DOSIMETRIC SPACER

Abstract: An apparatus for administering a fluid medicament to a patient in a gas for inhalation and for calculating the dosage administered to the patient comprising a holding member (1) for temporarily holding the medicament and gas prior to inhalation, means for introducing a quantity of the medicament into the holding chamber (1), a sensor (4) for detecting the introduction of the medicament into the holding chamber (1), detector means for detecting the rate of flow of gas inhaled by a patient from the holding chamber (1) and calculation means (25, 27, 29, 30, 31) operably connected to the sensor (4) and to the detector means for calculating the amount of medicament received by a patient. The calculating means (25, 27, 29, 30, 31) makes its calculation on the basis of the quantity of medicament released into the holding chamber (1), the volume of the holding chamber (1), the time elapsed from the detection of the introduction of the medicament, and the detected rate of flow of gas inhaled from the holding chamber (1). The calculation being made by assessing the concentration of the medicament in the holding chamber (1) on a time basis during reduction of the said concentration within the holding chamber (1), and by determining the volume of the gas received by the patient during inhalation, and the time elapsed from the detected introduction of medicament to the inhalation by the patient.

Description: DOSIMETRIC SPACER The present invention relates to a method and apparatus for administering a measured dosage of fluid medicament to a patient in a gas for inhalation. Throughout this specification and claims reference is made to a fluid medicament which may be a liquid or a powder m a fluidised form or m any other similar form. Patient-operated multi-dose inhalers (MDI) are known having a mouthpiece through which a patient inhales. The patient must activate the MEI as he begins to inhale so tnat a metered dose of medicament is sprayed into a stream of air as it is sucked tnrougn the mouthpiece Py the patient's inhalation. Unfortunately the above MDI is often operated incorrectly so that much of the dose of medicament is wasted. Tne MDI must be activated or fired just as tne patient begins to inhale so that the medicament is drawn αeep into tne periphery of tne lungs wnere it is most effective. If tne MDI is fixed too lace, most of tne medicament remains in the throat or bronchial tracts without any effect. Elderly patients and children are particularly likely to be unable to co-ordinate the firing cf tne MDI with the start of inhalation. Some MDIs and dry powder inhalers (DPI are available wmcr incluαe sensors hicπ detect wnen a patient is mnalmg ana automatically activate tne MDI Wmlεt tnese MDIs and DPIs wor well n detecting tne commencement of inhalation m adults, elderly patients and children nave difficulty m triggering the firing of the MDI since their inhalation flow rates are too small to be detected. Often, if a child or elderly patient is able to activate the MDI, this only occurs once their inhalation flow rate has increased to near its maximum, and triggering of the MDI therefore only occurs when the lungs of the patient are already half full . MDIs and DPIs have been proposed which have a spacer chamber or holding chamber in conjunction with the MDI or DPI. When the MDI is activated, a dose of medicament is fired from the mnaler at high velocity. If a patient inhales tne dose of medicament directly, then a large proportion of the dose will be impacted at the back of the throat due to the high velocity. Much of the dose does not reach tne lungs where the medicament s intended tc act In some cases, less than fifty percent of the dose of medicament is deposited m tne lungs A particulai problem with direct inhalation of the medicament by children in that tney are often unatle to inhale tne full dose released due to the small volume of their lungs. Tne holding cnamber may be disposed between the MDI and the patient. The medicament is sprayed into the holding chamber where it s held before the patient inhales frorr tne holding chamoer. The spacer cnamber aosorbs tne nig velocity of the medicament fired from tne MDI and acts as a "ouffer" chamoer. Tne patient tnen inhales tne dose at a much lower velocity. Th s car. reduce the amount cf tne medicament impacting on the back of the throat <oγ upwards of eighty percent, and may double the amount deposited in the lungs. Furthermore, the use of a holding chamber means that, provided the medicament has already been fired into the holding chamber, the patient no longer needs to co-ordinate the firing with his inhalation. The above proposal has some disadvantages. Although it iε impossible to guarantee that a given dosage of medicament has actually reached deep into the patient's lungs, it iε desirable to ensure that a dose as accurate as possible is given so that the patient's treatment is fully effective . In the past, a dose of medicament has been sprayed into a holding chamber from which the patient has repeatedly inhaled until the whole of the dose is presumed to have been inhaled. Such a presumption is an inaccurate measurement of dose actually inhaled by the patient. Firstly, as the patient inhales, more air is drawn into the holding chamber to replace the air which is inhaled. Thiε causes a dilution of the medicament within the holding cnamber. Therefore, even when a patient has inhaled two or three timeε, medicament remains within tne holding chamber. Secondly, the medicament sprayed into the holding chamber gradually settles on the walls and base of the noiding chamber over time. This is caused in part by gravity, and m part by static charges on the medicament and on the holding chamber. Therefore, mucn of tne medicament is not delivered to tne patient during inhalation, no matter now many times he inhales. It is an object of the present invention to reduce the above and other disadvantages, and in particular to accurately determine the dose of medicament received by the patient . The scope of the present application is defined m the appended claims. Embodiments of the present invention will now be described by way of example with reference to the drawings m which: Figures 1 and 2 snow a first embodiment of the present inventio , Figure 3 showε now the concentration of the medicament varies over time m graphic form; Figure 4 shows tne variation in dilution factor as tne medicament is inhaled m graphic form, Figure 5 εhows graphically the flow througn tne εenεor; Figures 6 ana 7 show a second embodiment cf the present invention, Figures 8, 9 and 10 show graphic characteristics of the second embodiment; Figures 11 and 12 show a third embodiment of tne present invention, Fiσure 13 show a fourth embodiment of the present invention; Figure 14 snows graphically tne flow of a r or gas detected by the sensor. Figure 15 shows a processor circuit for calculating the dose given to the patient, and Figure 16 shows a further embodiment of the present invention including control system. Referring to Figure 1 a holding chamber 1 includes an inlet 2 through which a liquid medicament passes into the holding chamber from the multi-dose inhaler (MDI) 3. The MDI 3 releases the liquid medicament in a cloud of droplets . A sensor 4 is disposed between the MDI 3 and the holding chamber 1 which detects each actuation of the MDI 3. The sensor 4 also detects the rate at which air or other gas enters the holding chamber 1 via the inlet 2. The holding chamber alεo includes an outlet 5 to which a mouthpiece 6 is attached. A patient inhales from the mouthpiece 6 drawing air or gas laden with medicament from the holding chamber 1. Thiε cauεeε more air or gaε to be drawn into the holding chamber 1 through the inlet 2. The rate of flow of air through the inlet is detected by the sensor 4. A one way valve 7 is disposed between the outlet 5 and the mouthpiece 6 so that the patient can only inhale from the holding chamber 1 but cannot exhale into the holding chamber 1. The patient must remove the mouthpiece 6 from his mouth before exhaling. Referring to Figure 2, a second one-way valve 8 is disposed in the mouthpiece 6 which permits exhaled air to be vented to atmosphere . Once the medicament has been released into the holding chamber, the concentration of the medicament decreaseε, firstly as a result of deposition as the medicament settles on the walls and base of the holding chamber due to gravity and electrostatic forces between the walls of the holding chamber and the medicament. Secondly, the concentration decreases as a result of dilution caused by air entering the holding chamber to replace air inhaled by the patient. Calculations must be carried out in order to determine the dose of medicament which has actually been delivered to the patient. To make theεe calculations, the following information must be known: (1 tne concentration of tne medicament within tne holding chamber 1 as shown i Figure 3. This concentration depends on the number of actuations of t e MDI releasing the medicament into the holding chamber and on the amount of t me between the release of the medicament into the holding cnamber and tne patient inhaling since tne medicament sediments over time; and (n) the dilution factor where the concentration of the medicament m tne holding cnamber 1 decreases each time tne patient inhales since air ci gas not containing medicament enters tne holding chamber 1. Tniε dilution s εhown m Figure 4. From this information, tne dose of medicament received by tne patient is monitored, and an indication s giver, py the apparatus when the desired dose has been administered This indication may be audible or visual. Referring tc Figure 5, tne detected flow pattern through the inlet 2 of the holding chamber 1 is shown. Treatment starts upon firing of the MDI whereafter the inhalation of the patient is detected. The rate of inhalation is detected so that the calculations may be made to determine at what point the desired dose has been given. This point can then be indicated. Calculation of the dose given to the patient shall now be described in connection with the embodiment shown in Figure 2. The patient firstly connects the MDI 3 to the port 2. The MDI 3 iε fired to release a cloud of medicament into the holding chamber 1 past the sensor 4. The sensor , which might be a microphone or a pressure detector, detects the introduction of medicament into the holding chamber 1 and produces a signal . A data processor (not shown) receives the signal from the sensor 4 and starts a clock (not shown) . The patient then puts the mouthpiece 6 to his mouth and inhales. Air and medicament within the holding chamber 1 iε drawn from the holding chamber through the port 5 and the mouthpiece. At the same time, air enters the holding chamber 1 through port 2 to replace the inhaled air, thereby causing dilution. The data processor calculates the amount of medicament delivered to the patient at very frequent intervals, typically every one hundredth of a second. In each of these sampled periods, the concentration of medicament within the holding chamber 1 is calculated tc take account of the deposition of the medicament or. the walls of the hoidinσ chamber 1 overtime, and cf the dilution effect of air entering the holding champer 1 wnicn doeε not carry any medicament . A memory containε a data look-up table which giveε the concentration of medicament in the chamber at a time after the introduction of the medicament based on the deposition rate of the medicament . The memory also contains a data look-up table which gives the concentration of medicament in the chamber following the introduction of a set volume of air. The concentration of medicament within the holding chamber 1 iε therefore calculated at the εampled time. The dose of medicament inhaled is then calculated by multiplying the volume of air sensed by the sensor during the εampled period by the concentration cf medicament within the holding chamber at that εampled period. The doεe calculated during thiε one sample period is then added to the dose calculated in calculations for previous sample periods . Once the cumulative total dose reaches a predetermined level, an indication s made to the patient that the full doεe has been given. This might be indicated by a light or by an audible signal. The patient may require several breaths before the predetermined doεe has been inhaled. The patient is able to exhale between inhalations through the mouthpiece since the one way valve 8 is able to vent the exhaled air to atmoεphere . The microprocessor must also count the number cf actuations or firings cf tne MDI m order to calculate the initial concentration of medicament within the noidmg chamber 1. The calculation apparatus used in th s empodiment is similar to the calculation apparatus described later in this specification in connection with figures 15 and 16. However, in the present embodiment, in addition to the decrease in concentration caused by deposition of the medicament, the dilution must also be taken into account . Referring now to figure 6, an alternative apparatus is shown which operates in conjunction with dry powder inhalers (DPI) . DPI'ε are normally actuated by the patient' ε mspiratory flow. They are not suitable for patients with a very low mspiratory flow since the DPI lε unlikely to oe triggered reliably. Dry powder inhalerε release the medicament m the form of a fine powder which is inhaled by a patient into their lungs. As with conventional MDI ' ε, conventional DPI'ε suffer from the disadvantage that much of a given dose impacts with the bacK of a patient's throat. Referring to Figure 6, a holding chamber 1 includes a first port 9 which is used botn to loaα and empty the holding chamber 1. The holding cnamoer also includeε a piston 10 movable within the cnamber 1 As the piston 10 is drawn back, air or gas is sucked into the holding champer 1 via the first port 9, and air trapped behind the piston escapes through a second port 11. The holding cnamber 1 includes a one way valve 12 which communicates with tne gas cr air loaded w tn medicament only wnen tne piston 10 is pulled fully bacK The one-way valve 12 permits air only to enter the buffer chamber . In use, the piston 10 is pulled back drawing air or gas into the holding chamber 1 through the first port 9. Before reaching the first port 9, the air or gas passes through a dry powder inhaler 13 which releases the medicament into the air or gas, and through a sensor 4. Once the piston 10 has been pulled back fully, it reveals the one-way valve 12. The piston 10 is fired in that position. The patient then removes the DPI 13 and replaces it with a mouthpiece 6 as shown in Figure 7. The patient then inhales from the mouthpiece 6 and air or gas loaded with tne medicament is sucKed from the noldmg cnamber passing tnrough the port 9, through the εenεor 4 and through the mouthpiece 6. The εenεor 4 detectε this airflow aε εhown in Figure 10. Ambient air enterε the buffer chamber 1 through the one-way valve 12 m order to replace the air or gas oemg inhaled. Calculations can again pe made to accurately measure when a given doεe of medicament has been administered Again, it is necessary to κnow the concentration cf tne medicament within tne holding champer 1, as shown m Figure 8, since sedimentation of medicament occurs over time. It is also necesεary to know the dilution factor during inhalation as shown in Figure 9. These can Pe calculated from the output of tne sensor 4 as descnoed m connectior with figure 2. Once the correct dose nas een administered, tmε s indicated. A further embodiment is shown n Figures 11 ana 12 and, in this embodiment the piston 10 returns across the holding chamber 1 as the patient inhales. There is no one-way valve 12 in the holding chamber as in the previous embodiment. During inhalation and, consequently, emptying of the holding chamber 1, the piston is arranged to move only in the direction of emptying the holding chamber 1 to prevent dilution. To permit the patient to exhale, a one¬ way valve 14 is disposed m the mouthpiece 6. Another advantage of this embodiment is that the dilution factor is eliminated, making doεage calculations εimpler, quicker and more accurate. No air enters the noldmg champer 1 to replace tne air or gas being inhaled since the piston moves to replace the inhaled air. Calculation of the dose given to the patient shall now be described m connection with the embodiment shown m Figures 11 and 12. The patient firstly connects tne DPI 13 to the port 9. The piston 10 is pulled back drawing air into the holding chamber 1 via the DPI 13 and the port 9. The sensor 4 , which might be a microphone or a pressure detector, detects this introduction of medicament into the holding chamber 1 and produces a signal . A data processor (not shown) receives the signal from the sensor 4 and starts a clock (not shown) . The patient then removes tne DPI from the port 9 and replaces t with a mouthpiece (Figure 12) . The patient inhales through tne mouthpiece, and the air flows past tne sensor 4. The data processor calculates the amount of medicament delivered tc the patient very frequently, typically every one hundredth of a second. The concentration of medicament within the holding chamber 1 is continuously calculated to take account of the deposition of medicament on the walls of the holding chamber 1 over time. A memory contains a data look-up table which gives the concentration of medicament m the chamber 1 at a time after introduction of the medicament . The doεe of medicament inhaled lε then calculated by multiplying the volume of air sensed by the sensor by the concentration of medicament . The dose calculated during this one nundredth of a second sample period is then added to the αose calculated m calculations for previous εample periodε . Once the cumulative total doεe reacheε a predetermined level, an indication is made to the patient that the full doεe haε been given Thiε might be indicated by a light or by an audible signal. Figure 15 snows a blocκ diagram of the processor εystem including a procesεor 25 powered by a power εupply 34 The sensor 4 sends signals to the processor 25 via an amplifier 32 to indicate wnen tne medicament is being introduced into tne holding cnamper 1, and the rate of inhalation of the patient. The processor 25 calculates tne dose given to tne patient on tne baεis of a program 29, a memory 30 containing look-up data 31, and a clock 27 Once the processor has calculated that tne predetermined dose has oeen given, a εignal lε output via the data output 33 Referring to Figureε 13 and 14, tne wnole system may be controlled by movement of the piston 10. No valves are used, but the mouthpiece includes two inlets, one from atmosphere and the other from the holding chamber 1. The sensor 4 detects when the patient is inhaling and exhaling. The piston 10 is automatically moved forwards when the patient inhales so that the patient inhales the air or gas containing medicament from the holding chamber 1. As with the earlier embodiments, an audible or visual warning can be given when the patient has received the correct dose. In such an embodiment, once the piston has been withdrawn to fill the holding chamber 1 with medicament and air, biassmg means may oe used to Piase tne piston to push tne a r and medicament out of the holding chamber 1, and locking means for fixing the piston. The sensor 4 is a pressure sensor which senses tne commencement of inhalation by a patient, and the microprocessor 25 releases the locking means to enable tne piston to move through the holding chamber 1 m order to dispense sufficient air and medicament to satisfy the mnalation of the patient, before the locking meanε fixes tne piston once the senεor 4 detectε that the patient εtopped inhaling When the patient exhaleε, tne exhaled breath is vented through the one way valve 14 in the mouthpiece The inhalation procesε is repeated until the microprocessor determines that the predetermined dose has oeen administered at wnicr point the patient is warned, ana the locking means permanently fixes tne piston so that no further medicament can be inhaled from the holding champer 1 In a further embodiment, as shown m figure 16, a piston 10 is movable through a holding chamber 1 having a port 9 through which air and medicament is drawn from a DPI as the piston 10 is withdrawn. The piston 10 is withdrawn by a patient pulling a connecting rod 20. The connecting rod 20 is toothed, and a solenoid latch 21 is disposed ust outside the holding chamber 1 which is engageable with the toothed connecting rod 20 to lock the piston 10. An optional spring 22 is diεposed around the connecting rod 20 between the piston 10 and one end of the holding chamber 1 which biases the piston 10 to expel gas and medicament from tne holding chamber 1 Furtnermore, a dose panel 35 is included for indicating the proportion of the prescribed dose which has been administered. This embodiment operates in generally the same way as described above m connection with Figures 11, 12 and 15 m that the dose given to tne patient is continuously monitored. Tne processor 25 useε the εignal from the sensor 4, a clock signal from a CIOCK 27, data on predetermined dose and data 31 on now the concentration varies with time m the form of a look-up table. As the calculated doεe given tc the patient increases, LEDs on the dose panel 35 are illuminated corresponding tc the proportion of the predetermined dose given, in this case a new LED is illuminated on each of 25%, 50%, 75% and 100%. Furtnei , when tne full predetermined dose has een administered, tne microproceεsor 25 drives tne solenoid latch 21 to engage with the toothed connecting rod 20 to lock the piston 1 This prevents any further medicament being delivered to the patient . The microprocessor system also includes a compliance data memory 36 for recording the date, time and dose delivered which can subsequently be analyzed by a doctor. Reference has been made above to look up tables which give data on how concentration of medicament decreases in time, and how concentration of medicament decreases by dilution caused by inhalation of known volumes. The data in the look-up tables must be gathered by experiment. For example, when the data for decrease m concentration of medicament w th time is gatnered, a known amount of medicament is introduced into the holding chamber, and tne air in the holding chamber 1 is then expelled after a time into a filter paper. The expelled medicament is then weighed. This experiment lε repeated for different time periods to establish the necessary data. Tne variation cf concentration with time profile is likely to be different for different medicaments. Therefore the apparatuε must have the correct profile programmed m. The data cf decrease m concentration of medicament with dilution is collected py introducing a known amount of medicament into the holding chamber, diluting the medicament by replacing some of tne air, and tnen expelling the air and medicament into a filter paper. A profile car. then pe created. In general, tne noldmg cnamper 1 would typically be of tne order of 100-500 ml in volume, and the sensor 4 might be of the pressure type, such as a pneumatic, or of the turbulence-detecting type such aε a microphone.

Claims: CLAIMS 1. Apparatus for administering a fluid medicament to a patient in a gas for inhalation and for calculating the dosage administered to the patient comprising a holding chamber for temporarily holding the medicament and gas prior to inhalation means for introducing a quantity of the medicament into the holding chamber, a sensor for sensing the introduction of the medicament into the holding chamber detector means for detecting the rate of flow of gaε inhaled by a patient from the holding chamber and calculation meanε operably connected to the sensor and to the detector means for calculating the amount of medicament received by a patient on the basis of . the preset quantity of medicament released into the holding chamber, of tne preset volume of the holding chamber, the time elapsed from the sensing of the introduction of the medicament, and of the detected rate of flow of gas inhaled from the holding chamber, the calculation oe g made by assessing tne concentration of the medicament tne noldmg chamber on a time basis during reduction cf tne said concentration within tne holding cnamber due at least m part tc deposition of the medicament within the holding cnamper, and by determining the volume of the gas received by the patient during inhalation, and the time elapsed from the sensed introduction of medicament to the inhalation by the patient . 2. Apparatus for administering a fluid medicament to a patient in a gas for inhalation and for calculating the dosage administered to the patient comprising a holding chamber for holding the medicament and gas prior to inhalation meanε for introducing a quantity of the medicament into the holding chamber, a εensor for sensing introduction of the medicament into the holding chamber detector means for detecting the rate of flow of gas inhaled by a patient from the holding chamber, and calculation means operably connected to tne εensor and tc the detector meanε for calculating the amount cf medicament received Py a patient, tne calculation means including a timing means for indicating the time elapsed since the senεor senseε the introduction of medicament into the holding chamber; means for supplying the initial concentration of medicament in the holding chamber immediately after tne introduction of medicament therein means for determmmα the concentration cf medicament m the holding chamber during inhalation by the patient, the concentration of medicament reducing with time due at least m part to deposition of the medicament withm the holding chamber, the determination being made on the basis of the initial concentration supplied by the means for supplying initial concentration, and of the time elapsed since the sensor sensed the introduction of medicament into the holding chamber, and means for determining the amount of medicament received by the patient by calculating the volume of gas inhaled by the patient from the holding chamber by integrating the rate of flow detected by the detector meanε, and by multiplying the calculated volume of gaε by the concentration of medicament the holding chamber at that time determined by the means for determining the concentration of medicament. 3. Apparatuε according to claim 1 or 2 including a memory for storing a look-up chart snowing the decrease of concentration of the medicament in tne holding cnamber over time . 4. Apparatus according to claim 3 wherein the means for determining the concentration of medicament in the holding champer during inhalation makes tne said determination also on the basis of tne IOOK-UP chart in the memory 5 Apparatus according to any cf claims 2, 3 or 4 wnereir the means for supplying initial concentration of medicament in the holding chamber immediately after the introduction of medicament determines the said initial concentration on the basis of a preset quantity of medicament introduction into the holding chamber, and of a preset volume of the holding chamber. 6. Apparatus according to any preceding claim wherein the holding chamber includes an inlet for permitting entry of gas into the holding chamber as gas is drawn out of the holding chamber by inhalation thereby causing a reduction of the concentration of medicament within the holding chamber by dilution. 7. Apparatus according to claim 6 wherein the means for determining the concentration of medicament in the holding chamber during inhalation makes the said determination also on the basis of the volume of gas previously inhaled by the patient . 8. Apparatus according to claim 6 or 7 including a memory for storing a look-up chart showing the decrease of concentration of the medicament in the holding chamber with the volume of air inhaled. 9. Apparatus according to any of claims 1-5 wherein the holding chamber includes a piston for reducing the volume cf gaε m the holding chamber as gas is inhaled, thereby preventing dilution 10. Apparatus according to claim 9 including means for locking the piston. 11 Apparatus according to claim 9 or 10 wherein the piston is movable within the holding chamber for drawing gaε and medicament into the holding chamber. 12. Apparatus according to any preceding claim including a port in the holding chamber through which a quantity of medicament is introduced into the holding chamber by said releasing means, ana through which gas lε inhaled by a patient . 13 Apparatus according to any of claims 10-12 wherein the meanε for locking the piεton lockε the piston upon administration of tne measured dose 14 Apparatuε according to claim 1 including indication meanε for indicating that the meaεured dosage has been administered. 15 Apparatus according to any preceding claim wherein the medicament is a cloud of liquid droplets 16 Apparatus according to any preceding claim wherein tne medicament is a cloud of drv powder particles 17 Apparatus according to any preceding claim wherein the holding chamber includes a port through which the gas disposed the chamber is inhaled, and through which the medicament is released into the holding chamber. 18. Apparatus according to any preceding claim wherein the sensor for sensing introduction of medicament into the holding chamber and the detector means for detecting the rate of flow of gas inhaled by a patient from the holding chamber are constituted by a single sensor. 19 Apparatus according to claim 18 wnerem tne single sensor is dispoεed m tne port of the noldmg chamber 20 Apparatus for administering a fluid medicament to a patient n a gaε for inhalation and for calculating tne ooεage administered to the patient comprising a holding cnamber for temporarily noldmg tne medicament and gaε prior to mnalation means for introducing a quantity of tne medicament into the holding chamber, a sensor for sensing the introduction of tne medicament into the holding chamber detector means for detecting tne rate cf flow of gas inhaled by a patient from tne holding chamber ana calculation means operaoly connected to tne sensor ana tc tne detector means for calculating tne amount cf medicament received by a patient on the basis of. the preset quantity of medicament released into the holding chamber, of the preset volume of the holding chamber, the time elapsed from the sensing of the introduction of the medicament, of the detected rate of flow of gas inhaled from the holding chamber, the calculation being made by assessing the concentration of the medicament in the holding chamber on the basiε of the detected inhaled volume during reduction of the said concentration within the holding chamber due at leaεt m part to dilution cf the medicament with the holding chamber, and by determining the volume of the gaε received by tne patient during mnalation 21. Apparatus for administering a fluid medicament to a patient m a gas for inhalation and for calculating the dosage administered to tne patient comprising a holding champer for noldmg the medicament and gas prior to inhalation means for introducing a quantity of the medicament into the holding cnamber, a sensor for sensing introduction of the medicament into the holding cnamber detector means for detecting tne rate of flow of gas inhaled by a patient from tne noldmg cnamber, and calculation means operably connected to the sensor ana to tne detector means for calculating tne amount of medicament received Py a patient, tne calculation meanε including a timing means for indicating the time elapsed since the sensor senses the introduction of medicament into the holding chamber; meanε for supplying the initial concentration of medicament in the holding chamber immediately after the introduction of medicament therein means for determining the concentration of medicament in the holding chamber during inhalation by the patient, the concentration of medicament reducing with the volume of gaε inhaled due at leaεt m part to dilution of the medicament withm the holding chamber, the determination being made on the basis of the initial concentration supplied by the means for supplying initial concentration, and of the volume of gas inhaled, calculated from the rate of flow of gas detected by the detector since the sensor sensed the introduction of medicament into the holding chamber, and means for determining the amount of medicament received by the patient by calculating the volume of gaε inhaled by the patient from tne holding chambe by integrating the rate of flow detected by the detector meanε, and by multiplying the calculated volume of gaε by the concentration of medicament in the holding chamber at that time determined by the meanε for determining the concentration of medicament 22 A method for administering a measured dosage cf a fluid medicament to a patient in a gas for inhalation using an apparatus comprising: a holding chamber for holding the medicament and gas prior to inhalation; meanε for introducing a quantity of medicament into the holding chamber; a εensor for sensing the introduction of medicament into the holding chamber; detector means for detecting the rate of flow of gas inhaled by a patient from the holding chamber, and calculation means operably connected to tne sensor and to the detector means for calculating the amount of medicament received by a patient, the method comprising: sensing the introduction of medicament into the holding chamber, the sensing being made by the sensor; monitoring the time elapsed since the introduction of medicament is sensed, tne monitoring being made by the calculation means; supplying the value of the initial concentration of medicament m the holding cnamber; determining the concentration of medicament m the holding chamber during inhalation by the patient, the concentration of medicament reducing with time due at least part to deposition of the medicament withm the holding chamber, the determination being made on the basis cf the supplied initial concentration and of the time elapsed since the sensor senses the introduction of medicament into the holding chamber, and determining the amount of medicament received by the patient by calculating the volume of gaε inhaled by the patient from the holding chamber by integration of the rate of flow detected by the detector meanε, and by multiplying the calculated volume of gas by the determined concentration of medicament m the holding chamber at that time . 23. A method of administering a fluid medicament to a patient in a gas for inhalation and for calculating the dosage administered to the patient comprising sensing the introduction of a quantity of medicament into a holding chamber; detecting the rate of flow of gas inhaled by a patient from the holding chamber; monitoring the time elapsed from the sensing of the introduction of the quantity of medicament into the holding chamber determining tne concentration cf medicament in the holding chamber during inhalation by the patient, the concentration of medicament reducing with time due at least m part to deposition of the medicament withm the holding chamber, the determination being made on the basis of the predetermined initial concentration of medicament with the holding champer immediately after the introduction of medicament therein, and on the basiε of the monitored time elapsed since the sensing of the introduction of medicament ; and calculating the amount of medicament received by the patient by calculating the volume of gas inhaled by the patient from the holding chamber by integrating the detected rate of flow, and by multiplying the calculated volume of gas inhaled by the determined concentration of medicament in the holding chamber.

Inventors: DENYER JONATHAN STANLEY HAROLD, NIKANDER KURT VERNER HOLGER, DENYER, JONATHAN, STANLEY, HAROLD, NIKANDER, KURT, VERNER, HOLGER
Applicants: AID MEDIC LTD, ASTRA AB, DENYER JONATHAN STANLEY HAROLD, NIKANDER KURT VERNER HOLGER, AB ASTRA, DENYER, JONATHAN, STANLEY, HAROLD, MEDIC-AID LIMITED, NIKANDER, KURT, VERNER, HOLGER
Application year: 1995
Main classification: A61M15
IPC codes: A61M11, A61M15, A61M16