within the selected and required operational limits of the ventilator. The alarm 28 is preferably both an audible and a visual alarm. The safety module 24, which is preferably a microprocessor, is programmed to monitor the operation of the ventilator, especially the primary gas flow to the entrainment module and the pressure downstream of the entrainment module, in order to determine whether the operating parameters are within pre-established ranges. Should a monitored parameter move into a range which is unsafe to the patient, the module 24 will command the closing of shutoff valve 26. A secondary pressurized gas source 42, within the unit 15, is coupled via a shutoff valve 44 to a humidifier 46. The output of humidifier 46 is a bias flow of heated humidified gas which is continuously supplied to the entrainment module 40 at a relatively low pressure perhaps just above atmospheric or slightly more elevated such as 5 psi (34485 Pascal). The secondary gas source 42 is typically in the form of one or more tanks containing the same gas as supplied by the 'high' pressure source 30. The humidifier 46 may be a cascade bubble humidifier or preferably a vapour phase humidifier and causes the bias flow to have approximately 100% relative humidity. The pressure of the bias flow may vary depending on the degree of humidification and the type of humidification. In addition, an ultrasonic nebulizer 47 may be employed to introduce a vapour mist to the bias flow of humidified gas. The stream of humidified gas and vapour mist, which is flowing at low velocity, is entrained in module 16 by high velocity gas pulses, produced in the manner to be described below, to form an output gas stream. As noted above, the output stream is supplied to the patient via an endotracheal tube (not fully illustrated). The entrainment module 16 also functions to receive gases exhaled by the patient. Depending on the state of a two-way flow control valve 48, the exhaled gas is either vented to the ambient atmosphere or delivered to a reclamation unit 49. A pressure sensor 50 may be interposed in the gas path which extends from the entrainment module to the endotracheal tube for sensing the pressure immediately upstream of the endotracheal tube and providing a corresponding input signal to the safety module 24 for insuring safe operation of the ventilator. With reference particularly to Figure 2, the entrainment module 16 comprises a housing 51 which forms an entrainment chamber 52. The housing 51 is a generally T-shaped cylindrical member which has an open output end. A fitting 54 at the output end couples chamber 52 fluidically to a conduit 56 which leads to or comprises the end of the endotracheal tube. Gas pulses, produced by modulating the gas exiting accumulator 34 by means of the valve 22, are injected into the entrainment chamber 52 through a nozzle 58. Nozzle 58 is a convergent or convergent-divergent nozzle and thus the velocity of the gas downstream of the nozzle throat is high. Nozzle 58 extends axially into chamber 52 through an end wall of the housing 51 along the central axis of the chamber. Nozzle 58 is aerodynamically shaped to enhance entrainment by directing the low pressure bias flow in the downstream direction in chamber 52. Nozzle 58 thus preferably has a forwardly tapering convergent external profile 60. An inlet leg 62 and an outlet leg 64 protrude radially at diametrically opposite locations of the housing 51. The legs 62 and 64 are substantially identical and are equidistant from the centrally disposed nozzle 58. Inlet leg 62 functions as a connector structure for coupling to a conduit for supplying the low velocity bias stream of humidified gas to the entrainment chamber 52 via port 66 as illustrated by the arrows in Figure 2. The humidified gas is continuously supplied to the entrainment chamber. During an inspiratory phase of the ventilation cycle (i.e. inhaling), humidified gas is entrained by a high velocity gas pulse injected into chamber 52 via the nozzle 58 and propelled axially through the chamber to conduit 56 and hence to the patient via the endotracheal tube. The ventilating gas pulses delivered to the patient will be comprised primarily of humidified gas supplied via inlet leg 62, the humidified gas being entrained by the pulses of dry gas supplied via the nozzle 58. Accordingly, the patient will receive gas having the highest possible relative humidity. During the expiratory phase of the ventilation cycle, the gas exhaled by the patient returns via the conduit 56 to the entrainment chamber 52. The exhaled gas is entrained by the low velocity bias flow and is thus discharged through discharge port 68 which leads to outlet leg 64. Leg 64 is coupled to a conduit for conducting the exhaled gas and excess humidified gas to valve 48. The expired carbon dioxide from the patient is discharged through port 68 in part due to the driving force of the bias flow of humidified gas which prevents the exhaled gases from entering port 66. The entrainment of the humidified gas by the high velocity pulses or slugs of primary gas is facilitated by the convergent exterior shape of nozzle 58 which, as mentioned above, functions as a flow control surface. The entrainment of the humidified gas is improved by the placement of the outlet 60 of nozzle 58 at an axial location of the chamber which is proximate the downstream axial terminus of the inlet port 66. Consequently, the high velocity pulse is injected into the chamber at a location slightly downstream from the entry of the humidified gas. As should now be obvious, the continuous supply of the low pressure humidified secondary gas functions to alternately supply humidified gas for entrainment and to remove the expired carbon dioxide from the ventilator unit without the use of any mechanical valves which would otherwise tend to deteriorate the entrainment effects and, thus, would result in lower tidal volumes. A low compliant tube connects nozzle 58 to the solenoid actuated control valve 22. Valve 22 is a bi-state valve having an open and closed position. The valve may be of the normally closed type. The command signals generated by control module 20 and applied to the solenoid of valve 22 determine the frequency and duration of the gas pulses delievered to the nozzle 58. Thus, valve 22 is cyclically opened and closed for selected time intervals to interrupt the flow of pressurized gas to nozzle 58 to thereby produce the desired gas pulse train characteristics to provide optimum treatment for the patient. The chracteristics of the train of pressurized gas pulses produced by valve 22 may best be appreciated by reference to Figures 4a, 4b and 4c. The horizontal axes represent the time in milliseconds and the vertical axes represent the flow rate of the high velocity ventilation gas exiting nozzle 58. The letter T represents the time of one ventilation cycle, i.e., the time of a inspiratory phase plus the time of a following expiratory phase. The symbol t₁ represents the time interval during which valve 22 is open. For each of the graphs of Figure 4, the time interval in which valve 22 is opened, i.e., the inspiratory time, is 30 percent of the ventilation cycle T. The graph of Figure 4a represents the pulse train characteristics when valve 22 is opened and closed at a 5 Hz frequency. Graph 4b represents the pulse characteristics when valve 22 is opened and closed at a 10 Hz frequency. Figure 4c represents the pulse characteristics when valve 22 is opened and closed at a 20 Hz frequency. The volume of gas supplied by the valve per breath is equal to the area under the flow rate-time curve of the graphs of Figure 4. The solid lines represent the flow characteristics for ventilator 10. The broken lines represent the flow characteristics for a ventilator which does not incorporate a feature for reducing the time required for the valve to change states in accordance with the present invention. It will be appreciated that the depicted curves have a trapezoidal shape rather than a square wave shaped due to the incremental time interval required for valve 22 to change from one state to another, i.e., from a fully closed state to a fully open state and vice versa. In the prior art, at high pulse frequencies there was insufficient time for the valve to open completely before receipt of a 'close' command. Accordingly, the triangular flow pattern indicated by the broken lines of Figure 4c resulted. A flow pattern as represented by the broken line showing of Figure 4c leads to a drastic reduction in the tidal volume, i.e., the volume of gas supplied to the patient, during the inspiratory phase. Consequently, in order that sufficient tidal volumes be supplied at high ventilation frequencies, the valve must be caused to react quickly to 'open' commands and should remain open for a significant portion of the inspiratory phase. With reference to Figure 3, the valve 22 is opened and closed by means of a solenoid 70 which is responsive to command signals generated by the control module 20. Control module 20 includes a square wave generator 72. A resistance capacitance network 73 is adjustable in the conventional manner to vary the time constant and thus the output frequency of square wave generator 72. The square wave output signal of generator 72 is applied to a timer circuit 74. Referring jointly to Figures 3 and 5, an adjustable voltage magnitude selection circuit and an adjustable duty cycle selection circuit are coupled to timer 74 to cause the timer to provide an output waveform having a selected amplitude (voltage V₁), pulse width (time t₁) and frequency f. Voltage V₁ is selected to be the minimum solenoid holding voltage required to sustain valve 22 in the opened position. This voltage is typically lower than the voltage necessary to cause the solenoid to open the valve. Use of a low voltage to maintain the valve open reduces the closing time for the valve. The closing time is further reduced by a short duration large negative voltage spike -V₂ which is generated at the end of the inspiratory phase of the cycle upon removal of the timer 74 output voltage from the valve solenoid. Time t₁ is selected to provide the optimum inspiratory time per ventilation cycle. Frequency f is selected to provide the optimum ventilation frequency in accordance with the condition of the patient. The square wave from circuit 72 is also applied to an overdrive timer circuit 76. The overdrive timer circuit is also adjustable to generate a second waveform having a second amplitude (voltage V₃-V₁) and second pulse width (time t₂) with the same frequency f as and in phase with the waveform provided by timer 74. Voltage V₃-V₁ and time t₂ are selected to reduce the valve opening time as detailed hereinafter. The two waveforms are combined, as represented schematically by summing circuit 77, and applied to the solenoid 70. The waveform applied to solenoid 70 is illustrated in Figure 5. The period of one opening and closing phase of cycle of valve 22, and hence the ventilation cycle, is given by time T. By applying the overdrive voltage V₃-V₁ to the solenoid, the overdrive voltage having an amplitude which is at least three times as great as the holding voltage V₁, a greater electromagnetic force is generated, and the opening time of the valve is significantly reduced. Thus, the tidal volumes produced by the ventilator at high frequencies is not substantially reduced by the time required for the valve to change its state. As noted above, in the graphs of Figure 4 the broken lines illustrate generally the pulse characteristics without application to the overdrive voltage to the solenoid and the solid lines represent the pulse characteristics of the ventilator when the foregoing described overdrive voltage is applied from the control module. It will be appreciated that the ventilator 10 is operated by selecting an optimum frequency and duty cycle, i.e., the ratio of inspiration time to ventilation cycle time, for the condition of the patient. The tidal volume of ventilation gas supplied to the patient is a function of pulse frequency and duration as well as gas pressure. Pressure regulator 32 regulates the pressure by conventional means. The control module functions to electronically control valve 22 to provide the optimum ventilation characteristics. The latter characteristics may change over the treatment period and the ventilator of the present invention is capable of manual or automatic readjustment in accordance with varying patient requirements. In actual practice, the control and safety modules may be a single subassembly including a programmable microprocessor and the operational mode may be entered from a keyboard and/or selected from preprogrammed data. Since variation of the ventilation parameters can be accomplished without disconnecting the patient from the ventilator, trauma is avoided that could otherwise occur. It should be appreciated that since the ventilator is of modular construction, sterilization and maintenance of the unit can be relatively easily achieved. The entrainment module 16 has no moving components and thus may be easily disconnected from the ventilator for sterilization and/or replacement. The bias flow may contribute at least as means and, depending on circumstances, approximately three times as much, as the gas pulsed through the nozzle providing a considerable dilution of the pulsed gas flow. The present invention has the flexibility, particularly operational parameters which are adjustable over broad ranges, which enables its use in a synchronous intermittent mandatory ventilation (IMV) mode. The IMV mode will be selected, via the microprocessor based control module 20, when it is desired to attempt to wean a patient from the ventilator. In the IMV mode a pulse, at a frequency less than the normal breathing rate, will be provided by a clock in the microprocessor to trigger the generation of command signals for the solenoid of the valve 22. A sensor 80, which could be a pressure sensor in the endotracheal tube, will sense spontaneous breathing by the patient and provide signals commensurate therewith which are inputted to the control module 20. The valve 22 will open at the selected frequency except each time spontaneous exhalation is sensed, in which case the opening of the valve will be delayed until the end of the exhalation and the clock will be reset to zero. The flexibility of the invention permits a wide range of ventilation frequencies from supraphysiological to natural breathing frequencies without requiring additional low frequency respiration circuits. The present invention may also, with the removal of the entrainment module 16 and low pressure gas supply unit 15, be employed in the case of a transcutaneous cricothyroidalostomy. In emergency situations, for example under battlefield conditions or in the case of medical technicians at the scene of an accident, a patient experiencing breathing difficulty cannot be provided with an endotracheal tube. That is, the proper insertion of an endotracheal tube may require as long as one-half hour, requires good lighting and requires a highly trained medical professional. The present invention, with the entrainment module removed but a nozzle similar to nozzle 58 retained, can be utilized by medical technicians in the following manner. A needle with associated catheter will be inserted into the trachea, the needle will then be withdrawn and the nozzle then inserted into the trachea via the catheter. Jet ventilation may then be started with exhalation being via the patient's mouth and/or nose.

Claims: A high frequency jet ventilator comprising a module (16) with a gas inlet port (66), a discharge port (68) in communication therewith across a chamber (52) and a nozzle (58) for the introduction of gas from a pressurized source into the chamber (52) in the direction of a breathing gas outlet (56), characterized by means for continuously supplying highly humidified breathing gas to the inlet port (66), a vent or a reclamation unit (49) constantly connected to the discharge port (68) to establish a bias flow of the breathing gas across the chamber (52), and means for modulating the output of the pressurized source to apply high velocity pulses of dry gas to the nozzle (58); the inlet port (66) and the discharge port (68) being coaxially aligned transversely to a central axis of the chamber (52) and the nozzle (58) being aligned along the central axis and protruding partly between the inlet and discharge ports (66,68) to promote entrainment of the highly humidified breathing gas towards the outlet (56) by the high velocity pulses of dry gas. A ventilator according to claim 1 characterised in that the nozzle (58) has an external convergent portion further to promote entrainment. A ventilator according to any preceding claim characterised in that electronic control means (20) is provided for generating a variable frequency electrical signal and optionally a variable duty cycle and pulse width signal for controlling gas pulse generating means (22). A ventilator according to claim 3 characterised in that the pulse generating means (22) includes a solenoid actuated, normally closed valve interposed between a source of high pressure gas and the nozzle (58) and in that the control means (20) includes means for generating solenoid control voltage pulses having first and second magnitude levels (V₁,V₃), the first level (V₁) being in excess of the solenoid rating, and the second level (V₃) being less than the solenoid rating but sufficient to hold the solenoid in the actuated state. A ventilator according to claim 3 or claim 4 in which the control means (20) are arranged so as to provide a stepped waveform for solenoid operation with a substantially instantaneous rise time.

Inventors: GLUCK, ERIC H., MCDONALD, HENRY, SABNIS, JAYANT, WEINBERG, BERNARD C.
Applicants: ADVANCED PULMONARY TECHNOLOGIES, INC.
Application year: 1987
Main classification: A61M16
IPC codes: A61G10, A61M16