JET VENTILATOR WITH PRESSURE AND VOLUME CONTROL [001] Pulmonary or respiratory therapy is provided to patients using systems that include a ventilator arranged to supply pulses of breathable gas at a rate at about or under the respiration rate of the patient. The systems also include a high frequency jet ventilator (HFJV) connected to supply breathable gas to the patient in pulses at a selected frequency rate well above the respiration rate of the patient. The pressure of the gas in each pulse of the HFJV is controlled to control the therapy. [002] Pulmonary ventilators are well known and widely used to provide a patient with respiratory or pulmonary therapy. In general, a ventilator machine is connected to a source or supply of breathable gas and operated to supply pulses of the breathable gas at a selected pressure and at a selected rate to a patient. Pulmonary ventilators are known and commercially available. As an example, the PURITAN BENNETT® machines include ventilators offered by MEDTRONIC, Inc. of Minneapolis, Minnesota. Dräger of Lübek Germany with USA offices in Houston, Texas is also understood to offer machines suitable for use in respiratory therapy. The Bellavista Neo and Avea EVS pulmonary ventilators are offered by Viasys of Chicago, Illinois. Other sources of pulmonary ventilators include CareFusion of Yorba Linda, California; Welch Allyn of Skaneatelees, New York, and Pulmonetic of Minneapolis, Minnesota. [003] For some patients such as neonates including premature babies, it has been found that the pulmonary or respiratory therapy provided by a high frequency jet ventilator (HFJV) enhances or improves the pulmonary or respiratory therapy when operated to supply pulses of breathable gas to the patient at the same time a pulmonary ventilator continues to supply pulses of breathable gas at or below the respiration rate of the patient. See: US Patent 4,481,944 issued November 13, 1984 (Bunnell); and US Patent 5,239,994 issued August 31, 1993 (Atkins). The LIFE PULSE® high frequency ventilator is a known HFJV offered by Bunnell, Inc. of Salt Lake City, Utah. Other known high frequency ventilators include a Sensormedics 3100Amachine offered by Vyaire Medical Inc. of Irvine California and the EVITA VN 00 offered by Dräger of Lübek Germany. [004] Typical pulmonary ventilation systems such as one illustrated in FIG.1 (prior art) include a ventilator 10 that functions to receive gas such as oxygen 12 and air 14. The ventilator 10 blends them in a blender 16 and directs the blended gas from the blender 16 to a flow controller 18. The flow controller 18 is configured to supply blended gas 30 from output 28 at a rate sufficient to support the inspiratory flow rate of the patient through input filtration 22. The input filtration 22 receives blended gas 30 which is filtered in supply filter 24 and then optionally humidified in the humidifier 26 after which the blended gas 18 is supplied as breathable gas 32 through supply line 33 to an input and output arrangement which here is shown to include a port 34 connected to an endotracheal tube 36 through a “Y” (wye) connector 37. The endotracheal tube 36 is inserted in the trachea (not shown) of the patient 20 to deliver the breathable gas 32 to the patient 20 as pulmonary or respiratory therapy. The breathable gas 32 also may be delivered directly into the trachea of the patient 20 through suitable tubing that functions as an input and output device positioned in an opening formed in the trachea by suitable procedures such as a tracheotomy. [005] The patient 20 is a human being and is typically a neonate such as a premature baby. The patient may also be any other being determined to be suitable to receive respiratory therapy from a ventilator and HFJV combination as discussed hereinafter. The patient 20 may also be any animal that can be treated with breathable gas 32. [006] As shown in FIG.1 (Prior Art), the port 34 is also connected to receive high frequency pulses of breathable gas 38 from a high frequency jet ventilator 40 (HFJV) via a high frequency jet ventilator supply line 42. The HFJV receives a feedback pressure signal from the port 34 via sensing line 44. The HFJV 40 also receives oxygen 12 and air 14 and is configured to blend them to form a blended gas. It could also receive blended gas from a source configured to supply a useful blend. The blended gas is then processed and supplied as pulses of breathable gas 38 at a frequency well above the respiration rate of the patient and preferably at a rate from about 220 to about 660 breaths per minute. [007] As seen in FIG.1 (Prior Art), the breathable gas 32 and 38 is supplied through port 34 and into the endotracheal tube 36. A separate port filter or filter device (not shown) may be connected to “Y” connector 37. The “Y” connector 37 has one leg 48 connected to receive breathable gas 32 from ventilator 10; and breathable gas 38 from the HFJV is connected to the port 34. Another leg 50 of the “Y” is connected to direct exhaust gas 54 outwardly; and a third leg 52 is connected to the endotracheal tube 36. After the breathable gases 32 and 38 are inspirated into the lungs of the patient 20, they are thereafter exhausted as exhaust gas 54 which proceeds from the endotracheal tube 36 and leg 50 of the “Y” to and through optional exhaust filtration 56 that includes an optional outlet filter 58 and may also include a water trap 60 to remove moisture from the exhaust gas 54. A water trap of the type comparable to those used in today’s pulmonary therapy systems and useful as water trap 60 in FIG.1 (Prior Art) is described in US Patent 3,454,005 (Eubanks, et al). Those skilled in the art will also understand that commercial water traps are available today from suppliers including, for example, Armstrong Medical Ltd of Coleraine, Northern Ireland. Medtronics also offers a Puritan-Bennett® water trap. Typical filters in the exhaust filtration structure 56 comparable to filter 58 in FIG.1 (Prior Art) useful in respiratory or pulmonary systems can be seen in US Patent Design D441,449 (Gaskel), in US Patent 6,619,287 (Blackhurst, et. al.) and in US Patent 3,782,083 (Rosenberg). [008] The breathable gas 32 is supplied to the “Y” and then expirated at a rate comparable to the normal respiration rate of the patient. The respiration rate is controlled by the exhaust valve 62 which functions to allow time for expiration. At the same time, the HFJV supplies gas 38 at frequency so there is in effect no time for expiration. That is, it is recognized the patient 20 is not able to respirate at the pulse rate or frequency of the high frequency pulses of breathable gas 38. In turn it has been theorized that the inbound high frequency pulses of breathable gas 38 to the patient 20 can be a stream at the center of the endotracheal tube 36 with the outbound gas (from the lungs) as high frequency pulses gas expirated the same rate as the high frequency pulses of breathable gas 38 in some form perhaps as a stream around or adjacent the inbound gas and thereafter further exiting through the port 50 as part of the exhaust gas 54. [009] Exhaust gas 54 may be dehydrated and filtered in the exhaust filtration 56 and then directed as filtered gas 64 to or through the exhaust valve 62 associated with the ventilator 10. The exhaust valve 62 is opened and closed to create pulses of breathable gases at the “Y” fitting 37. [010] The exhaust valve 62 along with a flow control device 68 and the blender 16 are controlled by the control 70 of the ventilator 10 to blend and supply pulses of blended gas 18. The control 70 of the ventilator 10 has controls to allow an operator to choose or select desired respiration functions such as pressure, respiration rate and, in this illustrated arrangement, the gas blend. The ventilator 10 may also have a pressure transducer 33 to detect the pressure at the port 34 via sensor line 74 of the breathable gas 32 being delivered to the patient 20. [011] Air 14 and oxygen 12 are the typical gases supplied to the ventilator 10 and blended in the blender 16 of the ventilator 10 to form the blended gas 18 as well as to the HFJV to form high frequency pulses of breathable gas 38. The amount of air 14 and oxygen 12 supplied is controllable and may be adjusted by the blender 16 through the controller 70 so that the breathable gas 32 may vary between essentially all air to air highly enriched with oxygen. The air 14 and the oxygen 12 may be available from central storage in hospitals and other medical facilities. Alternately, the air 14 may be drawn from the environment and compressed within the ventilator. While air and oxygen are the typical gases, other gases may be added or substituted. Other gases and medications may also be introduced into the air 14 and/or the oxygen 12 if desired. [012] For patients whose lungs have been compromised or that have not yet developed, such as premature babies, it is important to maintain a minimum intra-alveolar pressure to encourage the alveoli to function. Use of the HFJV 40 assists to maintain the intra-alveolar pressure. [013] In operation of systems such as that discussed in reference to FIG.1 (Prior Art), operators have relied on adjusting the pressure of the gas in each pulse of high frequency breathable gas 38 delivered by the HFJV 40 along with the pressure and rate of each pulse of breathable gas 32 delivered by the ventilator 10. The objective is to maintain blood gases within desired parameters as well as to maintain the lungs and in particular the intra-alveolar pressure and in turn the alveoli of the patient within desired guidelines. [014] While the frequency and pressure of each pulse of the HFJV are controlled, there are no known HFJV systems that control the volume of each pulse of high frequency pulse of breathable gas 38 to take into account gas losses at or near the endotracheal tube, lung compliance and changes over time. Also there are no known HFJV that are able to control both the volume of pulses as well as the pressure of pulses. [015] An improved method of providing pulmonary therapy to a patient includes first obtaining a breathable gas from a source and connecting a ventilator to that source to receive the breathable gas and to provide it to a patient through a provided supply line. The improved method further includes operating the ventilator to supply the breathable gas through suitable input and output structure for further transmission to the patient in the form of pulses at a rate that is at or less than about the respiration rate of the patient. The improved method further includes providing a high frequency jet ventilator (HFJV) and also connecting it to the source of breathable gas. The HFJV is operable to receive the breathable gas from the source and supply the breathable gas in the form of high frequency pulses through another supply line to the input and output structure for further transmission to the patient. The HFJV is configured with pulse controls to control the frequency of the high frequency pulses of breathable gas to be above the maximum respiration rate of the patient. The HFJV is also configured with controls to control the pressure of each pulse and to control the volume of each pulse of the high frequency breathable gas. The improved method includes operating the pressure controls, the pulse controls and the volume controls of the HFJV to supply the high frequency pulses of breathable gas in pulses at a selected frequency substantially above the maximum respiration rate of the patient and at either a selected pressure or having a selected volume all while the ventilator is supplying pulses of breathable gas at or below the respiration rate of the patient. [016] A preferred method includes obtaining and installing a flow sensor means for measuring the flow of the high frequency pulses of said breathable gas of said HFJV and connecting the flow sensor means to supply signals reflective of the flow of the high frequency pulses of breathable gas as detected by the flow sensor means to the HFJV. [017] In a more preferred method, means are provided to detect a signal reflective of at least one blood gas and wherein the user operates one or both of the pressure controls and volume controls to supply the high frequency pulses of the breathable gas to control the signal reflective of said one blood gas. [018] A more desired method of the HFJV is provided with a console having a display to display the frequency of the high frequency pulses being supplied to the patient and to display the pressure of the pulses of high frequency breathable gas being supplied to the patient. In addition, the console preferably has means to display the volume of the high frequency pulses being supplied to said patient. [019] In an alternate method, the HFJV is provided with means to calculate the volume of all the high frequency pulses being delivered to the patient over a period of one minute (the “minute volume") and further configuring said console with means to display the minute volume. The alternate method further provides console with a screen configured to display a graph of the pressure in the supply line measured at preselected intervals of time while operating the HFJV. [020] In a more specific preferred arrangement, the operator manipulates the frequency controls of said HFJV to set the frequency of the high frequency pulse rate of the breathable gas from at least about 10 times to about 30 times the maximum respiration rate of said patient. [021] An alternate method of providing pulmonary therapy to a patient such as a neonate having a maximum respiration rate and with means associated with the patient for detecting and displaying signals reflective of at least one blood gas includes providing a source of breathable gas and an HFJV and connecting the HFJV to receive the breathable gas and operating the HFJV to supply the breathable gas to the patient. The HFJV is configured with pulse controls to supply pulses of the breathable gas to the neonate at a selectable frequency from about 200 pulses per minute to about 660 pulses per minute. The alternate method also includes configuring the HFJV with pressure controls operable to regulate the pressure of the gas in each of the pulses of the breathable gas being supplied to the neonate, and configuring the HFJV with volume controls operable to regulate the volume of gas of each of the pulses of the breathable gas being delivered to said neonate at a selected pressure range set with said pressure controls. The alternate method also includes providing supply line means and connecting the supply means for supplying the pulses of the breathable gas from the HFJV to the neonate. The alternate method also includes operating the pressure controls and the volume controls of the HFJV to either regulate the pressure of each of the pulses of the breathable gas being supplied to the neonate or the volume and pressure of said pulses of said breathable gas being supplied to said neonate. [022] An improved alternate method includes operating the pulse controls, the pressure controls and the volume controls of the HFJV to set said frequency and either the pressure or the volume to control the display reflective of said at least one blood gas of said neonate. [023] More specifically, the alternate method further involves providing a flow sensor means to sense the flow of the high frequency pulses of the breathable gas to the neonate and further requires connecting the flow sensor means in the supply line means to measure the flow of the pulses of the breathable gas. [024] In a preferred alternate method, configuring the HFJV to have a console with displays to display the rate and the pressure of the pulses being supplied to the neonate. In yet another alternate method, configuring the HFJV to have a display of the volume of each of the pulses being supplied to the neonate. [025] A more preferred method includes configuring the HFJV to have means to calculate the minute volume of all the pulses being delivered to said neonate over a period of one minute and further configuring said console to have means to display said minute volume. [026] In a desired method, the console of the HFJV is arranged to have a screen operable to display a graph of the pressure in the supply line at selected times. [027] Also disclosed is a high frequency jet ventilator (HFJV) system for connection to a source of breathable gas for supplying the breathable gas to a patient. The HFJV system comprises means for connection to a source of breathable gas along with pulse controls operable to supply pulses of the breathable gas to a patient at selectable frequency well above the respiration rate of the patient and in turn from about 220 pulses per minute to about 660 pulses per minute. The HFJV system also includes pressure controls operable to regulate the pressure of each of the pulses of the breathable gas and also volume controls operable to control the volume of each of the pulses of the breathable gas which is deliverable to the patient in a preselected pressure range. The HFJV system also includes supply line means for connecting said HFJV to the patient to supply the pulses of the breathable gas. And the system also includes flow sensor means for measuring the flow of the high frequency pulses of the breathable gas in the supply line means. The HFJV of the system also includes a console having displays reflective of the pulse rate, the pressure breathable gas of each pulse, the volume of each pulse and the flow of the breathable gas. [028] A preferred HFJV system further includes means to calculate the minute volume of all the high frequency pulses being delivered to a patient over a period of one minute and further configuring said console with means to display said minute volume. [029] In a highly preferred HFJV system, the HFJV has a console which includes a screen configured to display a moving graph of the drive pressure in the supply line at intervals of time while operating the HFJV. The graph may also display volume at intervals of time. [030] To further clarify the advantages and features of the systems and structure herein disclosed, a more particular description is rendered with reference to the appended drawings. It should be understood that the drawings depict only typical steps and embodiments and therefore are not to be considered limiting of the scope of the appended claims. More specifically: [031] FIG.1 is a block diagram of a prior art pulmonary ventilation system; [032] FIG.2 is a simplified diagram depicting a high frequency jet ventilator system as herein disclosed; [033] FIG.3 is a simplified flow diagram to illustrate the steps of the methods of ventilating a patient as herein disclosed; [034] FIG.4 is a simplified block diagram of the controller of a high frequency jet ventilator system as herein disclosed; and [035] FIG.5 is a block diagram representation of the display of a console of a high frequency jet ventilator system as herein disclosed. [036] FIG.2 depicts an improved high frequency jet ventilator (HFJV) in a system 80 having a HFJV ventilator 82 connected to patient box 84 from which connection is further made to a port 86 and thereafter to an endotracheal tube 88 for introduction into the trachea of a patient 90. The system 80 also includes a ventilator 81 connected to receive breathable gas from a source 92 and means to monitor and display and/or provide signals reflective of blood gas 101. It should be understood that a patient here may be any human or any animal able to take breathable gases. However, it should also be noted that many of the patients treated using a HFJV system 80 such as that shown in FIG.2 are neonates including premature human babies. [037] As seen in FIG.2, the system 80 includes an HFJV 82 which is connected to receive breathable gas from a source 92. The source can be room air, bottled gas and air supplied by a remote system along with supplemental oxygen blended to a desired ratio. Other gases and medications can be added for whatever other therapies are desired here or after the patient circuit 142. The gas from the source 92 as mixed is supplied through line 93 to the ventilator 81 and also through a diameter index safety system (DISS), connector 94 and a filter 96 to a series of flow control solenoid valves 102, 104 and 106. The three solenoid valves 102, 104 and 106 are used to regulate the pressure in the compliance chamber 120. The three solenoid valves 102, 104 and 106 are pulsed 120 degrees out of phase with one another to smooth the pressure of the gas in the compliance chamber 120. The solenoid valves 102, 104 and 106 are all arranged to fail closed on the absence of power and are controlled by the ventilator controller 118. While three solenoid valves 102, 104 and 106 are shown to provide for reliability should one of the three fail, the user may elect to use a different number of such valves. Alternately, one or more proportional valves may be used to accomplish the same pressure regulation of the pressure in the compliance chamber 120. [038] In FIG, 2, it can also be seen that as the breathable gas enters the HFJV 82, there is a relief valve 108 provided to protect the ventilator 82 from over pressure conditions in the supply or source 92. Also, a flow restrictor 110, valve 112 and filter 114 are provided to supply gas to a sample port 116 should the user elect to operate and open the valve 112 to verify or test the gas mixture coming from the source 92 during or before use. [039] The breathable gas from the solenoid valves 102, 104 and 106 proceeds into the compliance chamber 120 which functions as a reservoir to smooth the pressure of the breathable gas as it proceeds out therefrom toward the patient 90. When in operation, the volume of gas in the compliance chamber 120 may be directed to a dump valve 122 should it be determined that system fault or error has been detected where continued attempted ventilation of the patient could lead to patient harm. As the gas is being dumped from the valve 122, it passes into a muffler 128 to soften any noise that would arise as the gas exits the valve 122. The controller 118 operates the dump valve 122 when it is deemed desired to stop or interrupt further gas passing from the compliance chamber 120 to the patient box 84. Notably, another relief valve 124 is provided with a discharge to atmosphere 125 should there be an over pressure condition in compliance chamber 120 to protect the patient 90 from an overpressure situation. [040] As further seen in FIG 2, the breathable gas passes from the compliance chamber 120 to a flow meter 132 which measures the flow of the gas toward the patient and sends a signal via conductor 134 reflective of the flow to the controller 118 for further processing and display as desired. A suitable flow meter for this application has been found to be a MEMS mass flow sensor offered by Siargo Ltd. of Santa Clara, California. [041] The breathable gas 130 passes from the flow meter 132 through a check valve 136 toward the patient box 84 and through a patient circuit 142 which is comprised of the tubing between the HFJV 82 and the patient box 84 as well as an optional humidifier box to control the humidity of the gas 130 passing to the patient box 84 and more particularly to a pinch valve 140 which is controlled by the controller 118 via line 107 to open and close at the frequency desired (e.g., between 220 and 660 pulses per minute). In short, the pinch valve 140 causes pulses of breathable gas to be directed to the life port 86 and then to the endotracheal tube 88 and then on to the patient 90. [042] The patient box 84 also includes a purge system which receives purging gas from a purge regulator 150 in the HFJV 82 as well as a purge source valve 152. A purge pressure relief valve 146 is shown to protect the purge system from over pressure. Check valve 154 prevents back flow. The purge valve 160 is a solenoid valve operated by a patient box controller 156 between a first position where the purge gas 148 is directed through a purge filter 162 and a purge flow restrictor 164 to the port 86 to purge the port 86 and a second position where the purge gas 148 is directed to the zero valve 158 as discussed hereinafter. In the first position, purge gas is directed to effect purging of the port 86 may be desired to cause removal of any contamination in the pressure monitoring port 86. The flow restrictor 164 limits the flow of purge gas 148 such that there is a minimal positive pressure offset to the pressure monitoring line 103 to prevent accumulation of fluids in the pressure monitoring line 103. Fluids in the pressure monitoring line 103 may dampen or obscure the airway pressure signal of interest. If the airway pressure signal is degraded, the purge valve 160 may be activated to apply purge gas directly to the pressure monitoring line 103, bypassing the purge filter 162 and flow restrictor 164, in an attempt to clear any obstruction in the pressure monitoring line 103. [043] The zero valve 158 is a solenoid type valve that is operated by the patient box controller 156 between one position in which it is connected to an airway pressure transducer 166. The airway pressure transducer 166 sends a signal reflective of the airway pressure via line 103 to the patient box controller 156 and to the controller 118 via line 105 to regulate movement of the flow control valves 102,104 and 106. The zero valve 158 has a second position in which it connects the pressure transducer 166 to the atmosphere via line 168 to check and calibrate the transducer zero pressure reading as necessary. [044] Returning to the HFJV 82, it may also be seen in FIG.2 that a pressure transducer 170 sends signals reflective of the pressure of the gas as it is exiting the compliance chamber 120 to the controller 118 which in turn uses signals reflective of the pressure of the gas which is indicative of the patient condition. A test port 172 is also shown to allow a known pressure to be applied for calibration of the servo pressure transducer 170. [045] In operation, the high frequency jet valve system 80 receives breathable gas from a source 92 and supplies it through the filter 96 to flow control valves 102, 104 and 106. The breathable gas exits the flow control valves 102, 104 and 106 and goes to a compliance chamber 120 and through the flow meter 132 and then through check valve 136 and the patient circuit 142 to the pinch valve 140. The pinch valve 140 opens and closes at a frequency set by the user through the controller 118 to provide high frequency pulses of breathable gas 130 through the patient circuit 142 to line 141 and then to the port 86 and endotracheal tube 88 above the maximum respiration rate of a patient and preferably in the range of about 10 times to about 30 times the maximum respiration rate and even more preferably between 220 and 660 pulses per minute to the patient 90. [046] It can also be seen in FIG.2 that the ventilator 81 receives breathable gas from the source 92 and is then operated (see for example FIG.1 (prior art)) to supply pulses of breathable gas through line 99 at or below the respiration rate of the patient (as controlled by an exhaust valve (not shown) in the ventilator 81) through the “Y” connector 95 and the port 86 to the endotracheal tube 88 to the patient 90. Exhaust or expiration gas returns to the exhaust valve in the ventilator 81 through line 97. [047] A blood gas device 101 is also shown which can be a pulse oximeter or any other device that provides information of at least one blood gas of the patient. The user or operator may observe the at least one blood gas and adjust the controls of the HFJV 82 and/or the ventilator 81 to vary or change the at least one blood gas as desired. [048] When operating in the pressure mode, the drive pressure in the compliance chamber 120 is controlled by the ventilator controller 118 by adjusting the timing of the three flow control valves 102, 104, and 106 to achieve the desired peak inspiratory pressure in the patient airway as reflected by the pressure monitoring line 103 and the airway pressure transducer 166 here shown in patient box 84. The ventilator controller 118 is programable to affect the desired operation. [049] In the volume mode, the flow of gas into the compliance chamber 120 may be fixed to a particular value. In this case, the ventilator controller 118 sets the timing of the three flow control valves 102, 104 and 106 to desired fixed value, assuring a relatively constant flow into the compliance chamber 120 which results in a particular drive pressure. When the pinch valve 140 is opened for a known period of time, breathable gas at this fixed pressure is delivered to the patient interface 86 at essentially a constant volume. This volume may be varied by changing the flow control valve timing. An essentially constant volume is one that varies some with temperature and other empirical factors arising from each system and patient. [050] Another method of achieving a substantially fixed volume to the patient 90 is to fix the drive pressure in the compliance chamber 120 to a particular value. This may be accomplished by the ventilator controller 118 being programmed to adjust the timing of the three flow control valves 102, 104 and 106 to maintain the pressure in the compliance chamber 120 as determined by the servo pressure transducer 170. When the pinch valve 140 is opened by signals from the controller 118 for a known period of time, breathable gas at this fixed pressure is delivered to the port 86 through line 141 at what is considered a substantially constant volume. This volume may be varied by changing the drive pressure or the time the pinch valve 140 is open. A substantially constant volume is one that varies based on empirical factors arising from each system and each patient. [051] However, it should be understood that in the present arrangement, the preferred method of controlling flow to the patient is to use a flow meter 132 in line with the breathable gas source. The ventilator controller 118 would adjust the timing of the flow control valves 102, 104 and 106 in response to the output of the flow meter 132 to maintain a desired delivered volume at the desired delivery rate and inspiratory time. [052] Turning now to FIG.3, a block diagram shows the method steps of pulmonary or respiratory therapy. The steps involve first providing a ventilator 202 and supply line 204. The ventilator 202 is then connected to receive the breathable gas 200 and then connected 208 to a patient 90 to supply the breathable gas 200 to the patient. The ventilator 202 is operated to form pulses of breathable gas at a frequency or rate 209 that is at or less than the respiration rate of the patient 240. [053] In FIG 3, it is also seen that a high frequency jet ventilator (HFJV) is provided 210 along with a supply line 212. The HFJV is connected 214 to receive gas from the source of breathable gas 200 and connected 214 to the patient to supply the breathable gas from the ventilator. The HFJV is configured with pulse controls 216 which are operated to provide pulses of the breathable gas at a frequency higher than the maximum respiration rate of the patient and preferably from about 10 to about 20 times the maximum respiration rate of the patient. The HFJV is also configured with pressure controls 218 and with volume controls 220. The pressure controls 218 and volume controls 220 are operated 222 to control either the pressure of the gas in the pulse or the volume of the pulse at a selected range of breath settings (e.g., rate and pressure). [054] In a preferred method, a flow sensor may also be provided and operated 224 to provide flow information to assist in controlling the flow of the breathable gas. [055] The method or system includes providing a device (e.g., blood gas detector 101 in FIG.2) to provide signals reflective of blood gases 226 in the patient’s blood so the user can observe the blood gas and then operate the HFJV and its pulse controls and one or both of the pressure controls and volume controls to affect the flow of breathable gas and in turn the signals reflective of blood gases. Also, the HFJV is configured to have a display 228 showing pulse, pressure and volume data as desired. [056] A method of providing ventilation therapy to a patient also includes configuring the HFJV to have means to calculate the minute volume 230 of gas being delivered to the patient. The minute volume is the total gas supplied by the HFJV to the patient in one minute. A console is also provided and configured with a display including a graph 232 that shows the pressure on the vertical or Y axis by unit of real time along the X axis. [057] The block diagram of FIG.4 shows a controller 280 of an HFJV such as the controller 118 of the HFJV 82 of FIG 2. The controller 280 of FIG.4 receives AC power from a source 282 through a power supply unit 284 that converts the AC power to voltages at other levels for further transmission of power to the power control unit 286. The power control unit 286 is configured to distribute power to the various components in the controller 280 through conductors not shown for simplification of the illustration. A battery 288 is provided as a back up source of power to the power control unit 286. The battery 288 is sized to operate the HFJV for a preselected period of time in the event of loss of AC power for whatever reason. [058] The controller 280 of FIG.4 also is connected to a display 290 that contains visual displays of data as well as data input from buttons or switches all as hereinafter discussed. The display 290 is connected to a microprocessor 292 which receives input from the display 290 and also from other components in the controller 280. The microprocessor 292 also transmits data back to the display 290 for display as hereinafter discussed. [059] The controller 280 of FIG.4 also includes a microcontroller unit or MCU 294, a supervising MCU 296 and watchdog timer 298 that operates to monitor correct operation of the programs in the MCU 294 and the supervising MCU 296. The microcontroller unit or MCU 294 is programed to operate valve drivers 300 which operate solenoid valves such as, for example, solenoid valves 102, 104 and 106 found in the HFJU 82 in FIG.2. The microcontroller unit or MCU 294 also receives input signals from pressure detectors such as servo pressure transducer 170 seen in FIG.2 and other sensors and detectors through data conversion structure 302. [060] The controller 280 of FIG.4 also includes an alarm output 304 which supplies signals to activate various alarms (e.g, loss of power, extubation of endotracheal tube, over pressure) when operating data is in an alarm condition that is preprogramed into the microcontroller unit or MCU 294. Alarms operate to alert the user of a condition that is outside of set standards typically set by the Federal Food and Drug Administration. The microcontroller unit or MCU 294 also may have a receiver port 308 to transmit data to the Electronic Health Record (EHR) 306 such as operating conditions (e.g. pulse rate, pressure). The receiver 308 also sends back information regarding alarm conditions and other EHR information when permitted by policy, rule and/or statute. [061] Local staff or users such as nurses in a neonatal intensive care unit (NICU) are alerted to alarm conditions by signals sent to the nearby nursing station by a “nurse call” circuit 310 operated by the microcontroller unit or MCU 294 within the controller 280 of FIG.4. That is, in some cases, a nurses’ station near the patient’s room in, for example, a hospital or clinic have an alarm light to alert a nurse to a condition or event that could suggest the need for action by the nurse observing the alarm light. Similarly, the microprocessor 292 is configured to communicate other data for service communication 312 purposes to an external device to aid in calibration and maintenance activities as permitted by local policy, rule and/or statute. [062] The microcontroller unit or MCU 292 of FIG.4 also has a Logging/Storage unit 314 which is a form of memory that records data such as alarm conditions, pressure and pressure changes and the like as may be required by local rule, policy and statute. For example, some operating data may need to be retained so the history of operation may be recovered for later evaluation. [063] Turning now to FIG.5, an HFJV display 240 is part of or on a console 241. The display 240 is depicted showing operating switches and buttons as well as other visual indicators and a graph as hereinafter discussed. That is, an HFJV has a console or chassis 241 sized to contain most of the components such as the HFJV 82 of FIG.2 and the operating controller of 280 of FIG.4. It may also have an on-off switch or button somewhere on the console (e.g., on the back) to connect electric power from a source such as a wall plug. A cord (not shown) extends from the wall plug to the switch (not shown) to the power supply unit such as power supply unit 284 and other various components as seen in FIG.4. [064] The display 240 on console 241 as seen in FIG.5 includes a STANDBY button or switch 242 which pauses or suspends operation of the HFJV such as HFJV 82 seen in FIG.2. The STANDBY button does not turn off the HFJV but allows components to remain activated while suspending operation. While any form of switch may be used for the STANDBY button or switch 242, an un-depress/depress form is here employed and is of the type where the button is illuminated when depressed. [065] Also seen on the display 240 is a PRESSURE button 244 and a VOLUME button 246. The PRESSURE button 244 and the VOLUME button 246 are similar to the STANDBY button 242 and are of the un-depress/depress type which illuminate when depressed. In operation, the user selects by pushing or depressing one of the buttons, namely: STANDBY 242, PRESSURE 244 and VOLUME 246. The buttons or switch STANDBY 242, PRESSURE 244 and VOLUME 246 may be mechanically ganged so that only one can be depressed. That is, when one is depressed the others are gaged or automatically moved to their depressed position. [066] When the PRESSURE switch or button 244 is depressed, the STANDBY button 242 moves to an un-depressed condition. In turn, depressing the STANDBY button 242 then places the HFJV in the standby condition and moves the PRESSURE switch or button 244 to the un- depressed position. And at the same time, the VOLUME switch 246 cannot be moved to the depressed condition. When the PRESSURE switch 244 is depressed, an HFJV such as HFJV 82 of FIG.2 is activated and operates to supply pulses of breathable air to a patient at a pressure that is set by the user to be between a maximum or high and a minimum or low. Activation or depressing the PRESSURE switch 244 allows control of the peak inspiratory pressure (PIP) which is presented visually on an indicator 252. In FIG.5, the number 23 is shown on the indicator 252 to reflect that a detected pressure may be 23 centimeters of water (cmH2O). That is, the PIP is the pressure of each pulse of breathable gas being supplied and visually displayed on indicator 252. The PIP shown on indicator 252 may be changed by use of a PIP operator 262 shown in FIG 5 displaying the same number as seen on the PIP indicator 252. The PIP operator 262 can be moved between an un-depressed position as seen in 262 and a depressed condition as seen in phantom at 264. When in the depressed condition as seen in phantom at 264, the display changes to visually present a number reflective of the PIP and at the same time display + (plus) and – (minus) indicators that are touch sensitive. That is, one can touch the plus and minus to raise and lower the set point for PIP. Thereafter the user may un-depress the operatory 262 allowing the PIP to be displayed at 252. With a new set point entered, the system operates to bring the PIP to that set point which can be observed on the indicator 252. [067] When the VOLUME switch 246 of the display 240 is depressed, it causes the PRESSURE switch 244 and STANDBY switch 242 to be forced into the un-depressed condition. The VOLUME is displayed as MINUTE VOLUME 256 which is the total milliliters of breathable gas delivered in one minute. A volume over one minute is used because the number is bigger and easier to read in comparison to measuring volume over shorter or smaller units of time. When the VOLUME switch 246 is positioned in the depressed condition, the pressure such as the PIP and PEEP are locked to a fixed range with the actual pressure being displayed in the PIP display 252 and in the PEEP display 268. [068] The MINUTE VOLUME display 256 is also a switch in that it operates between a depressed and an un-depressed condition (as shown). When depressed, the screen changes from showing a number to a display that presents a number reflective of the MINUTE VOLUME with + (plus) and – (minus) indicators that are touch sensitive and can be touched to raise and lower the setting for MINUTE VOLUME. That is, the operator may touch the plus to raise the minute volume set point and the negative to lower the minute volume set point. Thereafter, the user may un-depress the indicator 256 allowing the MINUTE VOLUME to be displayed. [069] The display 240 of the console (not shown) also includes a humidifier switch or button 248. The humidifier button or switch 248 is also a two-position switch which may be depressed or un-depressed. In the undepressed condition, the humidifier here found in the patient circuit 142 (FIG.2) is off. When the humidifier switch is depressed, the humidifier (not shown) in the circuit 142 is activated adding humidity to the breathable gas being delivered to the port 86 (FIG.2) and the patient 90. [070] The display 240 seen in FIG.5 also has a READY indicator 250 which is a light that operates between a lit condition and an unlit condition. Quite simply, when the HFJV is activated by turning it on, the READY indicator is dark or unlit. After a suitable period of time, the READY indicator is illuminated when at least the desired pressure or volume has been reached and is stable and all alarms provided by the alarm output 304 (FIG.4) have been activated and are ready. The READY light returns to the unlit condition upon deactivation of the HFJV system 80 (FIG.2). [071] The display 240 of FIG.5 also has a SUCTION switch or button 253 which operates between an undepressed condition and a depressed condition. In the depressed condition, the button or switch 253 is illuminated and at the same time places the HFJV 82 (FIG.2) in standby and allows a suction catheter to be advanced through a port in the “Y” wye connector such as ”Y” connector 95 and extend into the endotracheal tube 88 to remove any secretions that may have collected there to be placed on the lines to extract any possible contamination that may have lodged between the patient 90 and the “Y” 95 (FIG.2). [072] The user or operator may also watch the display 240 to not only see the PIP on PIP indicator 252 as well as the ΔP(delta P) which is seen on indicator 266. The ΔP is a calculation of the difference between PIP and PEEP (Positive End Expiratory Pressure). As a pressure it is presented in centimeters of water (cmH2O). [073] The display 240 also includes a drive pressure indicator 260 which may also be called the servo pressure. When the VOLUME button 246 is depressed, the drive pressure is typically set between a high of about 2.9 and 2.0 as reflected in the drive pressure indicator 260 while the user operates to control the minute volume as seen on the minute volume display 256 as hereinbefore discussed. However, the drive pressure indicator 260 is also a switch that operates between a depressed and an un-depressed condition. When depressed, the indicator changes from showing a number that presents a number reflective of the drive pressure to a new display that not only has the drive pressure but also has + (plus) and a – (minus) indicators that are touch sensitive and can be touched to raise and lower the setting for drive pressure. That is, the operator may touch the plus to raise the drive pressure and the negative to lower the drive pressure. Thereafter, the user may un-depress the drive pressure indicator 260 allowing a real time display of the actual drive pressure. [074] The display 240 also contains a PEEP indicator 268 to show the PEEP as a pressure in centimeters of water (cmH2O). A I:E ratio indicator 270 is also shown with a ratio of the inspiratory time to expiratory time at whatever are the settings of the HFJV 82 then in place. This value is calculated based on the set breath rate and inspiratory time. The MAP indicator 272 is present to show the mean airway pressure which includes the pressure in the airway from the HFJV and the ventilator as well as the pressure from any spontaneous breathing. The MAP indicator 272 also displays as a pressure in centimeters of water (cmH2O). [075] The display 240 also includes rate display 274 to show the rate of the pulses of breathable gas 130 (FIG.2) being delivered to the patient 90. The rate display 274 is also a switch that operates between a depressed and an un-depressed condition. When depressed, the rate display 274 changes from showing a number that presents a number reflective of the drive pressure to a new display that not only has the rate displayed but also has + (plus) and – (minus) indicators that are touch sensitive and can be touched to raise and lower the setting for rate of pulses of breathable air. That is, the operator may touch the plus to raise the rate and the negative to lower the rate. Thereafter, the user may un-depress the rate display 274 allowing a real time display of the actual rate of pulses of breathable air in breaths per minute. [076] Also shown in FIG.5 is an indicator of inspiratory time (I-time) is I breath indicator 273 which displays the time for an inspiratory breath in seconds. Shown in FIG.5 is the number 0.020 seconds as seen in indicator 273 which is representative of what might be seen in some operating configurations. [077] The display 240 also shows a line graph 276 which presents the minute volume 257 (which is also seen in indicator 256) in real time moving back and forth 275 as the minute volume changes. Also shown is a graph 277 which shows drive pressure as seen in drive pressure indicator 260 on the Y axis 265 over time along the X axis 267. Presenting the drive pressure over time allows the user to observe drive pressure over time and in turn observe the delivery of pulmonary or respiratory therapy to the patient over a longer term. An experienced user will be able to notice highs and lows in the drive pressure indicating in turn the overall status of the patient. Also seen is a battery status panel 279 which has a test function 281 and a status graph 283 which functions like a fuel gage. Also seen are plus minus buttons that may be used in the alternative from that hereinbefore discussed to adjust functions like mean airway pressure and drive pressure. [078] Also seen above the display 240 is an alarm lamp 271. [079] Those skilled in the art will recognize disclosed structures and methods may be practiced using materials that may be different from those identified hereinabove without departing from the principles as disclosed. Only specific embodiments have been disclosed to illustrate the structures and methods as defined by the appended claims.