AU2017202586A1 - System and method of administering a pharmaceutical gas to a patient - Google Patents

Abstract

A method and system for delivering a pharmaceutical gas to a patient. The method and system provide a known desired quantity of the pharmaceutical gas to the patient independent of the respiratory pattern of the patient. The preferred pharmaceutical gases are CO and NO, both of 5 which are provided as a concentration in a carrier gas. The gas control system determines the delivery of the pharmaceutical gas to the patient to result in the known desired quantity (e.g. in molecules, milligrams or other quantified units) of the pharmaceutical gas being delivered. Upon completion of that known desired quantity of pharmaceutical gas over a plurality of breaths, the system can either terminate any further delivery of the pharmaceutical gas or can activate an 10 alarm to alert the user that the known quantity has been delivered. The system also has alarm functions to alert the user of possible malfunctions of the system.

Description

2017202586 19 Apr 2017

SYSTEM AND METHOD OF ADMINISTERING A PHARMACEUTICAL GAS TO A PATIENT

Background

The present invention relates to a method and system for administering a pharmaceutical gas to a patient and, more particularly, to a method and system for 5 mtoduring carbon monoxide CO or nitric Oxide NO to a patient in a predetermined quantify.

Background of the Invention

The normal or conventional way of giving a pharmaceutical drug to a patient is to prescribe the dose based on the quantity of drug (usually in weight) per unit weight 10 of the patient (e.g. tng/Kg) with the dose being specified to be delivered over a period of time or being repeated at specified intervals of time. This allows the user to control the quantity of drug and ensures the quantity of drug being delivered is in proportion to the patient’s size. This is to reduce the patient to patient variability in response to the drag due to the size of the patient i.e. a 7Kg baby will not get the same quantity of 15 drug as a 80 Kg adult 3h recent times there have been a number of gases which have been shown to have pharmaceutical action in humans and animals. Examples include Nitric Oxide (NO) Zapol et al US 5,485,827 and more recently Carbon Monoxide (CO) Otterbein et al (U.S. Published Patent Application No. 2003/0219496). hr the Otterbein patent 20 application, CO is described as having a pharmacological action in a number of medical conditions including ileus and vascular disease. hi these cases, the carbon monoxide gas needs to be delivered to the patients alveoli where it can move across the alveolar membrane and into the blood stream where its action can take effect. The current dosing used in these cases is for the 25 patient to breath at a specified concentration of CO in ppm for a specified period of 1 2017202586 19 Apr 2017 time. Accurate dosing of CO for these treatments is Important as CO reacts with the hemoglobin in the blood to form carboxyhemogJobin which means the hemoglobin is no longer able to carry oxygen to the tissues of 4e body. If too much CO is given, the 5 There is a tight window for CO delivery between the therapeutic level and the level that causes earboxyhemaglobin above safe levels. Up until now CO has been delivered as a constant concentration in the gas breathed by the patient/animal for a specified period of time. For example in reference 3 of the Otterbein publication, (Example, 2 pg 13) the therapeutic dose delivered to mice for the treatment of ileus 10 was 250 ppm of CO for 1 hour.

However, this method of dosing CO can be associated with large variability in the actual dose being delivered to the animal/humans alveoli. This variability is bemuse the quantity of CO being delivered to the animal/patient is dependent on a number of variables including, but not limited to, the patients tidal volume, respiratory 15 rate, diffusion rate across the alveolar and ventilation/perfusion (V/Q) matching.

The amount of CO delivered into a patient’s alveoli can be determined by the ideal gas law as shown in tire following equation: N = P.V/(Ru.T) (1)

Where: 20 N is the number of moles of the gas (mole) P is the absolute pressure of the gas (joule/m3) V is the volume of the particular gas (m3)

Ru is the universal gas constant, 8.315 (joute/(gmqle. °K) T is the absolute temperature (°K) 25 If we assume atmospheric pressure (101,315 joule/m3) and 20 °C (293 °K) as the temperature and we express the volume in mL ( xlO’6 m3 ) then equation (!) reduces to: 2 2017202586 19 Apr 2017 (2) N = 4.16xl0"5. V (moles)

Equation (2) can be used to calculate the number of moies of gas delivered to a patient’s alveolar volume over a period of tin» when given a specified concentration by using the following equation: 5 NCo= RR·t. Cco-IO-6·4.16xlO'5.Va (3)

Where;

Cco is the concentration of GO (ppm)

Va is the alveolar volume (mL) ER is the respiratory rate in (BPM) 10 t is die time in minutes (mins)

For example if flbe CO dose tor ileus in humans was 250 ppm of CO for one hour (60 minutes), the alveolar volume is 300 mL and the patients respiratory rate is 12 breaths per minute (bpm) then the amount of CO gas in moles delivered to the patients alveoli over that period would be: 15 Nco= 12,60.250, 10 6' 4.16 xlO'5 . 300 = 2,25 x Iff3 (moles)

This can be converted into the mass of drug delivered (Mco) using the gram molecular weight of CO which is 28 as shown in the following equation:

Mco = Nco. 28 = 63 x 10*3 (g) * 63 (mg) (4)

However, although this works for a given set of assumptions, a spontaneous 20 patient’s respiratory rate can vary widely from perhaps 8 to 20 breaths per minute depending on circumstances and the patient’s alveolar volume per breath can also vary significantly from say 200 to 400 mL depending on the metabolic need. These variables can have a dramatic effect on the amount of gaseous drug being delivered to the patient over the same period of time. For instance if the patients respiratory rate 25 was 8 bpm and the alveolar volume was 200 mL, the CO dose delivered to the patients alveoli would have been 27.8 (mg), likewise if the patients respiratory rate was 20 bpm and the alveolar volume was 400 mL, than the dose delivered to the 3 2017202586 19 Apr 2017 15 20 patients alveoli would have been 139.2 (mg) thus representing a five fold difference in the amount of dreg being delivered.

Ibis means, in the example of CO, the quantity of gaseous drug a patient gets as measured in grams could vary substantially depending on the patient’s ventilation 5 pattern. For a dose based on constant concentration and time, the effect of these variables could mean that an individual patient could get significantly higher or lower doses of CO in grams and this could result in either high unsafe levels of earboxyhemag! obin or doses too low to be effective. Although not all die gaseous drug delivered to the alveoli will be taken up by the bodies bloodstream (due to 10 variables such as cardiac output and the diffusion coefficient of the gas) controlling die amount delivered to the alveoli takes away a major source of variability.

In addition, there is a need to administer NO to a patient in a predetermined quantity as described in “Cell-free hemoglobin limits nitric oxide bioavailabllity in sickle-cell disease” Nature Medicine, Volume 8, Number 12, December 2002, pages 1383 ei seq. This paper describes tire use of inhaled NO to react with cell free hemoglobin to form plasma methemaglobin and so reduce the ability of the cell free hemoglobin in theplasma to consume endogenously produced NO (fig, 5, page 1386). The quantity of NO delivered to the patient blood needs to be equivalent to tire amount of cell free hemoglobin that is in the patients plasma. The amount of NO delivered to a sample of sickle cell patients was 80ppm of NO for 1.5 hours. However, them was variability in the amount of methemoglobin produced in individual patients as shown by the error bars on Fig. 4b. So, in a similar way to the CO example, a known quantity of NO needs to be delivered to a patient to provide the desired therapeutic effect and again it is important to remove any variability of

Accordingly, it would be advantageous to have a system and method of introducing pharmaceutical gases (such as carbon monoxide and nitric oxide) that allows for the precise control of a known quantity of the pharmaceutical gas to be 4 2017202586 19 Apr 2017 delivered to the patients alveoli and which is not subject to change based on the patients respiratory patterns.

Summary of the Invention

Accordingly, the present invention relates to a system and method for 5 administering a pharmaceutical gas, such as carbon monoxide aud nitric oxide, that allows a clinician to determine and control the desired quantity of the gas to be delivered to the patient. The method determines the desired quantity of the pharmaceutical gas to be administered to the patient and then administers the desired quantity of the pharmaceutical gas irrespective of the patients respiratory patterns. If the prescription is 10 specified as a total quantity of drag, then the method terminates the administration of the pharmaceutical gas when the desired total quantity has been administered to the patient.

Thus, by the method of the present invention, the amount of the pharmaceutical gas is deEvered to the patient as a known desired quantity and that known desired quantity can be expressed in various unite of measurement, such as, but not limited to, IS fee weight of drag in micrograms (pg), milligrams (mg), grams (g) etc., the moles of drag in nanomoles (nM), micromoles (μΜ), millimoles (mM) moles (M) etc, or fee volume of drag, at a known concentration or partial pressure, in microliters (pL), milliliters (mL), liters (L) etc. Tire desired quantity of the pharmaceutical gas can also be expressed as an amount pear unit of time for a period of time such as mg/hour for 2 20 hours.

The invention also includes a system for administering a pharmaceutical gas, such as carbon monoxide dr nitric oxide, and fee system includes an inlet means that can be connected to fee source of the pharmaceutical gas and deliver the gas to a patient by means of a patient device. That patient device can be any device that actually introduces 25 fee pharmaceutical gas Into fee patient such as a nasal cannula, endotracheal tube, face mask or the like. There is also a gas control system feat controls the introduction of the quantity of a pharmaceutical gas from fee gas source through fee patient device. Again, therefore, the system provides a known quantity of gas to fee patient 5 2017202586 19 Apr 2017

IS

As such, the present invention allows a user to set a desired quantity of gaseous drug to be delivered to a patient’s alveoli and for the system to then deliver that gaseous drug over multiple breaths until the prescribed amount has been delivered. 5 As a further embodiment, the system and method may simply provide an alarm, visual and/or audible, to alert the user when the predetermined total quantity of the pharmaceutical gas has been administered to the patient and not actually terminate that administration. As such, the user is warned that the total predetermined desired quantity administered over the plurality of breaths has now been delivered to the 10 patient so that the user can take the appropriate action, including a closer monitoring of the patient.

These and other features and advantages of 11» present invention will become more readily apparent during the following detailed description taken in conjunction with the drawings herein.

Brief Description of the Drawings FIGS. 1 and 2 are views of a front panel of an apparatus for carrying out the present invention showing different user options; HQ 3 is a schematic view of the present invention used with a spontaneously breathing patient; and 20 FIG. 4 is a schematic view of the present invention used with a patient being breathed by means of a ventilator.

Detailed Description of the Invention

In the following detailed description, CO is used as the pharmaceutical gas but the description can also be valid for NO. Referring now to Mg. 1, there is shown a front 25 view of an apparatus that can be used in carrying out the present invention. As can be 6 2017202586 19 Apr 2017 seen, there Is a front panel 10 that can be a part of the apparatus and on that panel these are input setting knobs and displays which allow the user to set and monitor the amount of CO that is to be delivered to the patient.

The means for determining the desired quantity of CO to be delivered is by 5 means of an input setting knob 12 with the set amount being shown on the setting display 8. The unite shown in Rg. 1 are in milligrams per kilogram that is, the units are measured in a dosage per kilogram of the patient’s ideal body weight. Along with that input, there is a forte input 14 whereby the user can enter the patient’s ideal body weight in kilograms with die amount also displayed on die setting display 8. With those 10 inputs, the use® can set the quantity of the pharmaceutical gas to be administered to the patient in proportion to the size Of die patient and Which induces the patient to patient variability in response to the pharmaceutical gas due to the size of die patient, i.e. a 7 kilogram baby Will not be administeted the same quantity of the pharmaceutical gas as a 80 kilogram adult 15 Tie front panel 10 also has a monitor display 6 which can display total dose of CO (mg) to be delivered (shown at 16) as calculated for multiplying the dosage/kg by the patients ideal body weight in kg.

Once the desired quantity of gaseous drug has been set on the device the system then determines the amount of pharmaceutical gas that is to be delivered in 20 each breath and die amount of time and/or the number of breaths that- it will take to deliver the total desired quantity of drug. The monitor display 6 can also display a running total of the delivered dose of CO (mg) (shown at 17) as it is delivered to the patient so the user can monitor the progress of the treatment This can be updated each breath as more pharmaceutical gas is delivered. 25 As stated, the units illustrated in Fig. 1 are in metric units, however, it can be seen that other unite of mass and volume could be used in carrying out the present invention i.e, ounces and cubic inches and other designs of a front panel can be used as will later be understood. 7 2017202586 19 Apr 2017

Referring to Fig. % there is shown a similar front panel 10 for the apparatus as shown in Hg. 1 but illustrating a different user setting option. The desired quantity of CO to be delivered to die patient is prescribed as a rate of delivery by means of hiput setting knob 13 and is in units of mg/hr of GO to he delivered & this option, the device 5 also allows the time duration (in hours) of treatment to be set by a means of an input setting knob 15. If required, the input setting by input 'Setting knob 15 could be set to continuous where the dose per hour would run continuously until the user changed the setting. With tee input settings, the apparatus can calculate and display the desired quantity of die pharmaceutical gas to be administered to the patient, 10 Also, as in Pig. 1, the front panel 10 also has a monitor display 6 which can display total dose of CO (mg) to be delivered (shown at 16) as calculated by multiplying the dosage/hr by the total time duration (hr.). Once the desired quantity of pharmaceutical gas has been set on the device, the system then determines the amount of pharmaceutical gas to be delivered in each breath and the amount of time and/or the 15 number of breaths that it will take to deliver tire total desired quantity off drug. As before, the monitor display 6 can display a tunning total of the delivered dose of CO (mg) (shown at 17) as it is delivered to the patient so the user can monitor the progress of the treatment This can be updated each breath as more pharmaceutical gas is detivered. 20 As can be appreciated, Pigs. 1 and 2 illustrate two of the many options far setting the desired quantity and duration of pharmaceutical gas therapy. These options are not meant to be exhaustive and there are other setting options described or that can be understood from the detailed descriptions that follow.

Once the desired quantity of gaseous drug has been set on toe device, toe gas 25 control system can then determine the amount of pharmaceutical gas to be delivered in each breath and toe amount of time and/or the number of breaths that it will take to deliver toe desired quantity of pharmaceutical: gas. 8 2017202586 19 Apr 2017

There are a number of different approaches that the gas control system can use to determine the amount per breath and how long to deliver that dose so the desired quantity of pharmaceutical gas is delivered independent of the respiratory pattern of the patient: 5 a) The user can set the quantity of pharmaceutical gas to he delivered during each breath (Mco to*) and the gas control system calculates the number of breaths (ntotbs) which will be required to deliver the total quantity of pharmaceutical gas (Mco) i-e-

Hbreatlis = Mco / Mcota* (5) 10 Once the total number of breaths (Uto&s) required has been determined the value can be displayed on the front panel 12 by means of display 16 to inform the uses: of the number of breaths. b) The user can set the number of breaths (nbreaths) that will administer die total quantity of the pharmaceutical gas and the system calculates the amount per 15 breath (Mco toth) to be delivered.

Mco breath = Mco/ Utofcs (m§) (6)

Once the amount per breath (Mco breath) to be delivered has been determined, the value can be displayed on the front panel 10 to inform the user of the amount. (c) The user could set the time duration for which the treatment is to be 20 delivered over. The amount per breath would then be determined by calculating the quantity per minute and then, by monitoring the patients respiration rate in breaths per minute, the amount of breath can be calculated. This calculation can he repeated after every breath so any changes in the patients respiratory rate does not effect the overall quantity of gaseous drug being delivered. 25 d) If the desired quantity of pharmaceutical gas was entered as a dose per

Kg of the patient’s ideal body weight (pg/kg) along with the patient’s Ideal body 9 2017202586 19Apr2017 weight (Kg) then the amount per breath (MCo breath) can be determined as a function of the patient’s ideal body weight (IBW), the set dose per kilogram (Mkg) and the patient’s monitored respiratory rate (RR.) or combinations thereof;

Mco breath = f (IBW, Mfeg, RR) and the number of breaths can then be 5 calculated as; %-eaths = Mco / Mco breath (?)

Once the amount per breath (Mco wiO and the number of breaths (nbreaths) required to be delivered has been detennined, the values can be displayed on the front panel 10 to inform the user of the amounts the device has selected. 10 e) Instead of the ideal body weight (IBW) of the patient, the height and sex of the patient eould be entered (which is how EBW is determined). f) If the desired quantity of pharmaceutical gas per unit of time is entered into the device, then the device can calculate the quantity per breath to be delivered to the patient bared on the current monitored respiratory breath rate (as determined by 15 the breath trigger sensor). This quantity per breath can be recalculated after every breath when new information on the respiratory rate is available to ensure the quantity per unit of time is maintained even if the patient respiratory breath pattern changes over time. g) There are also other ways of vatyingfhe quantity of pharmaceutical gas 20 delivered per breath to ensure the quantity per unit of time is maintained even if the patients respiratory rate changes. Another example is where the device has two different amounts of delivery per breath, a high amount and a low amount The device chooses which one to use bared on tire calculated quantity per unit of time being delivered over the past number of breaths. If the amount per unit of time is 25 greater than required, it uses the low amount per breath until the situation corrects itself; likewise, if the quantity per unit of time is running low, then the Unit switches to the high amount per breath. 10 2017202586 19 Apr 2017

The device can also have programmed limits which restrict the maximum and minimum values that can he selected for McO breath so that the system doesn’t select inappropriately too high or too low values. These limits can he set to vary based on the patient’s ideal body weight, or other indicator of the patient size arch as the 5 patient’s height, or the respiratory rate of the patient.

The aforesaid information is sufficient for the system of the present invention to deliver the dose to the patient and to determine the amount per breath, time of administration or other parameter in order to commence the administration of CO and to terminate that administration when the user set quantity of the pharmaceutical gas 10 has been delivered to the patient.

Turning now to Hg. 3, there is shown a schematic of a system that can be used to carry out the present invention when the patient is breathing spontaneously. As can be seen, there is a patient device 18 that delivers Ae dosage of the pharmaceutical gas from the gas delivery system 22 to the patient 41 via a gas conducting conduit 19. As 15 indicated, the patient device 18 can be any one of a variety of devices that actually directs the pharmaceutical gas into the patient and may be a nasal cannula, a mask, an endotracheal tube and the like.

With the Fig. 3 embodiment, there is a source of the pharmaceutical gas by means of a gas supply tank 20 containing the pharmaceutical gas generally in a carrier 20 gas. When the pharmaceutical gas is carbon monoxide, for example, As conventional, commercially available carrier gas is air. The supply of carbon monoxide and air is provided in concentrations of 3(8)0 ppm however, concentrations within Ae range of 1000 to 5000 ppm of CO in air are also possible alternatives. In Ae case of NO as Ae pharmaceutical gas, Ae carrier gas is conventionally nitrogen 25 and Ae typical available concentrations range from 100 ppm to 1600 ppm.

Accordingly, from Ae supply tank 20, Aere is a tank pressure gauge 21 and a regulator 23 to bring Ae tank pressure down to Ae working pressure Of Ae gas delivery system 22. The pharmaceutical gas enters Ae gas delivery system 22 through 11 2017202586 19 Apr 2017 an inlet 24 that can provide a ready connection between that delivery system 22 and fte supply tank 20 via a conduit The gas delivery system 22 has a filter 25 to ensure no contaminants can mterfete with the safe operation of the system and a pressure sensor 27 to detect if the supply pressure is adequate and thereafter includes a gas shut 5 off valve 26 as a control of the pharmaceutical gas entering the deliver system 22 and to provide safety control in the event the delivery system 22 is over delivering the pharmaceutical gas to the patient, fir the event of such over delivery, the shut off valve 26 can he immediately closed and an alarm 42 sounded to alert the user that the gas delivery system has been disabled. As such, the shut off valve 26 can be a 10 solenoid operated valve that is operated from signals directed from a central processing unit including a microprocessor.

Downstream from the shut off valve 26 is a flow control system that controls the flow of the pharmaceutical gas to the patient through the patient device 18. hi the embodiment shown, the flow control system comprises a high flow control valve 28 15 and a low control valve 30 and just downstream from the high and low flow control valves 28, 30, respectively, are a high flow orifice 32 and a low flow orifice 34 and the purpose and use of the high and low flow valves 28,30 and the high and low flow orifices 32,34 will be later explained. A gas flow sensor 36 is also located in the flow of pharmaceutical gas to the patient device 18 and, as shown, is downstream from the 20 flow control system, however, the gas flow sensor 36 may alternatively be located upstream of the flow control system.

Next, there is a patient trigger sensor 38. When the patient breathes in during inspiration it creates a small sub atmospheric pressure in the nose or other area where tire patient device 18 is located, and hence in the patient device 18 itself. The patient 25 trigger sensor 38 detects this pressure drop and provides a signal indicative of the start of inspiration of the patient Similarly, when the patient breathes out there is a positive pressure in the patient device 18 and the patient trigger sensor 38 detects that positive pressure and provides a signal indicative of the beginning of expiration. This 12 2017202586 19 Apr 2017 allows the patient trigger sensor 38 to determine not only the respiratory ate of the patient but also the inspiratory and expiratory times.

Finally there is a CPU 40 that communicates with the patient trigger sensor 38, the high and low flow valves 28,30, the gas shut off valve 26 and other components 5 in order to carry out the purpose and intent of the present invention. The CPU 40 may include a processing component such as a microprocessor to carry out all of the solutions to the equations that are used by the gas delivery system 22 to deliver the predetermined quantity of the pharmaceutical gas to a patient. The CPU 40 is connected to tire front panel 10 where the user can enter settings and monitor therapy. 10 The me of the delivery system 22 of toe present invention for spontaneous breathing can now be explained- When the delivery system 22 detects by means of , toe patient trigger sensor 38 toat inspiration has started, there is a signal that is provided to the CPU 40 to deliver a dose of a pharmaceutical gas (Mco breath.) mto toe patient’s inspiratory gas flow, preferably during the first ¥i of the inspiratory cycle. 15 This amount per breath has been determined based on toe desired quantity of pharmaceutical gas toat has heen set on the system and toe calculations made in a) to g) described earlier·.

The actual volume of gas delivered during toe breath depends on the concentration of toe pharmaceutical gas in toe carrier gas that is supplied by toe 20 supply ta-nlr 20. A typical source concentration (Cco) for CO would be 31X30 ppm (range 500 to 5000). The volume of source gas (V<j) per bieato to provide a dose per breath (Mco team ) when toe source of CO is 3000 ppm is given by toe following equation, combining equations 2,3,4 and 6;

Vd = Mco breath- / (28 . Cco 4.16 xl04!) (8) 25 Given that

Mco = 60 x 10-3 (g)

Cco = 3000 (ppm) nbteaihs =600

Then Vd=28.6<xriL·) 13 2017202586 19 Apr 2017

To deliver the volume of source gas per breath (Va), that is, the pharmaceutical gas and the carrier gas, the delivery system 22 Opens a flow control valve, such as high flow valve 28 or low flow valve 30 to allow the gas to flow to the patient until the volume per breath (Va) has been delivered. The presence of the high flow orifice 5 32 and the low flow orifice 36 limits the flow of gas to a fixed set level during the period that the high or low flow valves 28, 30 are open so the delivery system 22 can determine the period of time the high or low flow valves 28, 30 should be open to deliver the volume per breath (Va) required, Also, as another option, the flow can be determined by the gas flow sensor 36 to monitor the gas flow to the patient device 18 10 and thus to the patient and can shut off the appropriate high or low flow control valve 28, 30 when the desired predetermined quantity of pharmaceutical gas dbse has been delivered to the patient.

As can be seen, to provide enough range to cover all the possible doses, the use of multiple flow valves, that is, the high flow valve 28 and the low flow valve 30 15 along with corresponding multiple orifices, high flow orifice 32 and low flow caSfiee 34, can be used in parallel so as to provide high and low rang® of gas flow. For instance, the low flow gas flow through the low flow valve 30 could be set to 1 L/min and the high flow gas flow through the high flow control valve 28 could be set to 6 L/min. The flow range of the particular gas flow valve is selected to ensure that the 20 volume of gas per breath (V<j) can be delivered to the patient in at least ½ the inspiratory time.

As an example, if the patient was breathing at 12 breaths per minute and had an LE ratio of 1:2 then the inspiratory time would be 1.66 seconds and half that Would be 0.83 seconds. 25 The time (t) taken to deliver a Va of 28 mL can be calculated as follows, t = Va . 60 /(Q. 1000) (secs) (9)

When Q (the flow of gas when the high flow valve 28 is open) s 6 L/mins t “ 0.28 (secs) 14 2017202586 19 Apr 2017

That time is therefore well within % file inspiratory time allowed of 0.83 seconds.

He delivery system 22 can also include monitoring and alarm features to alert the user if the delivery system 22 is not working correctly. Those alarm conditions 5 can be determined by the CPU 40 and the alarm 42 activated to alert the riser to the particular feult condition. The alarm 42 can be audible, visual or both and the alarm conditions can be any one or all of the following:

No breath detected

Low source gas pressure 10 Inaccurate delivery of the volume per breath (Va)

Over delivery of the volume per breath (V<0

Under delivery of the volume per breath (V<j)

Under certain conditions, such as when the delivery system 22 is over delivering the pharmaceutical gas, the CPU 40 may signal the gas dint off valve 26 15 and immediately cease any further delivery of the pharmaceutical gas and the alarm 42 also activated.

The use of the alarm 42 can also be an alternative to actually shutting off the supply of toe pharmaceutical gas to a patient when the predetermined desired quantity of pharmaceutical gas has been fully delivered' to the patient In such case, as an 20 alternative to ceasing tire further supply of the pharmaceutical gas to the patient, the delivery system 22 may, by means of the CPU 40, activate the alarm 42 to alert the user that the total predetermined desired quantity of the pharmaceutical gas has been delivered. The user can then determine whether to manually deactivate the delivery system 22 or continue the delivery of the pharmaceutical gas under more watchful 25 control of the patienfs status.

Turning now to Fig. 4, there is shown a schematic view of a gas delivery system 44 used in conjunction with a patient being breathed by a ventilator 46. ha the Kg. 4 15 2017202586 19 Apr 2017 embodiment, again there is a supply tank 20 that includes a conventional gas regulator 23 and pressure gauge 21 to supply the pharmaceutical gas along with the carrier gas to an inlet 24 in the gas delivery system 44. Briefly summarizing the components of the Fig. 4 embodiment, since they are basically the same components as described with 5 respect to the Fig. 3 embodiment, there can be a filter 25 and a pressure sensor 27 in the gas delivery system 44. Again there is a shut off valve 26 to control the overall flow of the pharmaceutical gas through the gas delivery system 44.

The high and low flow control valves 28 and 30 control the flow of the pharmaceutical gas through the gas delivery system 44 and, the high and low flow 10 valves 28, 30 operate as described With respect to the Fig. 3 embodiment with high and low flow orifices 32, 34 located downstream of the flow control valves.

Again there is a gas flow sensor 36 and a patient trigger sensor 66, both of which communicate with the CPU 40. With this embodiment, however, the pharmaceutical gas is carried through an outlet conduit 70 to a patient device 72 that also receives the 15 breathing gas from the ventilator 46. As such, the ventilator 46 delivers a flow of gas through the inspiratory limb 74 and gas is returned to the ventilator 46 through the expiratory limb 76.

The flow of gas from the ventilator 46 is thus supplemented by the flow of pharmaceutical gas from the gas delivery system 44 where that gas is mixed at or 20 proximate to the patient device 72 for introduction into the patient 78. Since all of the pharmaceutical gas is still delivered to the patient over the plurality of breaths, basically the CPU 40 can carry out the same determination of flows and the like as explained with respect to the Fig. 3 embodiment. The main difference between this Fig. 4 embodiment, and that shown in Fig. 3 is that the patient trigger sensor 66 is designed to operate in a 25 way that works with a ventilator 46.

For instance, when the ventilator 46 provides gas flow to a patient during inspiration, it causes a positive pressure in the breathing circuit. The positive pressure is conducted through the outlet conduit 70 and is detected by die patient trigger sensor 66 16 2017202586 19 Apr 2017 and is recognized as the start of inspiration. This is the opposite to the embodiment of Fig. 3 where the patient breathes spontaneously and a negative pressure is generated during inspiration in the patient device 18; this negative pressure is conducted to the patient trigger sensor 38 of Fig. 3 and is recognized as the start of inspiration. As can be 5 appreciated, the patient trigger sensor 38 of Fig. 3 and the patient trigger sensor of Fig. 4 could be the same pressure sensor and the gas delivery system 44 can be set for work with a ventilator or a spontaneously breathing patient.

Those skilled in the art will readily recognize numerous adaptations and modifications which can be made to the pharmaceutical gas delivery system and method 10 of delivering a pharmaceutical gas of the present invention which will result in an improved method and system for introducing a known desired quantity of a pharmaceutical gas into a patient, yet all of which will fall within the scope and spirit of the present invention as defined in the following claims. Accordingly, the invention is to be limited only by the following claims and their equivalents. 17

Claims (30)

1. CLAIMS The claims defining the invention are as follows:

   1. A method of administering carbon monoxide (CO) or nitric oxide (NO) gas to a patient comprising the steps of: determining the desired quantity of CO or NO gas to be administered to a patient; administering the CO or NO gas to a patient so that the desired quantity of CO or NO gas delivered is independent of the respiratory pattern of a patient.
2. 2. The method of claim 1 wherein the step of administering the gas to a patient comprises administering CO or NO in a carrier gas to a patient.
3. 3. The method of claim 1 wherein the step of administering the gas to a patient includes the step of measuring and using the respiratory rate of the patient.
4. 4. The method of claim 1 wherein the step of administering the desired quantity of gas includes the step of determining the volume of gas to be delivered per breath and then delivering that volume for a plurality of breaths until the desired quantity of gas has been delivered.
5. 5. The method of claim 1 wherein the step of administering the desired quantity of gas comprises measuring the gas flow to the patient during a breath and terminating the administration of the gas based upon the measured flow of gas to the patient when the desired amount for that breath has been delivered.
6. 6. The method of claim 2 wherein the step of administering the desired quantity of gas comprises determining the concentration of the CO or NO gas in the carrier gas being administered and calculating the time required at the calculated concentration to administer the desired quantity of the gas for that breath and the step of terminating the administration of the gas comprises terminating the gas when the calculated time has elapsed. .
7. 7. The method of claim 1 wherein the step of determining the desired quantity of gas to be administered to a patient comprises determining the desired quantity in units of mass or units of mass per unit of time.
8. 8. The method of claim 1 wherein the step of determining the desired quantity of gas to be administered to a patient comprises determining the desired quantity in units of moles or moles per unit of time.
9. 9. The method of claim 1 wherein the step of determining the desired quantity of gas to be administered to a patient comprises determining the desired quantity in units of mass per ideal body weight and the patients ideal body weight or in units of mass per unit of time per ideal body weight and the patients ideal body weight.
10. 10. A system for administering carbon monoxide (CO) or nitric oxide (NO) gas to a patient, the system comprising: an inlet means for connecting to a source of CO or NO gas, an outlet means for connecting to a patient device for introducing a gas into the lungs of a patient, ' means for determining the desired quantity of CO or NO gas to be delivered to a patient over a plurality of breaths, a gas control system for delivering the desired quantity of the CO or NO gas independent of the patients respiratory pattern.
11. 11. The system of claim 10 wherein the means for determining the desired quantity of CO or NO gas comprises an input setting control.
12. 12. The system of claim 10 wherein the source of CO or NO gas comprises CO or NO gas at a known concentration in a carrier gas.
13. 13. The system of claim 12 wherein the gas control system includes a central processing unit (CPU) and wherein the CPU controls the amount of gas delivered during the patients breath based upon the concentration of the CO or NO gas in the carrier gas.
14. 14. The system of claim 13 wherein the CPU uses the concentration of CO or NO gas in the carrier gas to deliver the CO or NO gas and carrier gas over a plurality of breaths until the desired quantity of gas has been delivered.
15. 15. The system of claim 10 wherein the gas control system includes a sensor means that determines the volume of gas being delivered per breath of a patient.
16. 16. The system of claim 10 wherein the gas control system includes a flow sensor that determines the gas flow to the patient.
17. 17. The system of claim 10 wherein the gas control system includes a patient trigger sensor that senses the beginning and end of the inspiratory cycle of a patient.
18. 18. The system of claim 10 wherein the gas control system comprises at least one gas flow valve that is operable by the CPU to provide the gas at a known flow for a period of time.
19. 19. The system of claim 18 wherein the gas control system comprises a plurality of gas flow control valves in parallel having different ranges of flow allowed through the gas flow control valves.
20. 20. The system of claim 18 wherein the gas control system further includes an orifice downstream from at least one gas control valve to limit the flow of gas through said at least one gas control valve.
21. 21. The system of claim 10 wherein the means for determining the desired quantity of gas is a setting control in units of mass per unit of time.
22. 22. The system of claim 10 wherein the means for determining the desired quantity of gas is a setting control in units of mass.
23. 23. The system of claim 10 wherein the means for determining the desired quantity of gas is a setting control with units of mass per unit of ideal body weight per unit of time and a setting control for inputting the patients ideal body weight.
24. 24. The system of claim 10 wherein the means for determining the desired quantity of gas is a setting control with units of mass per unit of ideal body weight and a setting control for inputting the patients ideal body weight.
25. 25. The system of claim 10 wherein the means for determining the desired quantity of gas is a setting control with units of mass per unit of time and a setting control for inputting the time duration of the treatment.
26. 26. The system of claim 10 wherein the gas control system includes a patient trigger sensor that senses the beginning of the inspiratory cycle of a spontaneously breathing or ventilated patient.
27. 27. The system of claim 26 wherein the gas control system includes a central processing unit (CPU) and wherein the CPU calculates the quantity of gas to be delivered per breath based on the desired quantity of gas, the concentration of the CO or NO gas in the carrier gas and the respiratory rate of the patient as determined from the patient trigger sensor.
28. 28. The system of claim 26 wherein the gas control system includes a central processing unit (CPU) and wherein the CPU calculates the quantity of gas to be delivered per breath based on the desired quantity of gas, the concentration of the CO or NO gas in the carrier gas, the time duration of the treatment and the respiratory rate of the patient.
29. 29. The system of claim 26 wherein the gas control system delivers the quantity of gas to be delivered per breath in the first half of the inspiratory time when the patient trigger sensor indicates the beginning of the inspiratory cycle.
30. 30. A system for administering carbon monoxide (CO) or nitric oxide (NO) gas to a patient, the system comprising: an inlet means for connecting to a source of CO or NO gas, . an outlet means for connecting to a patient device for introducing gas into the lungs of a patient, mftans for determining the desired quantity of CO or NO gas to be delivered to a patient; a gas control system for delivering the CO or NO gas into a patient over a plurality of breaths; an alarm device, said gas control system activating said alarm when said desired quantity of the CO or NO gas has been delivered to a patient.