CA2126331C - Intelligent inhaler providing feedback to both patient and medical professional - Google Patents
Intelligent inhaler providing feedback to both patient and medical professionalInfo
- Publication number
- CA2126331C CA2126331C CA002126331A CA2126331A CA2126331C CA 2126331 C CA2126331 C CA 2126331C CA 002126331 A CA002126331 A CA 002126331A CA 2126331 A CA2126331 A CA 2126331A CA 2126331 C CA2126331 C CA 2126331C
- Authority
- CA
- Canada
- Prior art keywords
- patient
- delivery
- data
- medication
- mouthpiece
- Prior art date
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
- A61B8/0875—Detecting organic movements or changes, e.g. tumours, cysts, swellings for diagnosis of bone
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M15/00—Inhalators
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M15/00—Inhalators
- A61M15/0065—Inhalators with dosage or measuring devices
- A61M15/0068—Indicating or counting the number of dispensed doses or of remaining doses
- A61M15/008—Electronic counters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61J—CONTAINERS SPECIALLY ADAPTED FOR MEDICAL OR PHARMACEUTICAL PURPOSES; DEVICES OR METHODS SPECIALLY ADAPTED FOR BRINGING PHARMACEUTICAL PRODUCTS INTO PARTICULAR PHYSICAL OR ADMINISTERING FORMS; DEVICES FOR ADMINISTERING FOOD OR MEDICINES ORALLY; BABY COMFORTERS; DEVICES FOR RECEIVING SPITTLE
- A61J7/00—Devices for administering medicines orally, e.g. spoons; Pill counting devices; Arrangements for time indication or reminder for taking medicine
- A61J7/04—Arrangements for time indication or reminder for taking medicine, e.g. programmed dispensers
- A61J7/0409—Arrangements for time indication or reminder for taking medicine, e.g. programmed dispensers with timers
- A61J7/0481—Arrangements for time indication or reminder for taking medicine, e.g. programmed dispensers with timers working on a schedule basis
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M15/00—Inhalators
- A61M15/0065—Inhalators with dosage or measuring devices
- A61M15/0068—Indicating or counting the number of dispensed doses or of remaining doses
- A61M15/0083—Timers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M15/00—Inhalators
- A61M15/009—Inhalators using medicine packages with incorporated spraying means, e.g. aerosol cans
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
- A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
- A61M2016/0039—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the inspiratory circuit
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
- A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
- A61M2016/0042—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the expiratory circuit
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/35—Communication
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/35—Communication
- A61M2205/3546—Range
- A61M2205/3561—Range local, e.g. within room or hospital
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/50—General characteristics of the apparatus with microprocessors or computers
- A61M2205/52—General characteristics of the apparatus with microprocessors or computers with memories providing a history of measured variating parameters of apparatus or patient
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02A—TECHNOLOGIES FOR ADAPTATION TO CLIMATE CHANGE
- Y02A90/00—Technologies having an indirect contribution to adaptation to climate change
- Y02A90/10—Information and communication technologies [ICT] supporting adaptation to climate change, e.g. for weather forecasting or climate simulation
Abstract
An inhaler device ( 100) for aerosol delivery of medication employs a microprocessor (220) and electronic sensors (230) for measuring parameters indicative of a patient's inhalation of airborne medication. The sensors produce output signals representative of parameters which determine the proper delivery of medication to receptor sites in the patient's lungs, such as, the rate of flow of air through the inhaler device to the patient's lungs, the duration of inspiration of the medication, and the volume of medication inhaled. The microprocessor is responsive to the output signals of the sensors and stores a record of inhalation events which can be retrieved remotely or by connecting the microprocessor to a display terminal (108). The microprocessor makes possible a display of data indicative of the delivery of medication for each inhalation event over a course of treatment, thus providing compliance feedback to both the patient and the medical professional.
Description
WO 93/128~3 PC~r/US92/10804 ' .~-,, 2126331 .
I~TEI.I,I~;E~T TN~ r~C~ tNG ~ nRa~:R TO BOT~I
PAT:~:BNT A~ DICAI, P~OF~8~3IO~
R~ JND OF ~ l~-V151~
Field of Invention The ~ield of the pres~nt in~ention relates generally to an inhaler device for aerosol delivery of medicine. ~ore particularly, the present inven-tion is directed to a de~ice for improving medica-tion compliance by providing feedback regardin~
correct and consistent usage of ~dicine inhalers tv a patient and/or professional such as a physician~ :
pharmacist, or therapist. The present invention is fur~her directed to a ~ethod by which such professional~ can track the usage of medicine inhalers between ~isits, and modify medicinal therapy bA~~~ on downlo~ of this information to - a clinical workstation allowing display and analysis.
The Prior Ar~
Getting patients to correctly use medicine inhalers is a major problem. Estimates indicate as few as one quarter of patients using inhalers do so correctly ~Orehek, J., "Patient Error in Use of Bronchodilator Metered Aerosols," Br~t~sh MQ~;Ca1 Journal, 1:76 (1976); Paterson, I.C. and G.K. Crompton, "Use of Pressurized Aerosols by Asthmatic Patients," British Medical Journal, 1:7677 (1976); Saunders, K.B., "Misuse of Inhaled Broncho-dilator Agents," British Medical Jou~nal, WO93~12~23 P~T/US9~/10804 t~
I~TEI.I,I~;E~T TN~ r~C~ tNG ~ nRa~:R TO BOT~I
PAT:~:BNT A~ DICAI, P~OF~8~3IO~
R~ JND OF ~ l~-V151~
Field of Invention The ~ield of the pres~nt in~ention relates generally to an inhaler device for aerosol delivery of medicine. ~ore particularly, the present inven-tion is directed to a de~ice for improving medica-tion compliance by providing feedback regardin~
correct and consistent usage of ~dicine inhalers tv a patient and/or professional such as a physician~ :
pharmacist, or therapist. The present invention is fur~her directed to a ~ethod by which such professional~ can track the usage of medicine inhalers between ~isits, and modify medicinal therapy bA~~~ on downlo~ of this information to - a clinical workstation allowing display and analysis.
The Prior Ar~
Getting patients to correctly use medicine inhalers is a major problem. Estimates indicate as few as one quarter of patients using inhalers do so correctly ~Orehek, J., "Patient Error in Use of Bronchodilator Metered Aerosols," Br~t~sh MQ~;Ca1 Journal, 1:76 (1976); Paterson, I.C. and G.K. Crompton, "Use of Pressurized Aerosols by Asthmatic Patients," British Medical Journal, 1:7677 (1976); Saunders, K.B., "Misuse of Inhaled Broncho-dilator Agents," British Medical Jou~nal, WO93~12~23 P~T/US9~/10804 t~
2 ~2 633 ~ - 2 -1:1037-1038 (196S); Shim, C., and ~.H. Williams, "The Adequacy of Inhalation of Aerosol from Canister Nebulizers;" ~he ~merican Jourr~l of MPAic~ne, 69:~91-894 (1980)]. In addition to ~ çce~e~ry patient morbidity and mortality, an unfortunate consequence is that patients may stop taking their ~edications because they are not ~e~ins any or enough bene~it. Conversely, having ~ailed to obtain expected benefits through prescribed usage, 80~e patients will overuse medications and thereby increa~e the risk of side sffects cau~ed by higher than nor~al do~ag~ (ç~g~, fungal inf~ction~ in the mouth and throat or nervou~ ~y~tem ~f~ct~ cAltge~ by medication absor~ed in the ga3trointestinal tract).
These problems are e~p*ci~ly ~vident in the case of aerosol phar~aceutical~ delivered by hand-held inhaler~. Hand-held metered dose inhalQr~
(~DI~) are a preferrad method of tr~atment for common respiratory ail~ents, ~incR the deliv~ry of ~edic~tion diractly to i~ int~nA~ ~ite of Act~on in the lung~ allows a reduction in dosage by an order of magnitude or gr~atar. However, certain of these com~o~ , such ~8 anti-inflammatory cortico-steroid~, may take many weeks of admini~tration before having a signific~nt effect. Moreover, the inhalation and breath-holding ~aneuver requirRd for ~ cçq-~ful deliv~ry of aero~ol to the lowar airway~
is counterintuitive and poorly under~tood by mo6t patients. Thus, a patient may be compliant in u~ing tha madication when pr~scribed, ~ut un~cc~ful in using it in the corract ~anner.
When therapeutic results are not ob~Aine~, it may not be evident to the phy~ician which step~) in W093/12823 PCT/US92/1~
f 2126~3~ :
the proce~ are the problem. Relevant que~tions, for example, are Nwas the medication not taken at all?", "was it taken at the corr~ct interYal~ and in ~LO~eX relationRhip to expo~ure to ~llergens or other irritants?", and "was the inh~lation perfor~ed correctly?".
Another problem the physician faces i~ how to interpret variability in therape~tic respon~e. I~
the v~riability due to ~o~e fundamental ~nqe in the pati~nt'~ condition (e~, the pati~nt now ha~ a~
lou ~Lade upper re~piratory infection) or is it cau~ed by difference~ in deliverQd medicat~on dosage?
~epo~ition of aerosol ~edication ~n the human lung i5 primarily deter~ined by ~wo pL~_Eere~, inertial impaction and gra~itational ~edimentat~on~
Impaction of aero~ol~ in the lung~ occurs pri~arily at airway bifurcations, and has been ~hown in scintigraphic studiQs to incre~ a~ ~ function of flow rate. Sedi~entation in~olve~ gravitational settling of a~roaol particl~s on the ~irways and al~eoli. 11~ , S.P., PaYi~, D., Garland, N. and S.W. Clarke, "Effect~ of Various ~h~lation Mo~c on the D~po~ition of Radioactive Pres~urized Aerosols,"
EU~ r J. Re8D;rAtOnr D~S. . S~D1e~ 119, 63: 57-65, ( 1982 ) demonstrated that the percentage of aero~ol depo~ited in the lungs of patients wa6 signifi~antly greater when the pat~ ents held their breath for ten E~onAC than when br~ath holding was only four -ecQnA~.
Thus, for aerosol to be ~o~o~ted in the lower airway~, the primary site of action for common medi-cations such as corticosteroids and bronch~ ators, PCT/~S92/10804 21263~
the patient must coordinate the relea~e of medica- ~
tion, inhale slowly enough to minimize 106s of ~edi-cine through impaction in the throat and upper air-ways, and br~ath hold long ~no~l~h to allow time for small particle~ to settle. In practice, this mean~
an inhalation rate below one liter per ~econd, and a breath hold for up to ten seconds.
A hand-held (e.a., metered or unit-do~e~
inhaler currently is a pa~sive device that provides n no information regarding the medication actually delivered. Orehek et ~ ound that only five of twenty a~thmatic patients correctly i~halQd. "The other 15 patients fail~d either to in~pire deeply or hold their breath a~terwards, or both, or poorly coordinated the puff and the in~piration.U Orehek et al., "Patient ~l~G~ in Usa of Br~nchs~ilator Metered Aero~ol~,~ Rr~t~h ~ l Journ~ 76, (1976).
For example, it has ~en found that in a group of 30 acute a~th~atic patient~ direc~ly ob~arv~d in a clinical setting, 47% (14 patients) used incorrect ique. Tha fourt~en pati~nts wi~h in~equate t~hniqus were then trained. Ten of them were ret~ted after an interval of one day to one month.
Five of the patient~ ~re ~till u~ing th~ir inhalers eo~.eetly; the other five had revQrted to their original ineorreet tee~iques. Shim, C., and M.H. Williams, "The Adequacy of Tnh~ lation of Aelo~ol from Canister Nebulizers,~ The Ameri~
Journal of ~edicine. 69:891-894 (1980).
The device and appro~eh deser~ed her~in would hav~ proYided im~ediate feedback to the patients that they had reYerted to incorrect uae o~ their W~3/12823 PCT~US92/10804 inhalers, and provided them with pecific ~~ nc~
as to what corrective action was requir~d. Thus, retraining would not have had to wait until their next ~isit to the clinic.
The present approach al~o fo ters the d~livery of a uniform do~e to the target ~ite3 of th~
patient'~ lungs upon each inhaler usage with the expectation of consi~tent therapeutic re~ponse.
Thu~, if the patient's ~ympto~s or condition changes, the physici~n can evaluate the change with r~ n~hle ~surance ~hat the difference i5 not simply due to a variation in ~edication do ~ge. By ~ak~ng data regardinq the patient's inhal~r use during the entire period betw~en clinic Vi8it8 available to the physician, therapy can be ~anaged on a more informed basis.
It ha~ been observed that, ~The lung pre~ents a significant barr~er to the ponetr~tion of drug particl~s of a size s~all ~ h to ~aximize thera-peutic efficacy." Padfield, J.~ Principl~ ofDrug Delivery to the Respiratory Tr~ctH, ~g D~livery to the Resu~r~tory Tr~Ct~ ~n~ton, D., and Jones, T., Qd., Horwood, Lundon (1987).
Padfield conclud~ "The design of delivery ~y~tem for admini~ter~ng drug~ to the lung can ha~e as much, or more, impact as the choice of drug." (i~-) Previous attempts to improve the ef~ectiven~ss of aero~ol medicine inhalers include a number of - device~ including ~ra~rs, aerosol holding chambQrs, flow-activated triggering me~h~n;cms, and dry powder generators.
The problem of medicine ~Ppocition in the mouth and throat can be alleviated in ~ome caaes by the W093/12823 PCr/US92/108~
2~26331 t~
use of a tube spacer, an extension tube inserted between the metered unit-do~e inhaler and he patient'~ ~outh. This pro~-e~ re ~till require~
coordinated patient action and in itself provides no f~e~h~k to the patient as to the Sl1rCePF or f~ilure o~ the overall sffort.
Another approach to improving NDI u~age i5 the use of chambers or reservoirs into whieh the aerosol ~ eh~rged prior to inhalation. Such device~
reduee the need for coordination of actuation and start of inhalation. A widely used device i~
described in Sackner, et. al., U.S. Patent No.
4,484,577, 1984. Thi~ device al~o provides an audible whi~tl~ when the in~piration rate i~ abov~ a fixed level. Th~ dev~ee f~ils to addrQss inter-patient variations in correct inhalation patterns, a~ well as the br~th-holding ~taqe. A co~mon draw-baek of all ehamber deviees i8 their bulk. Such deviees may not fit eonveniently in a pocket or pur~e, and many patiQnt~ are unwilling to u~e ~uch large devices due to ~elf c- ~~io~r ~ r~ . The proce~ in accorA~nee with the pre~ent invention ean be u~ed irre~peetive of whether a tube spaeer or a reservoir is u~ed.
Conventional ~y~tems al80 include ~everal inhaler deviees wh~ch a~dL~-- the eoordinati~n problem by incorporating a ~ean~ of trigger~ng the medication relea~e by the start of inhalation. Such devices have bean described by Wass, U.S. Patent No. D
4,664,107 1987, ~nd Johnson et. ~1., U.S. P~tent 4,803,978 1989. ~har.r, U.S. Patent 4,739,754, 1988 de~cribes a ~Suction Resistant Inhaler" whose design fosters a deep inhalation by the patient.
WO93~12823 Other conventional devices have incorporated electroomech~nical components in order to record the timing and date of usage for revi~w by a healthcare professional. Spector, et. al., "Compliance of Patients with Asthma with ~n Experimental AerQsoll2ed Medicatlon: Implications for Controlled Clinical Trials, n Jou~nal of Aller~y & Clini~
T~mlln~logy~ 77:6~-70 (1986) discloses the u~e of a nebulizer chronolog to I L 'OL~ the patient~ u~age of MDIs between clinic visits. Thi~ incorporate~
device for r~cording the time and datQ of each canister actuation for later review by physicians conducting r~-r-~ch on pattern~ of patient compliance. Thi deYice lacks the ~p~hility for lS ob~Ai~ any information regarding the inspiratory maneuver itself. Furthermore, since the intention of the ~tudy wa~ to record patient~' MDI usage patterns w~thout their knowl~dge, the device not provide any fe~Ah~k to the patl~nt~ regarding proper inhalation ~e~hnique.
S ~ilar de~ice~ are de w ribed by ~and et. ~1., - U.5. Patent 4,817,822, 1989, and ~çr~ertine, U.S.
Patent 5,020,527, 1991. The Rand device incorpo-rates a mechAn;cal rachet wheel and driving member 25 to drive an indicator of the number of actuations of an aero~ol cani~ter. The~ r~rtine device provides a timer and a counter for tr~ckin~ the number of and time between actuations.
In tha aforem~ntioned d~vice~ thQ time cour~e of air flow is not measured, nor is it comparad to the desired pattern for the ~pQC~fiC patiQnt a8 may be d~termined by a healthcare profe~sional. Thus, the~e devices addre6s only the a~pect of compliance WO~3~12823 PCT/US92~1~8~
- 8 - ;
relating to if and when the medicine was used. In order to A~.F~ whether an aerosol medication has been used effectively, it i8 n~cecr~ry to further deter~ine infor~ation regarding ~he pat~ent's coordination of actuation and inspiration, Yolu~e and flow rate of inspiration, and post-inspiratory breath holding.
In ~ummary, con~entional devices fail to adequately addrec~ ~he need for immediate patisnt feedback regarding multiple ~teps in the corr~ct u~e of inhaler~. The~e devices are al~o ~nAAequate in providing infor~ation to both patient and healthoare professional reqarding the critical factor~ which determine the sllcce~n of m~dicine delivery, including coordination of inhalation w~th actuation, inhalation flow r~te and duration of br~ath holding.
What i8 neeAe~ i8 a hand-held inhaler devlce which can monitor the complete time coursQ of airflow during ~n inhalation, and ~h~ pO~CB~a8 the r~r~hility to guide the pati~nt in it~ correct us~ge before, during, and after u~e~ What is al~o n~e~e~ i8 ~u~h an inhaler whose functions include the capacity to ~eCULd relevant information about the timing and nature of itR use for ~ubs~qu~nt review by a healthcare professional.
SUM~Y OF ~ V ~ ON
The pre~ent device detects how much air i8 inhaled through the inhaler with what time course (including such derived measurements as how much volume is inspired within the bounds of a gi~en flow range) as well as certain event such as the triggering of the release of aerosol. The system WO93~12823 PCT/US~2/10804 2126~
can be set up to co~pare the re~ultant time course to either (a) a st~nd~rd target envelope (e.q., one or more of flow, volu~e, and time) for that ~edica-tion or (b) a specific target ~nvelope for that particular patient programmed into the intelligent inhal~tion device by a healthc~re professional.
RAre~ on ~he ~p~ri~on, the ~uccess or failure o~
effectiYe inhaler actuation and aerosol inspiration can be signaled to the patient (e.a., vi ually or through sound) and may be ~e_o~ed with a t~me and date stamp for later ~co~ n~ and evaluation by a suitable healthcar~-profe~sional. ~n a preferred emb~di~ent of the i~vention, the device would al~o the ability to signal ~he patisnt to continue post-in6piratory ~reath-holdin~, and record the end o~ br~ath holding ~or U8e ~n interpret~ng the ~ ce~ of medication delivery.
In addition, immediate feedback can be ~upplied to the patient as to the specifie nature of any mistake~ made. For example, a ~ ge miqht bs given that the patient's ~h~lAtion was too rapid.
In a preferred embodiment of the invention suf f icient memory is provided to ~tore data from a large number of inhalation6. Thi8 aUtomatQd ~eCG~d may be u~ed in conjunction with a manual log kept by the patient (e.a., what,e~ent, such as eYro~re to an allergen, cau~ed the need to administer the medi-cation) or in a ~emi-automated fashion by h~ving the - patient or att~n~ant e~C9~9 event-related infor-mation into thQ ~nhaler device memory. An example of the latter would be the pr~ssing o~ a button in a certain pattern that would be ~-oc;ated w~th a ,. . : .
PCr~US92/10804 2~26331 specific event. This event information could be stored together with a ti~e and date ~;tamp. ~.
In an alternate ~ho~ iment of the invention, the inhaler device would po~er~ the capability to 5 signal the patient at the times ~or which ~ts use has b~aen prescribed.. Thi ~ ~ignal c:ould be provided by means of indicator light (s), audible beep~ or ~ -tones, vibration of the unit, or some combination thereof. Timing of ~uch signals would be program~ed ~0 in accordance with ~n~rd or patient specific prescription~ for ucage.
In another alternate ~nbodiD~ent of the inven-tion, the inhaler device would be integrated with a holding cha~ber (reservoir) ~nto which the aerosol i~ releaeed prior to inhalation. The interior volume of thi8 chamber would be large ~no~ to allow for the eYp~n~ion of the aero~ol. Electronic functions remain ~he same as those provided in the nsn-chamber device.
2 0 RRT~ ~ C~TpTTQN OF DRAWTNGS
Figure 1 i8 an oblique side vi~w of the p~-ent intellig@nt inhaler device.
Figure 2A i8 a side ~ectional view of the r~Ch~i cal construction of the device illustrating major components including the incorporation of the type of pressurized canister most widely used for dispensing metered do~es o~ aerosols.
Figurè 2B i~ a ~ectional view of an alternate mech~n;cal construction inco.~Glating a Venturi-type flo~ meter.
WO ~3/12823 PCI~/USg2/10804 21~6331 Figura 3 illustrates typical me~ ages and graphic oul_~ul, ~upplied to the patient or att~n~nt by the device.
Figure 4 is a bloclc diagram of electronics illustrating the overall architectur~ of the intelligent inhaler device ~igures 5A through 5E show the circuit diagrams for subsyste~ns of the device.
Figures 6~ and 6B are f low chart~; ~howing the overall pro~ef~eC for use of the intelligent inhaler by healthcare profes~ional and patient.
n~T~T~.~n r~ }2TpTToN
The overall ~oce58 of the pres~nt intelligent inhaler ~ystem i8 shown in Figure 6A which pro~.rides an overview of the protocol for closing the thera-peutic loop. ~he target profile envQlope i~
~elected and ins~ d te q., via a clinical computer-hAr~1 woLJ~sl~ation) ~ Th~ targ~t envelope is ~a) a generic patt~rn, or tb) a tailored time : 20 cour~e b~ on ~he patient'~ ind~idual Epirometric values or other input, ~s appropriate. The device is used by the patient and at the next vi~it to the phyRician's office, thQ utilization data are extracted and transferred to the clinical work-station where th~y are revi~wad by the phy~ician or other healthcare professional including analysis of ~ s with respect to pre~ious periods. T~e prescription is adju~tQd if and as appropriate and, if nc:~r-~ry, a new target profile for the given patient and medication is loaded into the int~
gent inhaler device.
WO93~12823 PCT/US92/10804 f Figure 6B i8 an overview of the proce~s for utilization by tha patient. Initially, the devi~e reminds the patient ~hat it is time to take the medication. Thi~ is used $or ~dicatio~, such afi cortico~teroids, which are taken o~er long periods of time rather than in an immediate reaction to an ~cute event ~uch a~ an asth~atic episode. The device is then turned on and the relea~e of aerosol triggered.
Recording of data b~gin~ at the ~tart o~
in~piration or upon actuation of the ~edication canister, whichever i~ earlie~t.
The actual ti~e cour~e of each inhalation i8 compared to the objecti~e target ti~e course, a co~pari~on derived, and a signal given a~ to succes~
or failure. At the end of inhalation, a timer i5 started which run~ for the period of time during which the patient ~hould hold his or her brQath. At the end of ten -o~n~C (or o~her period as ~peci-fied), an auditory and/or visual ~ignal i~ supplied to the patient. The patient can y~e~ a button to signal then breath holding ~ctually ended. In an alternate embodiment, he patient can ~ignal that event ~y exhaling (at least initially) back into the 2s hand-held d~vice with the t$me recorded when an increase in air flow abOVQ a sp~cified threshold is detected.
In addition, sugge~tions for corrective action (e.g., hold breath for a longer time) can be given.
Recorded data are stored for later readout into a record-keeping device (such as a computer-based clinical workstation in a physician's office) for 3 PCT/US92/~0804 interpr2tation and perhap~ compar~son to other time periods by a healthcare professional. ;;
An external view of the preferred phy~i~ale~bodiment i8 ~hown in Figure 1. Located in the housing 100, is a pressurized ~2d~cation cani~ter 102. An important feature i8 the ability to insert and utilize st~Ard metered-do~e inhaler canister~, although the device can be modi~ied to support other con~ners as appropriate. Communication with the patient occurs with input through push-button witch mean~ 104, and o~uL through ~ED indicators 106 and LCD panel display 108. Communication to and from the clinical workstation in the office of the physician .i~ through input/o~L~ data co~un~ation mean. 221 3 ~hown in Figure 2. While thi8 i ~hown as a ~imple 1/0 data ~ .ector ~cket in Figure 1, the invention i not 80 limited. The data communi-cation mean~ 221 in Figure 2A alBo i8 ~n~e~ to include a compact tr~n~c~~ver ~ean~ for communi-2~ cating with a spatially r~ota conLLDl ~ource, ~uch as a workstation, through a radiofreyuency communi-cation ch~nn6l, or the like in accor~nc~ with well known ter~nique~. The remote WG~ ~Lation is capable o~ receiving transmission of data such as the time o~ actual usage or the ~nhalation pattern. The present device iB also c~rahle of being reprogrammed by the remote work~tation to alter the do~age or to provide specific fe~hack to the patiQnt a8 to corrective action.
Air to be mixed with tha aerosoliz8d medication - enters from the ~r~ni n~ in the top of the inhalar hou~ing 112, and the patient's inspiration pulls the air and aero~ol mixture through mou~hpiece .114.
WO93/12823 PCT/U~92/10804 ~,;
2l~3~l A mechanical construction diagram of a preferred e~bodiment of the device is ~hown in Figure 2A. The "on" ~witch 104 for the dev~ce turn~
on the power in the battery 205 (which i8 phyBiCally A~c~cfiible through cover 207) for circuit. which are not active between times of inhaler usage. Other circuits ~ay be powered at predetermined time~, and power i~ supplied continuously to circuits re~o~ible for main~ ing the cont~nts of ~emory.
The Application SpQci~ic IntQgrat~d Circu~t (ASIC) 220 contains the microp~o.~ or, memory, calendar/-clock, power controller, LED/~ound driver, LCD
driver, input/o~uL interface, button-~witch inter- :
face, and analog to digital con~erter~ ~he elec-tronics are co~n~ctable to a work~t~tion by a con~entional ~o~ector means 221. Whether ~he device has been ~hA~en properly i8 determined by input from ~otion e~n-?r 222. Flow i~ measur~d ut~lizing a flow measuring mean~ or flow meter (com~ri~ed of~elements 232, 230, 234 and 112) as follow~. Differential prQ~sure i~ ~ea~ured through ~rt~ re ~en~or ~i~phragm 230 which i~ connected by flow rh~nn~ls 232 to both outside atmo~ph~re and interior ~low chamber 234. Pre~ e ~nsor dia-phragm 230 is connected to the pres~u~e -~nrQr elec-tronics 240 which arç interfaced to an analog to digital converter on ASIC 220. A~rosolized medica~ent is releas~d when the medication cani~ter 102 is de~ e~ and its valve 203 is open~d with the p~e~ ized liquid being ~r~h~rged through the atomizer 242. An actuation pres~ure switch 244 is di~ e~ for contact with cani~ter 102 when the WO93/12~23 2126~3 I PCI/US92/10804 canis~er is depreR~ed to discharge a unit of medicine through ato~izer 242.
Figure 2B illustrates an alternatiYQ embodiment utilizinq a v~l-L~i flow meter de~ign. This 5 construction is the ~ame as in Figure 2A except that the linear respon~e of pressure sen~or d~aphragm 230 is proportional to ~low through the Venturi-flow meter 250, with the signal transmitted by the pre~sure ~en~or electronics 240. Thi~ implementa-lO tion provides the ab~ lity for the patient to exhale~at least initially) into the device to indi~ate he end of the breath-holding period. The exhalation would be into he input port 112 to avoid cloggirlg the atomizer 242 . Th~ 8 por_ 112 could be u ed for 15 recording the patient'~ maximal e2~alation or other ~piroD~et~ic D~easurementfi. The form of p.~ re ~en~or is not cr$tical. A ~ onAt~ctor pres~ure sen~or might be directly "incorporated into an ASIC
device ~wise, K.D., and K. Na~afi, ~Micro~abrication Technigue6 for Integrated SQn~ors and Ni~G_y~Lems~
Science, 254:13351342, (1991~]. Alternatively, a d~fferent mean~ for ~easuring air flow ~uch a6 a miniaturized ma~ flow sen~or, could be Qmployed~
Figure 3 ~hows a ~et of ~ample mQssages to the pati~n~. F~h~k regarding indiv~A~ inhal~tion effort~ appears in the left column, including an illustration of the ti~e cour~e of inspiration rela-tive to a target rang~. GenQral instructions are - ~hown in the center, and prompts for event recordin~-are shown on the right. ~heRQ me~sag~s are displayed by the LCD panel 108 as shown in Figure 1.
Auditory ouL~hL comes through the Piezo sound generator 260 as ~hown in Figure 2A and 2B.
W093/12823 PCT/US9~tlO804 f Figure 4 shows a block diagram of the sy~tem.In a preferxed embodiment, many of the electronic elements are incorporat~d within application spQcific integrated circuit (ASIC) 220, including the micropro~s~r, RAM and RO~ ~torage, calendar/-clo~k, A/D converter, 1~0 function~, and drivers for LCD, sound, and LED deYic~6~ However, in variou~
imple~entations of ~he invention these function may be di~tributed on ~ultiple integrat~d circuits, including ~t~n~Ard and/or custo~ devices. The ~cope of the invention is not limited to any ~ingle ~pecific imple~entation.
The micropL-_P-~Qr m¢~ory requir~ment ~re ~upplied by the R~nAo~-Açç~r~ ~mory (RAM) and the Read-Only Memory (ROM) ~odule~. The calendar/clock ~dule provide~ the ability to signal to the patient when it i~ time to t~ke the medication, ~nd g~ner-ate~ time and date st~mp~ for ~ch inhaler use. The analog input signal from the p~e7~ e ~n~r elec-tronics is trans~ormed by the analog to digitalconverter. The power controller provides power to all the device sub~ystems including the m~cro-pL O~ or and associated co~ponents, flow-measuring circuit, LED/Qound display and driver, ind the LCD
alphanumeric p~nel and dxiver. Input/ouL~uL
Gircuitry handle~ signals coming into and/or going out o~ the pu~h-button contact ~witches and two-way communications with the computer-h~re~ clinical workstation or other suitable device occurs through the external communications conn~ctor 221.
Figures 5A through 5B illustrate subsystem circuit diagrams. Figure 5A shows the power CO11~LO1 circuit. Mcdules such as the PAM are powered W093/12~23 PCT/US9~/~0~04 continually. As to power control, when the motion sen~or 500 is triggered with transmission ~hrough the MOSFET semiconductor 502 on the left or the "on"
504 button switch closed, the NAND 508a, 508b gate change state and ~witch on the NOSFET ~emi~n~ctor 510 on the right to provide voltage to the micro-pror~C~or. ~hen the microprocessor goes into the ~'sleep mode" after its opexational sequenc~, it trans~its an l-of f '~ ~ignal to the ~OSFET 8emi-conAl~ctor 512 which deactivates the NAND gates 508a, 508b and shuts the system down. The device i8 battery operated using preferably a lithium battery ~or long life.
Figure 5B shows the p~ e -~Pror flow~eter electronic~. The strain gauqe re~istor~ 520a, 520b, 520c and 52Od in the bridge circuit are located on the pxessure-sensor ~i~p~ragm 230 which ~easures the pres~ure differential in the flow m~ter co~prised of el~ents 232, 230, 234 and 112 in Figure 2A or in the ~llLuL~ flow ~ter 2S0 Bhown in Figure 2B. In accor~nce with te~hniquçs which are well known to those ~killed in the art, an analog ~ignal i~
generated through the two stages of operational amplifiers 522, 524. This signal i8 tran~formed by the analog-to-digital converter 530 and fed via a bus to the micropt~ or (not ~hown).
Figure 5C illustrates ~he LED/~o~ln~ display and driver. The control signal comes from the micro-~oc~--or to 8 bit latch 540. The ~G..L~ol signal is ~tored by the 8-bit latch 540. Selected components, such as zero to six of the L~D~ 542 and zero to two Piezo -o~ generators 544 are turned on. In like manner, co~ponents which are on can be turned off ~ , . ~
WO93~12B23 PCT~US~2/108~
~, Zl?~633~
wlth a subsequent control signal tran~tt~d by the mlcroproo~or .
Figure 5D presents the block diagram for th~
LCD alrhAn~eric panel and driver. The eo..L~ol signal comes in over ~he bu~ to the microprooQ~sor and the LCD controller provide~ input to ~he LCD
dri~er (input to rows of display) and the LCD dot-matrix display panel (input to colu~ns of di~play) in ~ccordance with te~hnique which ~re well known.
Figure 5E illu8tr~te8 the pu.h-button switch interface. Becau~e ~hi~ interface r~id~s on the microprsç~cr bu~, a three state buffer i8 u8ed (off, flo~ting, on). In the fi~ure, the ter~
tri~tate is used, reflecting a particular version of the buffer pro~l~cQ~ by National Semiconductor Corpo-ration. The current status of each of the pu~h-button switches i8 held within the bu~fer. The thLee _tate buffer is interrogatQd by the mic~o-~ G. --~or by turning the thre~ ~tatQ control to "on"
and th~ statu o~ ~ach line (~on~ or ~o~f~
tran~mitted from the three-state bu~f~r back to the mio~G~ooe~or over the micropro~ or bu~.
Figure 6A -~hows the overall protocol whereby data collected by the intelligent inhaler are used to close the therapeutic loop, and enable the healthcare pro~ider to track the patient's ~edica-tion u~e between visits. The physician ~lects the target profile for the patient and medication. The profile is loaded into the device and the device is u~ed by the patient. At the next ~isit of the patient to the healthcare provider, the data related to pati~nt utilization o~ the device is extracted and ~o~ed to the clinical workstation. rhe data are wos3~12823 2 ~ 2 6 3 3 1 PCT/US92/108~
-- 19 -- , ., then reviewed by the physician and trend analysis can be don~, not only within the given ~et of data, but in co~parison to pre~iou~ period~. An ad~u~t-ment ean be made to the prescription ~f the physician ~hoQ~e~ to do 50. If ~here i8 a change, the new prescription infor~ation and/or target profile are loaded into the intelligent inhaler device.
Figure 6B illustrates the pr~eF~ of utiliza-tion of the intelligent inhalation device by the patient. If the medication i~ tak~n at pre~cribed interYals rather than on an epicodic basis, a :.
remin~r of the time to take the medicine iB
sig~Alted to the patient. ~he patient depr~e~ the "on" ~witch to indicate the med~cating ~equence i~
to be st~rted and chA~ the device with the cani~ter in~erted 80 the mQdication i8 ad~quat~ly prepared for ~;~ch~rg~. DepreR~ion of the cani~ter ~ Y~h to Air~h~rge the m~dication i~ the trigger event. Recording of the data, including rQlea~e of aero~ol, airflow time cour~e, and ~roriated time and data StampB e~ r. DQri~ed valU~8 ar~ calcu-lated and compared to the target ~alue~ of the target function. The breath holding period is timed and an auditory and/or vi~ual ~ign~l ~upplied to the patient at its end. .Auditory and/or vi~ual f~dback i~ provided to the patiQnt a~ to ~ucce~ or failure of the inhalation actions including text ~o~sagas a~
to what correction~ ar~ a~o~ iate (e.a., T~U~
SLOWER). At the n~xt patient v~sit, the l~_ur~ad data are read into the hoEt clinic~l workst~tion and the d~ta analyzed and displayQd, Lncluding trend analysi~ in compari~on to pr~vious periods.
WO93/12823 PCT/U~92/10~04 2 ~6~ 3 ~ - 20 -A typical cycle of operation, with reference to Figures 1, 2A and 2B, is a~ follow~:
If the medication i8 to be taken regularly, the ti~e for the med~cation to be takan c~n be ~ignalled through Piezo sound generator 260 and/or LED di~play 108.
The unit is held in patient's hand such ~hat mouthpiece 114 faces the patient.
The patient pres es push-button ~witch 104, activating the "on" switch to clo~e and activate thle microproc~or and associated functions.
The patient r~A~e~ the unit per in~tructions, causing the motion ~e~or 222 to gonerate a signal for storage in the ~e~ory contained in the ASIC ~20.
If the on ~witch 104 ha not y~t been activated, motion sensor 222 causes the unit to turn on jU8t as if the on had b2en closed. Optionally, thi~ signal al o prompts indicator lights 106 to turn on a8 well.
Patient then places the ~outhpiece 114 in ~outh, depres~ec ~edication canister 102 firmly enough to cau~ ~etering ~ech~n~ 03 to ~;rch~rge a unit of medicine through atomizer 242, and the patient simultaneously begins to inhale. Depress$on of tha canister 102 causes closure of actuation sensing switch 244 and tran~ission of a signal for this event t~ microprocessor within the control electronics of ~SIC 220.
Nith the inhalation, aerosolized medication flow~ through the mouthpiQce 114 into the mouth of the patient.
Pra~u~ n~or ~r~ragm 230 e~ air flow coming through the upper housing opening 112 and wos3/l2823 PCT/US92/10804 mo~ing through flow chamber 234 by measuring the pres~ure differential between the outside air ~hrough passage 232 and the ~nternal chamber 234 (in the configuration shown in Fig. 2A). In the alt~r-nate construction shown in Figure 28, pre~sure sensor diaphragm Z30 senses air flow by measuring the pre sure differential between ~he two ~tage~ of Venturi flow meter 250. Pre ~ure-sensor electronics 240 generate~ a signal repl~eçntative of flow rate to the analog-to-digital con~erter contained in the ASIC 220.
The analog-to-digital circuitry converts thi~
signal to digital form, upon whi~h it i~ ~tored a~ a series of (e~g., 8-bit) sa~ples in a RA~ con~in~
in ~he ASIC 220.
As patient contin~s to in~pire, time ~erie~
flow samples in memory are compared with target objective profile representative of correct inhala- -tion technique al~o stored in ~AM contA~n~~ in ASIC
220. The microp~ r cont~;n6~ in ASIC 220 performs the compari~on of actual versus target value6 and depen~inq upon the result~ ~and~ stgnal~
to indicator LED's 106.
Upon completion of in~piration, ~sration of flow ie detected and measurement of time duration of breath hold beqins using the cal~ndar/clock module cont~in~ in ASIC 220.
Upon end o~ braath hold, patient p.f-~e~ pu~h button 104 which ~nA~ an evont ~ignal to micro-p~ or in ASIC 220 for ~torage in PAM and calcu-lation of breath-holding duration.
Re~t lts of the maneuver, incl~ ng breath holding performance are used to select textual or WO93/12823 PCT/~S~2/10804 ., ~ .
2 ~2 63~ ~ - 2~ -iconic feedback from a table stored in RAM contained in ASIC 220, in accordance with tec~ique~ which are well known for di~play to patient via LCD di~play s panel 108~ Note that text table c~n con ist of ~ultiple sections corresponding to differi~g la~guages.
After ~he inhalation m~neuver is complete, the device can pose questions to the patient on LCD
display 108 and answers such as "yes" or "no", or other answers corresron~ to the numb~r of ti~es the push button switch is activ2ted are input by the patient through pu h-button ~witoh 104.
A~ter a specifi~d time (long enough to per~it an additional ~ Arge of ~edication if there i~ to be on~) an o~y~L ~ignal from the mi~lo~ e_-or to the power ~o-,L~ol circuit cau~es the ~ystem to e~r 11 to sleep mode.
Data ~ro~ multiple maneuvers can b~ downloaded c~h~uently through ronn~ctor 221 into a clinical workctation or similar device for review by profes-sional including trend analysis within the se~ of ju~t downloaded data and comparison to previous period~.
Upon downlo~ g of data, records for individual maneuver~ are erased from the RA~
con~ne~in ~SIC 220, and battery 205 i8 checked for charge.
The site of compliance monitoring includQs a digital computer means (not shown) for communicating electronically with the microproce~-or ~eans 220 incorporated in the programmable inhaler~ The digital computer means at the monitoring site includes means for monitoring and i~oving a WO93/12823 2 1 2 6 3 3 1 PCT/U~92/108W
- 23 - ;
patient's medication compliance with the use o~ the hand-held i~haler~ The monitoring computer i8 lin~e~ with transmission ~ans for re~ote electronic retrieval of the data mea~ured by and storQd in the inhaler mi~Lo~oce~ror through data communication te~hn~gues which are well known, such as radio-freguency, optoelectronic communication, or the like. ', The monitoring computer is ~v~am~ed to evaluate the data received from the inhaler ~icro-proc~ror ~eane and to provide interpretations of the effectîveness of compl~ance efforts based on he retrie~ed data. The monitoring computer also includes a display mean~ for ffleaning~ul display of the compliance dataO Such di~pl y means preferably includes patient's projected target envelope for maximized delivery of ~edication ~ compared to the actual, m~a~ured performance of the patient.
It will be appr~ciatQd by tho~e ~killed in the art that there are a ~ultitude of methods for progra~ming the ~onitoring co~puter to achieve the evaluation of a pati~nt'~ medication compliance parameter~ which will maxi~izQ delivary of medica-tion to the large airways, s~all airway6, alveoli or any part of the respiratory tract. Thu8, the pr~ent m~thod is not intenA~ to be limitQd to ~
specific software impl~mentation for diagnosing a patient' 5 project~d compliancQ as a target ~nvelope of values and for mea~uring th~ actual performance of the patient with re~pect to the target envQlope.
In a preferred embodiment, the monitoring co~puter includes software which is readily p~v~Lammed by one skilled in the art to utilize data WO93/12823 PCT/US92/~0804 2~633~
input from diagnostic in~truments, diagno t~c tests, clinical records, clinical ob~ervation~, profes-sional opinions~ or the like in calculating a target envelope of inhalation para~eters which will ~axi-mize the delivery of aerosoliz~d medication to anyselected par~(.) of the re~piratory tr~ct of a particular patiant, or to indic~te o~her change~ in therapy such a~ type o~ medic~tion. The for~going data include quantifiable par~meters relating to thf~
physical condition of the airw~ys of a patient, such as the size of the patient'~ air p~s~age~.
The data are input into the ~onitoring computer as a table of value , or phy~ical para~eters indica tive of the condition and cArAr-lty of a patie~t's ~S air r~ eways and inhalation characteri~t~c~. The table of physical parameters are then ~apped to pxovide the target envelope of values, which if matched by the pat~ent's performancs, will m~xi~ize the distribution of the aero~ol mQdicat~on any selected parts of the respiratory tract. The moni-toring computer compares the patient's actual measured performance to the target envelope. The monitoring co~puter then communicates electronically with the mic~G~ or in the inhaler, ind a8 a func~ion of ~easured compliA~c~ par~meters, ~ o grams the microproc~or, ~f nec~Q~-~y, with differ-ent target inhalation profilQs, dosage 1eVQ1g or actuation event ti~es that will bring the pationt's performance within the target envelope and maximize ~he therapeUtiC '~r~
The advantages of the system dascribed herein over convantional devices may be sum~arized as ~ollows:
wos3/l28~ PCT/US92/10804 ~;
212S33~
(a~ the incorporation o~ both ~onitoring and '.
recording the patient's inhalation time cour e and related e~ents in a medicine inhaler device ~all and aesthetically pleasing eno~ to be u~ed during normal day-to-day activitie6, (b) the ability to load in a target perfor-mance en~elope for one or more inhalation ti~e/value csur es and/or one or ~ore ~elected variables (~uch as peak-flow rate) or to de ignate a 3peci~ied generic curve, (c) the ability to -~nre whether the device ha~ been c~ken properly prior to ~irc~Arge of a dose of aero~oi, (d) the ability to provid~ ediate f~e~ck both during the inhalation and ~fterwards a~ to where the patient' 8 performance fit~ relative to the target-perfor~nce envelop~ and whether and whan inhalation values fell outside that envelope, (a) the ability to pr~vide f~Q~haçk to the patient as to what co~ tive ~ction, ~f any, ~hould be taken, (f) the ~bility to provide a signal to the patient prompting him or her to continue breath holding, (g) the ~bility to ha~e the patient record the ti~ing of the end of the br~ath-holding period, (h) the ~bility to store any of tha data ~
ob~ne~, i (i~ the ability to download longi~ n~l results from the Intelligent Inhaler into a health-care ~ L~t~on or similar device, and (~) the ability for th~ healthcare profes-sional to review a patient's medicine usage for the ~,~?,63 ~
entire period between office visit~, and therefore revi~w trend~ in the patient's conditlon in the context of a detailed hi~torical record of the actual delivery of medication to its target ~ites of action in the lungsO
It ~hould be ~oted that all of the above capa-bilities wQuld not nece~fi~r~ly be included in every implementation of the 5y5te~.
The device and method described here are not limited to usage with any one pharmaceutical. They may be used with locally acting respiratory drug~
including bronchodilators, corticosteroids, anticho-linergics, antibiotics, and others, as well a~ with systemically acting drugs. Differing com~o~.~ may require v2riation in prescribed usage, including change6 în the inspiratory flow pattern. Such patterns may be oho~en in order to direct the roncentration of drug deposition at di~fer~nt sites within ~he respiratory tract, or compen~ate for varia_ions in patient'~ airways ~orphology due to di3e~-e or trau~a.
These problems are e~p*ci~ly ~vident in the case of aerosol phar~aceutical~ delivered by hand-held inhaler~. Hand-held metered dose inhalQr~
(~DI~) are a preferrad method of tr~atment for common respiratory ail~ents, ~incR the deliv~ry of ~edic~tion diractly to i~ int~nA~ ~ite of Act~on in the lung~ allows a reduction in dosage by an order of magnitude or gr~atar. However, certain of these com~o~ , such ~8 anti-inflammatory cortico-steroid~, may take many weeks of admini~tration before having a signific~nt effect. Moreover, the inhalation and breath-holding ~aneuver requirRd for ~ cçq-~ful deliv~ry of aero~ol to the lowar airway~
is counterintuitive and poorly under~tood by mo6t patients. Thus, a patient may be compliant in u~ing tha madication when pr~scribed, ~ut un~cc~ful in using it in the corract ~anner.
When therapeutic results are not ob~Aine~, it may not be evident to the phy~ician which step~) in W093/12823 PCT/US92/1~
f 2126~3~ :
the proce~ are the problem. Relevant que~tions, for example, are Nwas the medication not taken at all?", "was it taken at the corr~ct interYal~ and in ~LO~eX relationRhip to expo~ure to ~llergens or other irritants?", and "was the inh~lation perfor~ed correctly?".
Another problem the physician faces i~ how to interpret variability in therape~tic respon~e. I~
the v~riability due to ~o~e fundamental ~nqe in the pati~nt'~ condition (e~, the pati~nt now ha~ a~
lou ~Lade upper re~piratory infection) or is it cau~ed by difference~ in deliverQd medicat~on dosage?
~epo~ition of aerosol ~edication ~n the human lung i5 primarily deter~ined by ~wo pL~_Eere~, inertial impaction and gra~itational ~edimentat~on~
Impaction of aero~ol~ in the lung~ occurs pri~arily at airway bifurcations, and has been ~hown in scintigraphic studiQs to incre~ a~ ~ function of flow rate. Sedi~entation in~olve~ gravitational settling of a~roaol particl~s on the ~irways and al~eoli. 11~ , S.P., PaYi~, D., Garland, N. and S.W. Clarke, "Effect~ of Various ~h~lation Mo~c on the D~po~ition of Radioactive Pres~urized Aerosols,"
EU~ r J. Re8D;rAtOnr D~S. . S~D1e~ 119, 63: 57-65, ( 1982 ) demonstrated that the percentage of aero~ol depo~ited in the lungs of patients wa6 signifi~antly greater when the pat~ ents held their breath for ten E~onAC than when br~ath holding was only four -ecQnA~.
Thus, for aerosol to be ~o~o~ted in the lower airway~, the primary site of action for common medi-cations such as corticosteroids and bronch~ ators, PCT/~S92/10804 21263~
the patient must coordinate the relea~e of medica- ~
tion, inhale slowly enough to minimize 106s of ~edi-cine through impaction in the throat and upper air-ways, and br~ath hold long ~no~l~h to allow time for small particle~ to settle. In practice, this mean~
an inhalation rate below one liter per ~econd, and a breath hold for up to ten seconds.
A hand-held (e.a., metered or unit-do~e~
inhaler currently is a pa~sive device that provides n no information regarding the medication actually delivered. Orehek et ~ ound that only five of twenty a~thmatic patients correctly i~halQd. "The other 15 patients fail~d either to in~pire deeply or hold their breath a~terwards, or both, or poorly coordinated the puff and the in~piration.U Orehek et al., "Patient ~l~G~ in Usa of Br~nchs~ilator Metered Aero~ol~,~ Rr~t~h ~ l Journ~ 76, (1976).
For example, it has ~en found that in a group of 30 acute a~th~atic patient~ direc~ly ob~arv~d in a clinical setting, 47% (14 patients) used incorrect ique. Tha fourt~en pati~nts wi~h in~equate t~hniqus were then trained. Ten of them were ret~ted after an interval of one day to one month.
Five of the patient~ ~re ~till u~ing th~ir inhalers eo~.eetly; the other five had revQrted to their original ineorreet tee~iques. Shim, C., and M.H. Williams, "The Adequacy of Tnh~ lation of Aelo~ol from Canister Nebulizers,~ The Ameri~
Journal of ~edicine. 69:891-894 (1980).
The device and appro~eh deser~ed her~in would hav~ proYided im~ediate feedback to the patients that they had reYerted to incorrect uae o~ their W~3/12823 PCT~US92/10804 inhalers, and provided them with pecific ~~ nc~
as to what corrective action was requir~d. Thus, retraining would not have had to wait until their next ~isit to the clinic.
The present approach al~o fo ters the d~livery of a uniform do~e to the target ~ite3 of th~
patient'~ lungs upon each inhaler usage with the expectation of consi~tent therapeutic re~ponse.
Thu~, if the patient's ~ympto~s or condition changes, the physici~n can evaluate the change with r~ n~hle ~surance ~hat the difference i5 not simply due to a variation in ~edication do ~ge. By ~ak~ng data regardinq the patient's inhal~r use during the entire period betw~en clinic Vi8it8 available to the physician, therapy can be ~anaged on a more informed basis.
It ha~ been observed that, ~The lung pre~ents a significant barr~er to the ponetr~tion of drug particl~s of a size s~all ~ h to ~aximize thera-peutic efficacy." Padfield, J.~ Principl~ ofDrug Delivery to the Respiratory Tr~ctH, ~g D~livery to the Resu~r~tory Tr~Ct~ ~n~ton, D., and Jones, T., Qd., Horwood, Lundon (1987).
Padfield conclud~ "The design of delivery ~y~tem for admini~ter~ng drug~ to the lung can ha~e as much, or more, impact as the choice of drug." (i~-) Previous attempts to improve the ef~ectiven~ss of aero~ol medicine inhalers include a number of - device~ including ~ra~rs, aerosol holding chambQrs, flow-activated triggering me~h~n;cms, and dry powder generators.
The problem of medicine ~Ppocition in the mouth and throat can be alleviated in ~ome caaes by the W093/12823 PCr/US92/108~
2~26331 t~
use of a tube spacer, an extension tube inserted between the metered unit-do~e inhaler and he patient'~ ~outh. This pro~-e~ re ~till require~
coordinated patient action and in itself provides no f~e~h~k to the patient as to the Sl1rCePF or f~ilure o~ the overall sffort.
Another approach to improving NDI u~age i5 the use of chambers or reservoirs into whieh the aerosol ~ eh~rged prior to inhalation. Such device~
reduee the need for coordination of actuation and start of inhalation. A widely used device i~
described in Sackner, et. al., U.S. Patent No.
4,484,577, 1984. Thi~ device al~o provides an audible whi~tl~ when the in~piration rate i~ abov~ a fixed level. Th~ dev~ee f~ils to addrQss inter-patient variations in correct inhalation patterns, a~ well as the br~th-holding ~taqe. A co~mon draw-baek of all ehamber deviees i8 their bulk. Such deviees may not fit eonveniently in a pocket or pur~e, and many patiQnt~ are unwilling to u~e ~uch large devices due to ~elf c- ~~io~r ~ r~ . The proce~ in accorA~nee with the pre~ent invention ean be u~ed irre~peetive of whether a tube spaeer or a reservoir is u~ed.
Conventional ~y~tems al80 include ~everal inhaler deviees wh~ch a~dL~-- the eoordinati~n problem by incorporating a ~ean~ of trigger~ng the medication relea~e by the start of inhalation. Such devices have bean described by Wass, U.S. Patent No. D
4,664,107 1987, ~nd Johnson et. ~1., U.S. P~tent 4,803,978 1989. ~har.r, U.S. Patent 4,739,754, 1988 de~cribes a ~Suction Resistant Inhaler" whose design fosters a deep inhalation by the patient.
WO93~12823 Other conventional devices have incorporated electroomech~nical components in order to record the timing and date of usage for revi~w by a healthcare professional. Spector, et. al., "Compliance of Patients with Asthma with ~n Experimental AerQsoll2ed Medicatlon: Implications for Controlled Clinical Trials, n Jou~nal of Aller~y & Clini~
T~mlln~logy~ 77:6~-70 (1986) discloses the u~e of a nebulizer chronolog to I L 'OL~ the patient~ u~age of MDIs between clinic visits. Thi~ incorporate~
device for r~cording the time and datQ of each canister actuation for later review by physicians conducting r~-r-~ch on pattern~ of patient compliance. Thi deYice lacks the ~p~hility for lS ob~Ai~ any information regarding the inspiratory maneuver itself. Furthermore, since the intention of the ~tudy wa~ to record patient~' MDI usage patterns w~thout their knowl~dge, the device not provide any fe~Ah~k to the patl~nt~ regarding proper inhalation ~e~hnique.
S ~ilar de~ice~ are de w ribed by ~and et. ~1., - U.5. Patent 4,817,822, 1989, and ~çr~ertine, U.S.
Patent 5,020,527, 1991. The Rand device incorpo-rates a mechAn;cal rachet wheel and driving member 25 to drive an indicator of the number of actuations of an aero~ol cani~ter. The~ r~rtine device provides a timer and a counter for tr~ckin~ the number of and time between actuations.
In tha aforem~ntioned d~vice~ thQ time cour~e of air flow is not measured, nor is it comparad to the desired pattern for the ~pQC~fiC patiQnt a8 may be d~termined by a healthcare profe~sional. Thus, the~e devices addre6s only the a~pect of compliance WO~3~12823 PCT/US92~1~8~
- 8 - ;
relating to if and when the medicine was used. In order to A~.F~ whether an aerosol medication has been used effectively, it i8 n~cecr~ry to further deter~ine infor~ation regarding ~he pat~ent's coordination of actuation and inspiration, Yolu~e and flow rate of inspiration, and post-inspiratory breath holding.
In ~ummary, con~entional devices fail to adequately addrec~ ~he need for immediate patisnt feedback regarding multiple ~teps in the corr~ct u~e of inhaler~. The~e devices are al~o ~nAAequate in providing infor~ation to both patient and healthoare professional reqarding the critical factor~ which determine the sllcce~n of m~dicine delivery, including coordination of inhalation w~th actuation, inhalation flow r~te and duration of br~ath holding.
What i8 neeAe~ i8 a hand-held inhaler devlce which can monitor the complete time coursQ of airflow during ~n inhalation, and ~h~ pO~CB~a8 the r~r~hility to guide the pati~nt in it~ correct us~ge before, during, and after u~e~ What is al~o n~e~e~ i8 ~u~h an inhaler whose functions include the capacity to ~eCULd relevant information about the timing and nature of itR use for ~ubs~qu~nt review by a healthcare professional.
SUM~Y OF ~ V ~ ON
The pre~ent device detects how much air i8 inhaled through the inhaler with what time course (including such derived measurements as how much volume is inspired within the bounds of a gi~en flow range) as well as certain event such as the triggering of the release of aerosol. The system WO93~12823 PCT/US~2/10804 2126~
can be set up to co~pare the re~ultant time course to either (a) a st~nd~rd target envelope (e.q., one or more of flow, volu~e, and time) for that ~edica-tion or (b) a specific target ~nvelope for that particular patient programmed into the intelligent inhal~tion device by a healthc~re professional.
RAre~ on ~he ~p~ri~on, the ~uccess or failure o~
effectiYe inhaler actuation and aerosol inspiration can be signaled to the patient (e.a., vi ually or through sound) and may be ~e_o~ed with a t~me and date stamp for later ~co~ n~ and evaluation by a suitable healthcar~-profe~sional. ~n a preferred emb~di~ent of the i~vention, the device would al~o the ability to signal ~he patisnt to continue post-in6piratory ~reath-holdin~, and record the end o~ br~ath holding ~or U8e ~n interpret~ng the ~ ce~ of medication delivery.
In addition, immediate feedback can be ~upplied to the patient as to the specifie nature of any mistake~ made. For example, a ~ ge miqht bs given that the patient's ~h~lAtion was too rapid.
In a preferred embodiment of the invention suf f icient memory is provided to ~tore data from a large number of inhalation6. Thi8 aUtomatQd ~eCG~d may be u~ed in conjunction with a manual log kept by the patient (e.a., what,e~ent, such as eYro~re to an allergen, cau~ed the need to administer the medi-cation) or in a ~emi-automated fashion by h~ving the - patient or att~n~ant e~C9~9 event-related infor-mation into thQ ~nhaler device memory. An example of the latter would be the pr~ssing o~ a button in a certain pattern that would be ~-oc;ated w~th a ,. . : .
PCr~US92/10804 2~26331 specific event. This event information could be stored together with a ti~e and date ~;tamp. ~.
In an alternate ~ho~ iment of the invention, the inhaler device would po~er~ the capability to 5 signal the patient at the times ~or which ~ts use has b~aen prescribed.. Thi ~ ~ignal c:ould be provided by means of indicator light (s), audible beep~ or ~ -tones, vibration of the unit, or some combination thereof. Timing of ~uch signals would be program~ed ~0 in accordance with ~n~rd or patient specific prescription~ for ucage.
In another alternate ~nbodiD~ent of the inven-tion, the inhaler device would be integrated with a holding cha~ber (reservoir) ~nto which the aerosol i~ releaeed prior to inhalation. The interior volume of thi8 chamber would be large ~no~ to allow for the eYp~n~ion of the aero~ol. Electronic functions remain ~he same as those provided in the nsn-chamber device.
2 0 RRT~ ~ C~TpTTQN OF DRAWTNGS
Figure 1 i8 an oblique side vi~w of the p~-ent intellig@nt inhaler device.
Figure 2A i8 a side ~ectional view of the r~Ch~i cal construction of the device illustrating major components including the incorporation of the type of pressurized canister most widely used for dispensing metered do~es o~ aerosols.
Figurè 2B i~ a ~ectional view of an alternate mech~n;cal construction inco.~Glating a Venturi-type flo~ meter.
WO ~3/12823 PCI~/USg2/10804 21~6331 Figura 3 illustrates typical me~ ages and graphic oul_~ul, ~upplied to the patient or att~n~nt by the device.
Figure 4 is a bloclc diagram of electronics illustrating the overall architectur~ of the intelligent inhaler device ~igures 5A through 5E show the circuit diagrams for subsyste~ns of the device.
Figures 6~ and 6B are f low chart~; ~howing the overall pro~ef~eC for use of the intelligent inhaler by healthcare profes~ional and patient.
n~T~T~.~n r~ }2TpTToN
The overall ~oce58 of the pres~nt intelligent inhaler ~ystem i8 shown in Figure 6A which pro~.rides an overview of the protocol for closing the thera-peutic loop. ~he target profile envQlope i~
~elected and ins~ d te q., via a clinical computer-hAr~1 woLJ~sl~ation) ~ Th~ targ~t envelope is ~a) a generic patt~rn, or tb) a tailored time : 20 cour~e b~ on ~he patient'~ ind~idual Epirometric values or other input, ~s appropriate. The device is used by the patient and at the next vi~it to the phyRician's office, thQ utilization data are extracted and transferred to the clinical work-station where th~y are revi~wad by the phy~ician or other healthcare professional including analysis of ~ s with respect to pre~ious periods. T~e prescription is adju~tQd if and as appropriate and, if nc:~r-~ry, a new target profile for the given patient and medication is loaded into the int~
gent inhaler device.
WO93~12823 PCT/US92/10804 f Figure 6B i8 an overview of the proce~s for utilization by tha patient. Initially, the devi~e reminds the patient ~hat it is time to take the medication. Thi~ is used $or ~dicatio~, such afi cortico~teroids, which are taken o~er long periods of time rather than in an immediate reaction to an ~cute event ~uch a~ an asth~atic episode. The device is then turned on and the relea~e of aerosol triggered.
Recording of data b~gin~ at the ~tart o~
in~piration or upon actuation of the ~edication canister, whichever i~ earlie~t.
The actual ti~e cour~e of each inhalation i8 compared to the objecti~e target ti~e course, a co~pari~on derived, and a signal given a~ to succes~
or failure. At the end of inhalation, a timer i5 started which run~ for the period of time during which the patient ~hould hold his or her brQath. At the end of ten -o~n~C (or o~her period as ~peci-fied), an auditory and/or visual ~ignal i~ supplied to the patient. The patient can y~e~ a button to signal then breath holding ~ctually ended. In an alternate embodiment, he patient can ~ignal that event ~y exhaling (at least initially) back into the 2s hand-held d~vice with the t$me recorded when an increase in air flow abOVQ a sp~cified threshold is detected.
In addition, sugge~tions for corrective action (e.g., hold breath for a longer time) can be given.
Recorded data are stored for later readout into a record-keeping device (such as a computer-based clinical workstation in a physician's office) for 3 PCT/US92/~0804 interpr2tation and perhap~ compar~son to other time periods by a healthcare professional. ;;
An external view of the preferred phy~i~ale~bodiment i8 ~hown in Figure 1. Located in the housing 100, is a pressurized ~2d~cation cani~ter 102. An important feature i8 the ability to insert and utilize st~Ard metered-do~e inhaler canister~, although the device can be modi~ied to support other con~ners as appropriate. Communication with the patient occurs with input through push-button witch mean~ 104, and o~uL through ~ED indicators 106 and LCD panel display 108. Communication to and from the clinical workstation in the office of the physician .i~ through input/o~L~ data co~un~ation mean. 221 3 ~hown in Figure 2. While thi8 i ~hown as a ~imple 1/0 data ~ .ector ~cket in Figure 1, the invention i not 80 limited. The data communi-cation mean~ 221 in Figure 2A alBo i8 ~n~e~ to include a compact tr~n~c~~ver ~ean~ for communi-2~ cating with a spatially r~ota conLLDl ~ource, ~uch as a workstation, through a radiofreyuency communi-cation ch~nn6l, or the like in accor~nc~ with well known ter~nique~. The remote WG~ ~Lation is capable o~ receiving transmission of data such as the time o~ actual usage or the ~nhalation pattern. The present device iB also c~rahle of being reprogrammed by the remote work~tation to alter the do~age or to provide specific fe~hack to the patiQnt a8 to corrective action.
Air to be mixed with tha aerosoliz8d medication - enters from the ~r~ni n~ in the top of the inhalar hou~ing 112, and the patient's inspiration pulls the air and aero~ol mixture through mou~hpiece .114.
WO93/12823 PCT/U~92/10804 ~,;
2l~3~l A mechanical construction diagram of a preferred e~bodiment of the device is ~hown in Figure 2A. The "on" ~witch 104 for the dev~ce turn~
on the power in the battery 205 (which i8 phyBiCally A~c~cfiible through cover 207) for circuit. which are not active between times of inhaler usage. Other circuits ~ay be powered at predetermined time~, and power i~ supplied continuously to circuits re~o~ible for main~ ing the cont~nts of ~emory.
The Application SpQci~ic IntQgrat~d Circu~t (ASIC) 220 contains the microp~o.~ or, memory, calendar/-clock, power controller, LED/~ound driver, LCD
driver, input/o~uL interface, button-~witch inter- :
face, and analog to digital con~erter~ ~he elec-tronics are co~n~ctable to a work~t~tion by a con~entional ~o~ector means 221. Whether ~he device has been ~hA~en properly i8 determined by input from ~otion e~n-?r 222. Flow i~ measur~d ut~lizing a flow measuring mean~ or flow meter (com~ri~ed of~elements 232, 230, 234 and 112) as follow~. Differential prQ~sure i~ ~ea~ured through ~rt~ re ~en~or ~i~phragm 230 which i~ connected by flow rh~nn~ls 232 to both outside atmo~ph~re and interior ~low chamber 234. Pre~ e ~nsor dia-phragm 230 is connected to the pres~u~e -~nrQr elec-tronics 240 which arç interfaced to an analog to digital converter on ASIC 220. A~rosolized medica~ent is releas~d when the medication cani~ter 102 is de~ e~ and its valve 203 is open~d with the p~e~ ized liquid being ~r~h~rged through the atomizer 242. An actuation pres~ure switch 244 is di~ e~ for contact with cani~ter 102 when the WO93/12~23 2126~3 I PCI/US92/10804 canis~er is depreR~ed to discharge a unit of medicine through ato~izer 242.
Figure 2B illustrates an alternatiYQ embodiment utilizinq a v~l-L~i flow meter de~ign. This 5 construction is the ~ame as in Figure 2A except that the linear respon~e of pressure sen~or d~aphragm 230 is proportional to ~low through the Venturi-flow meter 250, with the signal transmitted by the pre~sure ~en~or electronics 240. Thi~ implementa-lO tion provides the ab~ lity for the patient to exhale~at least initially) into the device to indi~ate he end of the breath-holding period. The exhalation would be into he input port 112 to avoid cloggirlg the atomizer 242 . Th~ 8 por_ 112 could be u ed for 15 recording the patient'~ maximal e2~alation or other ~piroD~et~ic D~easurementfi. The form of p.~ re ~en~or is not cr$tical. A ~ onAt~ctor pres~ure sen~or might be directly "incorporated into an ASIC
device ~wise, K.D., and K. Na~afi, ~Micro~abrication Technigue6 for Integrated SQn~ors and Ni~G_y~Lems~
Science, 254:13351342, (1991~]. Alternatively, a d~fferent mean~ for ~easuring air flow ~uch a6 a miniaturized ma~ flow sen~or, could be Qmployed~
Figure 3 ~hows a ~et of ~ample mQssages to the pati~n~. F~h~k regarding indiv~A~ inhal~tion effort~ appears in the left column, including an illustration of the ti~e cour~e of inspiration rela-tive to a target rang~. GenQral instructions are - ~hown in the center, and prompts for event recordin~-are shown on the right. ~heRQ me~sag~s are displayed by the LCD panel 108 as shown in Figure 1.
Auditory ouL~hL comes through the Piezo sound generator 260 as ~hown in Figure 2A and 2B.
W093/12823 PCT/US9~tlO804 f Figure 4 shows a block diagram of the sy~tem.In a preferxed embodiment, many of the electronic elements are incorporat~d within application spQcific integrated circuit (ASIC) 220, including the micropro~s~r, RAM and RO~ ~torage, calendar/-clo~k, A/D converter, 1~0 function~, and drivers for LCD, sound, and LED deYic~6~ However, in variou~
imple~entations of ~he invention these function may be di~tributed on ~ultiple integrat~d circuits, including ~t~n~Ard and/or custo~ devices. The ~cope of the invention is not limited to any ~ingle ~pecific imple~entation.
The micropL-_P-~Qr m¢~ory requir~ment ~re ~upplied by the R~nAo~-Açç~r~ ~mory (RAM) and the Read-Only Memory (ROM) ~odule~. The calendar/clock ~dule provide~ the ability to signal to the patient when it i~ time to t~ke the medication, ~nd g~ner-ate~ time and date st~mp~ for ~ch inhaler use. The analog input signal from the p~e7~ e ~n~r elec-tronics is trans~ormed by the analog to digitalconverter. The power controller provides power to all the device sub~ystems including the m~cro-pL O~ or and associated co~ponents, flow-measuring circuit, LED/Qound display and driver, ind the LCD
alphanumeric p~nel and dxiver. Input/ouL~uL
Gircuitry handle~ signals coming into and/or going out o~ the pu~h-button contact ~witches and two-way communications with the computer-h~re~ clinical workstation or other suitable device occurs through the external communications conn~ctor 221.
Figures 5A through 5B illustrate subsystem circuit diagrams. Figure 5A shows the power CO11~LO1 circuit. Mcdules such as the PAM are powered W093/12~23 PCT/US9~/~0~04 continually. As to power control, when the motion sen~or 500 is triggered with transmission ~hrough the MOSFET semiconductor 502 on the left or the "on"
504 button switch closed, the NAND 508a, 508b gate change state and ~witch on the NOSFET ~emi~n~ctor 510 on the right to provide voltage to the micro-pror~C~or. ~hen the microprocessor goes into the ~'sleep mode" after its opexational sequenc~, it trans~its an l-of f '~ ~ignal to the ~OSFET 8emi-conAl~ctor 512 which deactivates the NAND gates 508a, 508b and shuts the system down. The device i8 battery operated using preferably a lithium battery ~or long life.
Figure 5B shows the p~ e -~Pror flow~eter electronic~. The strain gauqe re~istor~ 520a, 520b, 520c and 52Od in the bridge circuit are located on the pxessure-sensor ~i~p~ragm 230 which ~easures the pres~ure differential in the flow m~ter co~prised of el~ents 232, 230, 234 and 112 in Figure 2A or in the ~llLuL~ flow ~ter 2S0 Bhown in Figure 2B. In accor~nce with te~hniquçs which are well known to those ~killed in the art, an analog ~ignal i~
generated through the two stages of operational amplifiers 522, 524. This signal i8 tran~formed by the analog-to-digital converter 530 and fed via a bus to the micropt~ or (not ~hown).
Figure 5C illustrates ~he LED/~o~ln~ display and driver. The control signal comes from the micro-~oc~--or to 8 bit latch 540. The ~G..L~ol signal is ~tored by the 8-bit latch 540. Selected components, such as zero to six of the L~D~ 542 and zero to two Piezo -o~ generators 544 are turned on. In like manner, co~ponents which are on can be turned off ~ , . ~
WO93~12B23 PCT~US~2/108~
~, Zl?~633~
wlth a subsequent control signal tran~tt~d by the mlcroproo~or .
Figure 5D presents the block diagram for th~
LCD alrhAn~eric panel and driver. The eo..L~ol signal comes in over ~he bu~ to the microprooQ~sor and the LCD controller provide~ input to ~he LCD
dri~er (input to rows of display) and the LCD dot-matrix display panel (input to colu~ns of di~play) in ~ccordance with te~hnique which ~re well known.
Figure 5E illu8tr~te8 the pu.h-button switch interface. Becau~e ~hi~ interface r~id~s on the microprsç~cr bu~, a three state buffer i8 u8ed (off, flo~ting, on). In the fi~ure, the ter~
tri~tate is used, reflecting a particular version of the buffer pro~l~cQ~ by National Semiconductor Corpo-ration. The current status of each of the pu~h-button switches i8 held within the bu~fer. The thLee _tate buffer is interrogatQd by the mic~o-~ G. --~or by turning the thre~ ~tatQ control to "on"
and th~ statu o~ ~ach line (~on~ or ~o~f~
tran~mitted from the three-state bu~f~r back to the mio~G~ooe~or over the micropro~ or bu~.
Figure 6A -~hows the overall protocol whereby data collected by the intelligent inhaler are used to close the therapeutic loop, and enable the healthcare pro~ider to track the patient's ~edica-tion u~e between visits. The physician ~lects the target profile for the patient and medication. The profile is loaded into the device and the device is u~ed by the patient. At the next ~isit of the patient to the healthcare provider, the data related to pati~nt utilization o~ the device is extracted and ~o~ed to the clinical workstation. rhe data are wos3~12823 2 ~ 2 6 3 3 1 PCT/US92/108~
-- 19 -- , ., then reviewed by the physician and trend analysis can be don~, not only within the given ~et of data, but in co~parison to pre~iou~ period~. An ad~u~t-ment ean be made to the prescription ~f the physician ~hoQ~e~ to do 50. If ~here i8 a change, the new prescription infor~ation and/or target profile are loaded into the intelligent inhaler device.
Figure 6B illustrates the pr~eF~ of utiliza-tion of the intelligent inhalation device by the patient. If the medication i~ tak~n at pre~cribed interYals rather than on an epicodic basis, a :.
remin~r of the time to take the medicine iB
sig~Alted to the patient. ~he patient depr~e~ the "on" ~witch to indicate the med~cating ~equence i~
to be st~rted and chA~ the device with the cani~ter in~erted 80 the mQdication i8 ad~quat~ly prepared for ~;~ch~rg~. DepreR~ion of the cani~ter ~ Y~h to Air~h~rge the m~dication i~ the trigger event. Recording of the data, including rQlea~e of aero~ol, airflow time cour~e, and ~roriated time and data StampB e~ r. DQri~ed valU~8 ar~ calcu-lated and compared to the target ~alue~ of the target function. The breath holding period is timed and an auditory and/or vi~ual ~ign~l ~upplied to the patient at its end. .Auditory and/or vi~ual f~dback i~ provided to the patiQnt a~ to ~ucce~ or failure of the inhalation actions including text ~o~sagas a~
to what correction~ ar~ a~o~ iate (e.a., T~U~
SLOWER). At the n~xt patient v~sit, the l~_ur~ad data are read into the hoEt clinic~l workst~tion and the d~ta analyzed and displayQd, Lncluding trend analysi~ in compari~on to pr~vious periods.
WO93/12823 PCT/U~92/10~04 2 ~6~ 3 ~ - 20 -A typical cycle of operation, with reference to Figures 1, 2A and 2B, is a~ follow~:
If the medication i8 to be taken regularly, the ti~e for the med~cation to be takan c~n be ~ignalled through Piezo sound generator 260 and/or LED di~play 108.
The unit is held in patient's hand such ~hat mouthpiece 114 faces the patient.
The patient pres es push-button ~witch 104, activating the "on" switch to clo~e and activate thle microproc~or and associated functions.
The patient r~A~e~ the unit per in~tructions, causing the motion ~e~or 222 to gonerate a signal for storage in the ~e~ory contained in the ASIC ~20.
If the on ~witch 104 ha not y~t been activated, motion sensor 222 causes the unit to turn on jU8t as if the on had b2en closed. Optionally, thi~ signal al o prompts indicator lights 106 to turn on a8 well.
Patient then places the ~outhpiece 114 in ~outh, depres~ec ~edication canister 102 firmly enough to cau~ ~etering ~ech~n~ 03 to ~;rch~rge a unit of medicine through atomizer 242, and the patient simultaneously begins to inhale. Depress$on of tha canister 102 causes closure of actuation sensing switch 244 and tran~ission of a signal for this event t~ microprocessor within the control electronics of ~SIC 220.
Nith the inhalation, aerosolized medication flow~ through the mouthpiQce 114 into the mouth of the patient.
Pra~u~ n~or ~r~ragm 230 e~ air flow coming through the upper housing opening 112 and wos3/l2823 PCT/US92/10804 mo~ing through flow chamber 234 by measuring the pres~ure differential between the outside air ~hrough passage 232 and the ~nternal chamber 234 (in the configuration shown in Fig. 2A). In the alt~r-nate construction shown in Figure 28, pre~sure sensor diaphragm Z30 senses air flow by measuring the pre sure differential between ~he two ~tage~ of Venturi flow meter 250. Pre ~ure-sensor electronics 240 generate~ a signal repl~eçntative of flow rate to the analog-to-digital con~erter contained in the ASIC 220.
The analog-to-digital circuitry converts thi~
signal to digital form, upon whi~h it i~ ~tored a~ a series of (e~g., 8-bit) sa~ples in a RA~ con~in~
in ~he ASIC 220.
As patient contin~s to in~pire, time ~erie~
flow samples in memory are compared with target objective profile representative of correct inhala- -tion technique al~o stored in ~AM contA~n~~ in ASIC
220. The microp~ r cont~;n6~ in ASIC 220 performs the compari~on of actual versus target value6 and depen~inq upon the result~ ~and~ stgnal~
to indicator LED's 106.
Upon completion of in~piration, ~sration of flow ie detected and measurement of time duration of breath hold beqins using the cal~ndar/clock module cont~in~ in ASIC 220.
Upon end o~ braath hold, patient p.f-~e~ pu~h button 104 which ~nA~ an evont ~ignal to micro-p~ or in ASIC 220 for ~torage in PAM and calcu-lation of breath-holding duration.
Re~t lts of the maneuver, incl~ ng breath holding performance are used to select textual or WO93/12823 PCT/~S~2/10804 ., ~ .
2 ~2 63~ ~ - 2~ -iconic feedback from a table stored in RAM contained in ASIC 220, in accordance with tec~ique~ which are well known for di~play to patient via LCD di~play s panel 108~ Note that text table c~n con ist of ~ultiple sections corresponding to differi~g la~guages.
After ~he inhalation m~neuver is complete, the device can pose questions to the patient on LCD
display 108 and answers such as "yes" or "no", or other answers corresron~ to the numb~r of ti~es the push button switch is activ2ted are input by the patient through pu h-button ~witoh 104.
A~ter a specifi~d time (long enough to per~it an additional ~ Arge of ~edication if there i~ to be on~) an o~y~L ~ignal from the mi~lo~ e_-or to the power ~o-,L~ol circuit cau~es the ~ystem to e~r 11 to sleep mode.
Data ~ro~ multiple maneuvers can b~ downloaded c~h~uently through ronn~ctor 221 into a clinical workctation or similar device for review by profes-sional including trend analysis within the se~ of ju~t downloaded data and comparison to previous period~.
Upon downlo~ g of data, records for individual maneuver~ are erased from the RA~
con~ne~in ~SIC 220, and battery 205 i8 checked for charge.
The site of compliance monitoring includQs a digital computer means (not shown) for communicating electronically with the microproce~-or ~eans 220 incorporated in the programmable inhaler~ The digital computer means at the monitoring site includes means for monitoring and i~oving a WO93/12823 2 1 2 6 3 3 1 PCT/U~92/108W
- 23 - ;
patient's medication compliance with the use o~ the hand-held i~haler~ The monitoring computer i8 lin~e~ with transmission ~ans for re~ote electronic retrieval of the data mea~ured by and storQd in the inhaler mi~Lo~oce~ror through data communication te~hn~gues which are well known, such as radio-freguency, optoelectronic communication, or the like. ', The monitoring computer is ~v~am~ed to evaluate the data received from the inhaler ~icro-proc~ror ~eane and to provide interpretations of the effectîveness of compl~ance efforts based on he retrie~ed data. The monitoring computer also includes a display mean~ for ffleaning~ul display of the compliance dataO Such di~pl y means preferably includes patient's projected target envelope for maximized delivery of ~edication ~ compared to the actual, m~a~ured performance of the patient.
It will be appr~ciatQd by tho~e ~killed in the art that there are a ~ultitude of methods for progra~ming the ~onitoring co~puter to achieve the evaluation of a pati~nt'~ medication compliance parameter~ which will maxi~izQ delivary of medica-tion to the large airways, s~all airway6, alveoli or any part of the respiratory tract. Thu8, the pr~ent m~thod is not intenA~ to be limitQd to ~
specific software impl~mentation for diagnosing a patient' 5 project~d compliancQ as a target ~nvelope of values and for mea~uring th~ actual performance of the patient with re~pect to the target envQlope.
In a preferred embodiment, the monitoring co~puter includes software which is readily p~v~Lammed by one skilled in the art to utilize data WO93/12823 PCT/US92/~0804 2~633~
input from diagnostic in~truments, diagno t~c tests, clinical records, clinical ob~ervation~, profes-sional opinions~ or the like in calculating a target envelope of inhalation para~eters which will ~axi-mize the delivery of aerosoliz~d medication to anyselected par~(.) of the re~piratory tr~ct of a particular patiant, or to indic~te o~her change~ in therapy such a~ type o~ medic~tion. The for~going data include quantifiable par~meters relating to thf~
physical condition of the airw~ys of a patient, such as the size of the patient'~ air p~s~age~.
The data are input into the ~onitoring computer as a table of value , or phy~ical para~eters indica tive of the condition and cArAr-lty of a patie~t's ~S air r~ eways and inhalation characteri~t~c~. The table of physical parameters are then ~apped to pxovide the target envelope of values, which if matched by the pat~ent's performancs, will m~xi~ize the distribution of the aero~ol mQdicat~on any selected parts of the respiratory tract. The moni-toring computer compares the patient's actual measured performance to the target envelope. The monitoring co~puter then communicates electronically with the mic~G~ or in the inhaler, ind a8 a func~ion of ~easured compliA~c~ par~meters, ~ o grams the microproc~or, ~f nec~Q~-~y, with differ-ent target inhalation profilQs, dosage 1eVQ1g or actuation event ti~es that will bring the pationt's performance within the target envelope and maximize ~he therapeUtiC '~r~
The advantages of the system dascribed herein over convantional devices may be sum~arized as ~ollows:
wos3/l28~ PCT/US92/10804 ~;
212S33~
(a~ the incorporation o~ both ~onitoring and '.
recording the patient's inhalation time cour e and related e~ents in a medicine inhaler device ~all and aesthetically pleasing eno~ to be u~ed during normal day-to-day activitie6, (b) the ability to load in a target perfor-mance en~elope for one or more inhalation ti~e/value csur es and/or one or ~ore ~elected variables (~uch as peak-flow rate) or to de ignate a 3peci~ied generic curve, (c) the ability to -~nre whether the device ha~ been c~ken properly prior to ~irc~Arge of a dose of aero~oi, (d) the ability to provid~ ediate f~e~ck both during the inhalation and ~fterwards a~ to where the patient' 8 performance fit~ relative to the target-perfor~nce envelop~ and whether and whan inhalation values fell outside that envelope, (a) the ability to pr~vide f~Q~haçk to the patient as to what co~ tive ~ction, ~f any, ~hould be taken, (f) the ~bility to provide a signal to the patient prompting him or her to continue breath holding, (g) the ~bility to ha~e the patient record the ti~ing of the end of the br~ath-holding period, (h) the ~bility to store any of tha data ~
ob~ne~, i (i~ the ability to download longi~ n~l results from the Intelligent Inhaler into a health-care ~ L~t~on or similar device, and (~) the ability for th~ healthcare profes-sional to review a patient's medicine usage for the ~,~?,63 ~
entire period between office visit~, and therefore revi~w trend~ in the patient's conditlon in the context of a detailed hi~torical record of the actual delivery of medication to its target ~ites of action in the lungsO
It ~hould be ~oted that all of the above capa-bilities wQuld not nece~fi~r~ly be included in every implementation of the 5y5te~.
The device and method described here are not limited to usage with any one pharmaceutical. They may be used with locally acting respiratory drug~
including bronchodilators, corticosteroids, anticho-linergics, antibiotics, and others, as well a~ with systemically acting drugs. Differing com~o~.~ may require v2riation in prescribed usage, including change6 în the inspiratory flow pattern. Such patterns may be oho~en in order to direct the roncentration of drug deposition at di~fer~nt sites within ~he respiratory tract, or compen~ate for varia_ions in patient'~ airways ~orphology due to di3e~-e or trau~a.
Claims (10)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. A hand-held, portable inhaler device, comprising;
a delivery means, which upon actuation, releases a meter dose of aerosolized medication from an associated pressurized canister;
an electronic sensor means for continuous measurement of air flow through a channel;
a mouthpiece leading to the channel which leads to the delivery means;
a means for storage of data including relative time of actuation of the delivery means, and data representative of duration of inspiration through the channel;
a means for performing logical operations or interpretive calculations on the data; and a motion sensor means for detecting if the associated canister has been shaken prior to actuation of the delivery means.
a delivery means, which upon actuation, releases a meter dose of aerosolized medication from an associated pressurized canister;
an electronic sensor means for continuous measurement of air flow through a channel;
a mouthpiece leading to the channel which leads to the delivery means;
a means for storage of data including relative time of actuation of the delivery means, and data representative of duration of inspiration through the channel;
a means for performing logical operations or interpretive calculations on the data; and a motion sensor means for detecting if the associated canister has been shaken prior to actuation of the delivery means.
2. The device of Claim 1, further comprising;
a signaling means, responsive to the means for performing, for providing feedback to a user, wherein the feedback expresses to a user whether the delivery means has been used correctly.
a signaling means, responsive to the means for performing, for providing feedback to a user, wherein the feedback expresses to a user whether the delivery means has been used correctly.
3. The device of Claim 2, wherein the signaling means for signaling to a user a scheduled time for activating the delivery means.
4. The device of Claim 1, further comprising;
a means associated with the means for storage of data for retaining recorded data from multiple delivery activation events; and a means for later retrieval of the data for review by a healthcare professional.
a means associated with the means for storage of data for retaining recorded data from multiple delivery activation events; and a means for later retrieval of the data for review by a healthcare professional.
5. A device according to Claim 2, wherein a target envelope pattern representing the time course of an effective inspiration is stored in the storage means for comparison to actual inspiration patterns, whereby such comparison is used to govern feedback supplied.
6. A device according to Claim 2, wherein feedback to the user includes specific advice in the form of textual messages and/or labeled indicator lights as to the type of corrective action necessary for effective use of device.
7. A device according to Claim 1, wherein the means for performing logical operations further comprises a means for recording timing of the end of a post-inspiratory breathhold period.
8. A device according to Claim 1, wherein the mouthpiece is connected to the device such that rotation or removal of the mouthpiece turns the device on or off electrically.
9. The device of Claim 1, wherein the mouthpiece comprises a cover which upon rotation or removal activates the electronic functions.
10. A hand-held, portable inhaler device, comprising;
a delivery means, which upon actuation, releases a meter dose of aerosolized medication from an associated pressurized canister;
an electronic sensor means for continuous measurement of air flow through a channel;
a mouthpiece leading to the channel which leads to the delivery mechanism, the mouthpiece being connected to the device in a manner such that movement of the mouthpiece by the user results in electronically turning the device on or off;
a means for storage of data including relative time of actuation of the delivery means, and data representative of duration of inspiration through the channel; and a means for performing logical operations or interpretive calculations on the data.
a delivery means, which upon actuation, releases a meter dose of aerosolized medication from an associated pressurized canister;
an electronic sensor means for continuous measurement of air flow through a channel;
a mouthpiece leading to the channel which leads to the delivery mechanism, the mouthpiece being connected to the device in a manner such that movement of the mouthpiece by the user results in electronically turning the device on or off;
a means for storage of data including relative time of actuation of the delivery means, and data representative of duration of inspiration through the channel; and a means for performing logical operations or interpretive calculations on the data.
Applications Claiming Priority (2)
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US811,398 | 1977-06-29 | ||
US07/811,398 US5363842A (en) | 1991-12-20 | 1991-12-20 | Intelligent inhaler providing feedback to both patient and medical professional |
Publications (2)
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CA2126331A1 CA2126331A1 (en) | 1993-07-08 |
CA2126331C true CA2126331C (en) | 1999-01-19 |
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Application Number | Title | Priority Date | Filing Date |
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CA002126331A Expired - Fee Related CA2126331C (en) | 1991-12-20 | 1992-12-18 | Intelligent inhaler providing feedback to both patient and medical professional |
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US (1) | US5363842A (en) |
EP (1) | EP0617628B1 (en) |
JP (1) | JP3085586B2 (en) |
AT (1) | ATE166236T1 (en) |
CA (1) | CA2126331C (en) |
DE (1) | DE69225604T2 (en) |
WO (1) | WO1993012823A2 (en) |
Families Citing this family (453)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB8909891D0 (en) * | 1989-04-28 | 1989-06-14 | Riker Laboratories Inc | Device |
DE69430303T2 (en) * | 1991-03-05 | 2002-11-28 | Aradigm Corp | METHOD AND DEVICE FOR CORRECTING A ZERO SIGNAL OF A PRESSURE SENSOR FOR A FLOW METER |
US5404871A (en) * | 1991-03-05 | 1995-04-11 | Aradigm | Delivery of aerosol medications for inspiration |
AU662919B2 (en) * | 1991-07-02 | 1995-09-21 | Inhale, Inc. | Method and device for delivering aerosolized medicaments |
US6681767B1 (en) | 1991-07-02 | 2004-01-27 | Nektar Therapeutics | Method and device for delivering aerosolized medicaments |
US5507277A (en) * | 1993-01-29 | 1996-04-16 | Aradigm Corporation | Lockout device for controlled release of drug from patient-activateddispenser |
US5743250A (en) | 1993-01-29 | 1998-04-28 | Aradigm Corporation | Insulin delivery enhanced by coached breathing |
US5915378A (en) * | 1993-01-29 | 1999-06-29 | Aradigm Corporation | Creating an aerosolized formulation of insulin |
US5819726A (en) * | 1993-01-29 | 1998-10-13 | Aradigm Corporation | Method for the delivery of aerosolized drugs to the lung for the treatment of respiratory disease |
US6131567A (en) * | 1993-01-29 | 2000-10-17 | Aradigm Corporation | Method of use of monomeric insulin as a means for improving the reproducibility of inhaled insulin |
US6024090A (en) | 1993-01-29 | 2000-02-15 | Aradigm Corporation | Method of treating a diabetic patient by aerosolized administration of insulin lispro |
US5873358A (en) * | 1993-01-29 | 1999-02-23 | Aradigm Corporation | Method of maintaining a diabetic patient's blood glucose level in a desired range |
US5694919A (en) * | 1993-01-29 | 1997-12-09 | Aradigm Corporation | Lockout device for controlled release of drug from patient-activated dispenser |
US5934272A (en) * | 1993-01-29 | 1999-08-10 | Aradigm Corporation | Device and method of creating aerosolized mist of respiratory drug |
US5724957A (en) * | 1993-01-29 | 1998-03-10 | Aradigm Corporation | Intrapulmonary delivery of narcotics |
US5888477A (en) * | 1993-01-29 | 1999-03-30 | Aradigm Corporation | Use of monomeric insulin as a means for improving the bioavailability of inhaled insulin |
US5558085A (en) * | 1993-01-29 | 1996-09-24 | Aradigm Corporation | Intrapulmonary delivery of peptide drugs |
US6012450A (en) * | 1993-01-29 | 2000-01-11 | Aradigm Corporation | Intrapulmonary delivery of hematopoietic drug |
US5970973A (en) * | 1993-01-29 | 1999-10-26 | Aradigm Corporation | Method of delivering insulin lispro |
US6098620A (en) * | 1993-01-29 | 2000-08-08 | Aradigm Corporation | Device for aerosolizing narcotics |
FR2701399B1 (en) * | 1993-02-16 | 1995-03-31 | Valois | Portable spray device with actuation triggered by inhalation. |
CH686872A5 (en) * | 1993-08-09 | 1996-07-31 | Disetronic Ag | Medical Inhalationsgeraet. |
US5505195A (en) * | 1993-09-16 | 1996-04-09 | Medtrac Technologies Inc. | Dry powder inhalant device with dosage and air flow monitor |
US5505192A (en) * | 1993-11-12 | 1996-04-09 | New-Med Corporation | Dispenser monitoring system |
US6390088B1 (en) | 1993-12-13 | 2002-05-21 | Boehringer Ingelheim Kg | Aerosol inhaler |
DE4422710C1 (en) * | 1994-06-29 | 1995-09-14 | Boehringer Ingelheim Kg | Inhaler with storage container for aerosol |
DE69424992T2 (en) * | 1994-02-14 | 2000-10-26 | Aradigm Corp | Inhalation exercise device |
SE9400570D0 (en) * | 1994-02-21 | 1994-02-21 | Astra Ab | Inhalation device, inhaler and processing unit |
US5839429A (en) * | 1994-03-25 | 1998-11-24 | Astra Aktiebolag | Method and apparatus in connection with an inhaler |
SE9401020D0 (en) * | 1994-03-25 | 1994-03-25 | Astra Ab | Method and apparatus in connection with an inhaler |
US5482030A (en) * | 1994-06-13 | 1996-01-09 | Klein; David | Aerosol and non-aerosol spray counter |
SE503415C2 (en) * | 1994-07-05 | 1996-06-10 | Aiolos Medicinsk Teknik Ab | Method and apparatus for introducing an active substance into a person's respiratory system |
US5509404A (en) * | 1994-07-11 | 1996-04-23 | Aradigm Corporation | Intrapulmonary drug delivery within therapeutically relevant inspiratory flow/volume values |
JP3706136B2 (en) | 1994-09-21 | 2005-10-12 | ネクター セラピューティクス | Apparatus and method for dispersing dry powder drug |
US5522385A (en) * | 1994-09-27 | 1996-06-04 | Aradigm Corporation | Dynamic particle size control for aerosolized drug delivery |
GB9421687D0 (en) * | 1994-10-27 | 1994-12-14 | Aid Medic Ltd | Dosimetric spacer |
US5495848A (en) * | 1994-11-25 | 1996-03-05 | Nellcar Puritan Bennett | Monitoring system for delivery of therapeutic gas |
US5544647A (en) * | 1994-11-29 | 1996-08-13 | Iep Group, Inc. | Metered dose inhalator |
US5622163A (en) * | 1994-11-29 | 1997-04-22 | Iep Group, Inc. | Counter for fluid dispensers |
AU701843B2 (en) * | 1995-03-14 | 1999-02-04 | Siemens Aktiengesellschaft | Removable precision dosating unit for ultrasonic atomizer device |
ATE186222T1 (en) * | 1995-03-14 | 1999-11-15 | Siemens Ag | ULTRASONIC ATOMIZER WITH REMOVABLE PRECISION DOSING UNIT |
JPH11502845A (en) * | 1995-03-31 | 1999-03-09 | アラディグム コーポレーション | Pulmonary delivery of hematopoietic agents |
USD377215S (en) * | 1995-04-13 | 1997-01-07 | Glaxo Group Limited | Inhaler |
WO1996032099A1 (en) * | 1995-04-14 | 1996-10-17 | Glaxo Wellcome Inc. | Metered dose inhaler for albuterol |
RO119117B1 (en) * | 1995-04-14 | 2004-04-30 | Glaxo Wellcome Inc. | Fixed dose inhaler for fluticasone propionate |
US6029659A (en) * | 1995-04-17 | 2000-02-29 | Solar Shield Corporation | Inhalation device with counter |
US5809997A (en) * | 1995-05-18 | 1998-09-22 | Medtrac Technologies, Inc. | Electronic medication chronolog device |
US5921232A (en) * | 1995-07-12 | 1999-07-13 | A & D Company Limited | Handy type inhaler |
US5758638A (en) * | 1995-07-24 | 1998-06-02 | Kreamer; Jeffry W. | Indicator for a medicament inhaler |
US6034622A (en) * | 1995-08-18 | 2000-03-07 | Robert A. Levine | Location monitoring via implanted radio transmitter |
IT1276916B1 (en) * | 1995-10-12 | 1997-11-03 | Istoria Farmaceutici S P A | DEVICE FOR THE TREATMENT OF ASTHMATIC PATIENTS, ABLE TO MEASURE PEAK EXPIRATORY FLOW AND DELIVERY DRUGS FOR THE |
US5724986A (en) * | 1995-11-06 | 1998-03-10 | Jones Medical Instrument Co. | Casing and spirometer for metered dose inhaler |
GB2340407B (en) * | 1995-11-06 | 2000-04-05 | William Cunningham Jones Jr | Casing for metered dose inhaler |
US5833066A (en) * | 1996-01-02 | 1998-11-10 | Inhalermate, Llc | Carrying case for oral and nasal inhalation devices with counting mechanism |
US5823179A (en) | 1996-02-13 | 1998-10-20 | 1263152 Ontario Inc. | Nebulizer apparatus and method |
US5676129A (en) * | 1996-03-14 | 1997-10-14 | Oneida Research Services, Inc. | Dosage counter for metered dose inhaler (MDI) systems using a miniature pressure sensor |
US5839430A (en) * | 1996-04-26 | 1998-11-24 | Cama; Joseph | Combination inhaler and peak flow rate meter |
US5957125A (en) * | 1996-11-05 | 1999-09-28 | Medical Safety Products, Inc. | Apparatus for indicating proper orientation for oral and nasal inhalers |
US5890490A (en) * | 1996-11-29 | 1999-04-06 | Aylsworth; Alonzo C. | Therapeutic gas flow monitoring system |
US6024089A (en) | 1997-03-14 | 2000-02-15 | Nelcor Puritan Bennett Incorporated | System and method for setting and displaying ventilator alarms |
US5794612A (en) * | 1997-04-02 | 1998-08-18 | Aeromax Technologies, Inc. | MDI device with ultrasound sensor to detect aerosol dispensing |
US5865172A (en) * | 1997-04-08 | 1999-02-02 | The Board Of Regents Of The University Of Texas System | Method and apparatus for induction of inhaled pharmacological agent by a pediatric patient |
US5937852A (en) * | 1997-04-08 | 1999-08-17 | The Board Of Regents Of The University Of Texas System | Apparatus for induction of inhaled pharmacological agent by a pediatric patient |
US5911219A (en) * | 1997-04-18 | 1999-06-15 | Aylsworth; Alonzo C. | Therapeutic gas flow meter and monitor |
US6571790B1 (en) | 1997-05-12 | 2003-06-03 | Robert E. Weinstein | Method and device for organizing and coordinating the combined use of liquid medications for continuous nebulization for the treatment of respiratory disorders |
US5941241A (en) * | 1997-05-12 | 1999-08-24 | Weinstein; Robert E. | Method and device for organizing and coordinating the combined use of topical aerosols for the treatment of respiratory disorders |
TW533865U (en) * | 1997-06-10 | 2003-05-21 | Glaxo Group Ltd | Dispenser for dispensing medicament and actuation indicating device |
US6135106A (en) * | 1997-08-22 | 2000-10-24 | Nellcor Puritan-Bennett, Inc. | CPAP pressure and flow transducer |
US6142149A (en) * | 1997-10-23 | 2000-11-07 | Steen; Scot Kenneth | Oximetry device, open oxygen delivery system oximetry device and method of controlling oxygen saturation |
US6192876B1 (en) | 1997-12-12 | 2001-02-27 | Astra Aktiebolag | Inhalation apparatus and method |
US6142339A (en) | 1998-01-16 | 2000-11-07 | 1263152 Ontario Inc. | Aerosol dispensing device |
EP1449557B1 (en) | 1998-01-16 | 2016-09-07 | Trudell Medical International | Dispensing device kit |
SE9801122D0 (en) * | 1998-03-30 | 1998-03-30 | Astra Ab | Inhalation device |
US6578571B1 (en) | 1998-04-20 | 2003-06-17 | Infamed Ltd. | Drug delivery device and methods therefor |
US6336453B1 (en) | 1999-04-30 | 2002-01-08 | Trudell Medical International | Indicating device for aerosol container |
US6729330B2 (en) | 1998-05-05 | 2004-05-04 | Trudell Medical International | Indicating device for aerosol container |
US6082358A (en) | 1998-05-05 | 2000-07-04 | 1263152 Ontario Inc. | Indicating device for aerosol container |
US7565905B2 (en) * | 1998-06-03 | 2009-07-28 | Scott Laboratories, Inc. | Apparatuses and methods for automatically assessing and monitoring a patient's responsiveness |
CN1311877C (en) * | 1998-06-03 | 2007-04-25 | 斯科特实验室公司 | Apparatus and method for providing a conscious patient relief from pain and anxiety associated with medical or surgical procedures |
US6257233B1 (en) | 1998-06-04 | 2001-07-10 | Inhale Therapeutic Systems | Dry powder dispersing apparatus and methods for their use |
US6152130A (en) * | 1998-06-12 | 2000-11-28 | Microdose Technologies, Inc. | Inhalation device with acoustic control |
ES2253898T3 (en) * | 1998-06-12 | 2006-06-01 | Microdose Technologies Inc. | DEVICE FOR THE ADMINISTRATION OF PHARMACOS AND MEDICINES. |
US6142146A (en) * | 1998-06-12 | 2000-11-07 | Microdose Technologies, Inc. | Inhalation device |
US6260549B1 (en) | 1998-06-18 | 2001-07-17 | Clavius Devices, Inc. | Breath-activated metered-dose inhaler |
WO2000012162A1 (en) * | 1998-08-28 | 2000-03-09 | Glaxo Group Limited | Dispenser |
DE19840748A1 (en) * | 1998-09-08 | 2000-03-09 | Brigitte Schneider | Spray bottle with timer |
CN1320058A (en) * | 1998-09-24 | 2001-10-31 | 阿斯特拉曾尼卡有限公司 | Improved inhaler |
US6564797B1 (en) * | 1998-09-30 | 2003-05-20 | Respironics, Inc. | Interactive pressure support system and method |
CA2351398A1 (en) * | 1998-11-30 | 2000-06-08 | Abbott Laboratories | Analyte test instrument having improved calibration and communication processes |
FI110065B (en) * | 1998-12-08 | 2002-11-29 | Instrumentarium Oyj | Device in a feedback control system |
FI982652A (en) * | 1998-12-08 | 2000-06-09 | Instrumentarium Oyj | Arrangement in connection with the equipment used in patient care |
GB2344533B (en) * | 1998-12-11 | 2000-10-18 | Bespak Plc | Improvements in or relating to dispensing apparatus |
US6397838B1 (en) * | 1998-12-23 | 2002-06-04 | Battelle Pulmonary Therapeutics, Inc. | Pulmonary aerosol delivery device and method |
US6116234A (en) * | 1999-02-01 | 2000-09-12 | Iep Pharmaceutical Devices Inc. | Metered dose inhaler agitator |
JP4712193B2 (en) * | 1999-03-06 | 2011-06-29 | グラクソ グループ リミテッド | Drug delivery system |
US6202642B1 (en) | 1999-04-23 | 2001-03-20 | Medtrac Technologies, Inc. | Electronic monitoring medication apparatus and method |
GB9911388D0 (en) * | 1999-05-18 | 1999-07-14 | Glaxo Group Ltd | Dispenser |
US9006175B2 (en) | 1999-06-29 | 2015-04-14 | Mannkind Corporation | Potentiation of glucose elimination |
DE19942080A1 (en) * | 1999-09-03 | 2001-03-08 | Inamed Gmbh | Inhaler |
AU7780700A (en) * | 1999-10-01 | 2001-05-10 | Glaxo Group Limited | Remote patient assessment system |
MXPA02003784A (en) * | 1999-10-16 | 2002-12-13 | Glaxo Group Ltd | Device housing for an aerosol container. |
GB9930374D0 (en) * | 1999-12-22 | 2000-02-16 | 3M Innovative Properties Co | Refillable device with counting means |
AU2001235009B2 (en) * | 2000-02-11 | 2004-10-07 | Respironics Respiratory Drug Delivery (Uk) Ltd | Drug delivery apparatus |
US8820316B2 (en) | 2000-02-11 | 2014-09-02 | Respironics Respiratory Drug Delivery (Uk) Ltd | Drug delivery apparatus |
GB0003197D0 (en) * | 2000-02-11 | 2000-04-05 | Aid Medic Ltd | Improvements in and relating to controlling drug delivery |
GB0003839D0 (en) * | 2000-02-19 | 2000-04-05 | Glaxo Group Ltd | Housing for an inhaler |
GB0004456D0 (en) * | 2000-02-26 | 2000-04-19 | Glaxo Group Ltd | Medicament dispenser |
DE10013093B4 (en) | 2000-03-17 | 2005-12-22 | Inamed Gmbh | Device for the controlled inhalation of therapeutic aerosols |
GB0012465D0 (en) * | 2000-05-24 | 2000-07-12 | Glaxo Group Ltd | Monitoring method |
GB0013619D0 (en) * | 2000-06-06 | 2000-07-26 | Glaxo Group Ltd | Sample container |
IL137185A (en) * | 2000-07-05 | 2009-09-01 | Asaf Halamish | Aerosol inhalation interface |
AU2001285825A1 (en) * | 2000-07-15 | 2002-01-30 | Glaxo Group Limited | Medicament dispenser |
AU2001293226A1 (en) * | 2000-08-28 | 2002-03-13 | Healthtech, Inc. | Respiratory gas sensors in flow path |
US6435175B1 (en) * | 2000-08-29 | 2002-08-20 | Sensormedics Corporation | Pulmonary drug delivery device |
JP2004510556A (en) * | 2000-10-09 | 2004-04-08 | シーメンス アクチエンゲゼルシヤフト | Drug supply device |
GB2368061B (en) * | 2000-10-20 | 2005-05-11 | Gw Pharmaceuticals Ltd | Dose dispensing apparatus |
AU2003268831B2 (en) * | 2000-11-30 | 2006-12-07 | Canon Kabushiki Kaisha | Portable Terminal and Health Management Method and System Using Portable Terminal |
JP4332293B2 (en) * | 2000-11-30 | 2009-09-16 | キヤノン株式会社 | Inhalation device and discharge head control method |
EP2384782A1 (en) * | 2000-11-30 | 2011-11-09 | Canon Kabushiki Kaisha | Portable terminal and health management method and system using portable terminal |
JP4454834B2 (en) * | 2000-11-30 | 2010-04-21 | キヤノン株式会社 | System and method for health management using portable terminal |
US7073499B1 (en) | 2001-02-06 | 2006-07-11 | Injet Digital Aerosols Limited | Inhaler with airflow regulation |
CA2809180C (en) * | 2001-03-20 | 2015-06-02 | Trudell Medical International | Nebulizer apparatus with an adjustable fluid orifice |
FR2823730B1 (en) * | 2001-04-24 | 2003-12-12 | Valois Sa | FLUID PRODUCT DISPENSING DEVICE |
WO2002087673A1 (en) * | 2001-04-25 | 2002-11-07 | Messer Austria Gmbh | Aerosol dosing device |
GB0111337D0 (en) * | 2001-05-10 | 2001-07-04 | Innovata Biomed Ltd | Device |
US6745760B2 (en) | 2001-05-15 | 2004-06-08 | Trudell Medical International | Medicament applicator |
DE10123749A1 (en) * | 2001-05-16 | 2002-12-12 | Inamed Gmbh | Aerosol delivery device |
US20030051728A1 (en) | 2001-06-05 | 2003-03-20 | Lloyd Peter M. | Method and device for delivering a physiologically active compound |
US7645442B2 (en) | 2001-05-24 | 2010-01-12 | Alexza Pharmaceuticals, Inc. | Rapid-heating drug delivery article and method of use |
US20070122353A1 (en) | 2001-05-24 | 2007-05-31 | Hale Ron L | Drug condensation aerosols and kits |
US7458374B2 (en) | 2002-05-13 | 2008-12-02 | Alexza Pharmaceuticals, Inc. | Method and apparatus for vaporizing a compound |
US6735477B2 (en) | 2001-07-09 | 2004-05-11 | Robert A. Levine | Internal monitoring system with detection of food intake |
WO2003008026A2 (en) * | 2001-07-16 | 2003-01-30 | Pneumoflex Systems, L.L.C. | Apparatus for self-induced cough-cardiopulmonary resuscitation |
CA2459867C (en) | 2001-09-06 | 2012-03-13 | Microdose Technologies, Inc. | Adaptors for inhalers to improve performance |
DE10146815B4 (en) * | 2001-09-18 | 2005-05-04 | Ing. Erich Pfeiffer Gmbh | Donor for media |
WO2003026558A2 (en) * | 2001-09-24 | 2003-04-03 | Scott Laboratories, Inc. | Methods and apparatuses for assuring quality and safety of drug administration and medical products and kits |
US20030101076A1 (en) * | 2001-10-02 | 2003-05-29 | Zaleski John R. | System for supporting clinical decision making through the modeling of acquired patient medical information |
EP1304131B1 (en) * | 2001-10-18 | 2005-06-29 | PARI GmbH Spezialisten für effektive Inhalation | Inhalator |
US6933850B2 (en) * | 2001-11-09 | 2005-08-23 | Valois S.A.S. | Fluid product distribution device and distributor comprising such a device |
US6684880B2 (en) * | 2001-12-04 | 2004-02-03 | Hewlett-Packard Development Company, L.P. | Applicator for dispensing bioactive compositions and methods for using the same |
US6994083B2 (en) | 2001-12-21 | 2006-02-07 | Trudell Medical International | Nebulizer apparatus and method |
US7458373B2 (en) * | 2002-01-15 | 2008-12-02 | Philip Morris Usa Inc. | Aerosol generator for drug formulation |
US6772756B2 (en) * | 2002-02-09 | 2004-08-10 | Advanced Inhalation Revolutions Inc. | Method and system for vaporization of a substance |
US6651844B2 (en) | 2002-02-22 | 2003-11-25 | Schering Corporation | Spray dispenser counter |
EP1894591B1 (en) | 2002-03-20 | 2013-06-26 | MannKind Corporation | Cartridge for an inhalation apparatus |
US7004164B2 (en) | 2002-03-21 | 2006-02-28 | Trudell Medical International | Indicating device for aerosol container |
US6830046B2 (en) * | 2002-04-29 | 2004-12-14 | Hewlett-Packard Development Company, L.P. | Metered dose inhaler |
GB0209782D0 (en) * | 2002-04-29 | 2002-06-05 | Glaxo Group Ltd | Medicament dispenser |
WO2003092576A2 (en) * | 2002-04-29 | 2003-11-13 | Glaxo Group Limited | Alerting system |
US20030205226A1 (en) | 2002-05-02 | 2003-11-06 | Pre Holding, Inc. | Aerosol medication inhalation system |
US20030221687A1 (en) * | 2002-05-09 | 2003-12-04 | William Kaigler | Medication and compliance management system and method |
US6889690B2 (en) | 2002-05-10 | 2005-05-10 | Oriel Therapeutics, Inc. | Dry powder inhalers, related blister devices, and associated methods of dispensing dry powder substances and fabricating blister packages |
US7118010B2 (en) * | 2002-05-10 | 2006-10-10 | Oriel Therapeutics, Inc. | Apparatus, systems and related methods for dispensing and /or evaluating dry powders |
US6985798B2 (en) * | 2002-05-10 | 2006-01-10 | Oriel Therapeutics, Inc. | Dry powder dose filling systems and related methods |
US7677411B2 (en) | 2002-05-10 | 2010-03-16 | Oriel Therapeutics, Inc. | Apparatus, systems and related methods for processing, dispensing and/or evaluatingl dry powders |
US6904908B2 (en) | 2002-05-21 | 2005-06-14 | Trudell Medical International | Visual indicator for an aerosol medication delivery apparatus and system |
CN100591378C (en) | 2002-06-27 | 2010-02-24 | 奥里尔治疗公司 | Dry powder dose filling systems and related methods |
GB0216831D0 (en) * | 2002-07-19 | 2002-08-28 | Glaxo Group Ltd | Medicament dispenser |
DE10243371B4 (en) * | 2002-09-18 | 2006-06-14 | Pari GmbH Spezialisten für effektive Inhalation | Aeorosoltherapiegerät |
US6886557B2 (en) * | 2002-10-31 | 2005-05-03 | Hewlett-Packard Development Company, L.P. | Inhalation device and method for delivering variable amounts of different components |
US6904907B2 (en) * | 2002-11-19 | 2005-06-14 | Honeywell International Inc. | Indirect flow measurement through a breath-operated inhaler |
GB2396825B (en) * | 2002-11-20 | 2004-12-08 | Profile Respiratory Systems Lt | Improved inhalation method and apparatus |
GB2395437C (en) * | 2002-11-20 | 2010-10-20 | Profile Respiratory Systems Ltd | Improved inhalation method and apparatus |
US7913688B2 (en) * | 2002-11-27 | 2011-03-29 | Alexza Pharmaceuticals, Inc. | Inhalation device for producing a drug aerosol |
US7189204B2 (en) | 2002-12-04 | 2007-03-13 | Cardiac Pacemakers, Inc. | Sleep detection using an adjustable threshold |
US7185650B2 (en) * | 2002-12-19 | 2007-03-06 | Arie Huber | Systems and methods for determining a minimum effective dose of an inhaled drug for an individual patient at a given time |
AU2003299788A1 (en) * | 2002-12-27 | 2004-07-29 | Scott Laboratories, Inc. | Apparatuses and methods for automatically assessing and monitoring a patient's responsiveness |
GB0301366D0 (en) * | 2003-01-21 | 2003-02-19 | Glaxo Group Ltd | A fixation device |
GB2397527A (en) | 2003-01-23 | 2004-07-28 | David Wald | Angina medication dose dispenser with log and analysis means for the diagnosis of risk of myocardial infartion |
GB2398250A (en) * | 2003-02-11 | 2004-08-18 | Bespak Plc | Inhaler with display and single operating button |
US7726303B2 (en) * | 2003-02-25 | 2010-06-01 | Hewlett-Packard Development Company, L.P. | Controlled medicament ejection |
US6910481B2 (en) | 2003-03-28 | 2005-06-28 | Ric Investments, Inc. | Pressure support compliance monitoring system |
GB2400565B (en) * | 2003-04-17 | 2005-03-02 | Bespak Plc | Nasal drug delivery |
WO2004096110A2 (en) * | 2003-04-28 | 2004-11-11 | Chi, Llc | Pursed lip breathing device |
US20040255936A1 (en) * | 2003-04-30 | 2004-12-23 | David Urbanus | Disposable metered dose inhaler with integrated electronic counter |
GB0311461D0 (en) * | 2003-05-19 | 2003-06-25 | Glaxo Group Ltd | Display system |
JP2007516404A (en) | 2003-05-21 | 2007-06-21 | アレックザ ファーマシューティカルズ, インコーポレイテッド | Optically or electrically ignited built-in heating unit and drug supply unit using the same |
US20050022815A1 (en) * | 2003-06-25 | 2005-02-03 | Sunrise Medical Hhg Inc. | Apparatus and method for monitoring supplemental oxygen usage |
GB0316355D0 (en) * | 2003-07-11 | 2003-08-13 | Glaxo Group Ltd | A dispenser |
US20050028815A1 (en) * | 2003-07-23 | 2005-02-10 | Deaton Daniel M. | Apparatus for electronic dosage counter |
US7270123B2 (en) * | 2003-08-13 | 2007-09-18 | Trudell Medical International | Nebulizer apparatus and method |
US7662101B2 (en) | 2003-09-18 | 2010-02-16 | Cardiac Pacemakers, Inc. | Therapy control based on cardiopulmonary status |
US8606356B2 (en) | 2003-09-18 | 2013-12-10 | Cardiac Pacemakers, Inc. | Autonomic arousal detection system and method |
US8002553B2 (en) | 2003-08-18 | 2011-08-23 | Cardiac Pacemakers, Inc. | Sleep quality data collection and evaluation |
US7610094B2 (en) | 2003-09-18 | 2009-10-27 | Cardiac Pacemakers, Inc. | Synergistic use of medical devices for detecting medical disorders |
US7575553B2 (en) * | 2003-09-18 | 2009-08-18 | Cardiac Pacemakers, Inc. | Methods and systems for assessing pulmonary disease |
US7887493B2 (en) | 2003-09-18 | 2011-02-15 | Cardiac Pacemakers, Inc. | Implantable device employing movement sensing for detecting sleep-related disorders |
US20050172958A1 (en) * | 2003-08-20 | 2005-08-11 | The Brigham And Women's Hospital, Inc. | Inhalation device and system for the remote monitoring of drug administration |
GB2406283B (en) * | 2003-09-24 | 2006-04-05 | Altana Pharma Ag | Compliance monitor and method |
US7342660B2 (en) * | 2003-09-25 | 2008-03-11 | Deka Products Limited Partnership | Detection system and method for aerosol delivery |
US7377277B2 (en) | 2003-10-27 | 2008-05-27 | Oriel Therapeutics, Inc. | Blister packages with frames and associated methods of fabricating dry powder drug containment systems |
US7451761B2 (en) | 2003-10-27 | 2008-11-18 | Oriel Therapeutics, Inc. | Dry powder inhalers, related blister package indexing and opening mechanisms, and associated methods of dispensing dry powder substances |
US7621273B2 (en) | 2003-10-28 | 2009-11-24 | Trudell Medical International | Indicating device with warning dosage indicator |
EP1694392A4 (en) * | 2003-11-25 | 2008-05-14 | Robert E Coifman | Devices for measuring inspiratory airflow |
US7100530B2 (en) | 2003-12-15 | 2006-09-05 | Trudell Medical International, Inc. | Dose indicating device |
US7819115B2 (en) * | 2004-01-30 | 2010-10-26 | Hewlett-Packard Development Company, L.P. | Inhalers and methods of controlling airflow in inhalers |
US7380550B2 (en) * | 2004-01-30 | 2008-06-03 | Hewlett-Packard Development Company, L.P. | Systems and methods for particle detection |
US7467630B2 (en) * | 2004-02-11 | 2008-12-23 | Hewlett-Packard Development Company, L.P. | Medicament dispenser |
US7481213B2 (en) * | 2004-02-11 | 2009-01-27 | Hewlett-Packard Development Company, L.P. | Medicament dispenser |
US9022027B2 (en) * | 2004-02-20 | 2015-05-05 | Pneumoflex Systems, Llc | Nebulizer with intra-oral vibrating mesh |
US8109266B2 (en) * | 2004-02-20 | 2012-02-07 | Pneumoflex Systems, Llc | Nebulizer having flow meter function |
CA2557020A1 (en) * | 2004-02-24 | 2005-09-01 | Boehringer Ingelheim International Gmbh | Atomiser |
DE102004009435A1 (en) * | 2004-02-24 | 2005-12-08 | Boehringer Ingelheim International Gmbh | atomizer |
JP2007524312A (en) * | 2004-02-26 | 2007-08-23 | ノボ・ノルデイスク・エー/エス | Method and system for secure pairing of wireless communication devices |
US7540286B2 (en) | 2004-06-03 | 2009-06-02 | Alexza Pharmaceuticals, Inc. | Multiple dose condensation aerosol devices and methods of forming condensation aerosols |
WO2005123165A1 (en) * | 2004-06-15 | 2005-12-29 | Novo Nordisk A/S | Inhalation breath assistant apparatus and method for assisting in inhalation therapies |
CN101010305B (en) | 2004-08-20 | 2010-08-11 | 曼金德公司 | Catalysis of diketopiperazine synthesis |
PL2322180T3 (en) | 2004-08-23 | 2015-10-30 | Mannkind Corp | Diketopiperazine salts for drug delivery |
US8210171B2 (en) * | 2004-09-13 | 2012-07-03 | Oriel Therapeutics, Inc. | Tubular dry powder drug containment systems, associated inhalers and methods |
US7543582B2 (en) | 2004-09-20 | 2009-06-09 | Trudell Medical International | Dose indicating device with display elements attached to container |
GB0422413D0 (en) * | 2004-10-08 | 2004-11-10 | Breath Ltd | High efficiency nebulisation |
WO2006045523A1 (en) * | 2004-10-21 | 2006-05-04 | Novo Nordisk A/S | Medication delivery system with a detector for providing a signal indicative of an amount of an ejected dose of drug |
DE602005018518D1 (en) | 2004-10-21 | 2010-02-04 | Novo Nordisk As | INJECTION DEVICE WITH A PROCESSOR FOR COLLECTING OUTPUT INFORMATION |
WO2006048417A1 (en) * | 2004-11-02 | 2006-05-11 | Novo Nordisk A/S | Inhalation therapy compliance tracking system and apparatus |
WO2006083876A2 (en) | 2005-02-01 | 2006-08-10 | Intelliject, Llc | Devices, systems, and methods for medicament delivery |
US7947017B2 (en) | 2004-11-22 | 2011-05-24 | Intelliject, Inc. | Devices, systems and methods for medicament delivery |
US7648483B2 (en) | 2004-11-22 | 2010-01-19 | Intelliject, Inc. | Devices, systems and methods for medicament delivery |
US10737028B2 (en) | 2004-11-22 | 2020-08-11 | Kaleo, Inc. | Devices, systems and methods for medicament delivery |
US7648482B2 (en) | 2004-11-22 | 2010-01-19 | Intelliject, Inc. | Devices, systems, and methods for medicament delivery |
CN101087625B (en) | 2004-11-22 | 2012-02-22 | 因特利杰克特有限公司 | Devices and systems for medicament delivery |
US11590286B2 (en) | 2004-11-22 | 2023-02-28 | Kaleo, Inc. | Devices, systems and methods for medicament delivery |
US20060130838A1 (en) * | 2004-12-20 | 2006-06-22 | Lee Yong Y | Data logger for monitoring asthmatic conditions |
US7832394B2 (en) * | 2004-12-22 | 2010-11-16 | Schechter Alan M | Apparatus for dispensing pressurized contents |
CA2899340A1 (en) | 2005-01-20 | 2006-07-27 | Trudell Medical International | Dispensing device |
US8231573B2 (en) | 2005-02-01 | 2012-07-31 | Intelliject, Inc. | Medicament delivery device having an electronic circuit system |
US8361026B2 (en) | 2005-02-01 | 2013-01-29 | Intelliject, Inc. | Apparatus and methods for self-administration of vaccines and other medicaments |
US7731686B2 (en) | 2005-02-01 | 2010-06-08 | Intelliject, Inc. | Devices, systems and methods for medicament delivery |
US8206360B2 (en) | 2005-02-01 | 2012-06-26 | Intelliject, Inc. | Devices, systems and methods for medicament delivery |
US9022980B2 (en) | 2005-02-01 | 2015-05-05 | Kaleo, Inc. | Medical injector simulation device |
GB0507100D0 (en) * | 2005-04-08 | 2005-05-11 | Team Holdings Uk Ltd | Improvements in or relating to inhalers |
JP2008539974A (en) * | 2005-05-12 | 2008-11-20 | コス・ライフ・サイエンセス・インコーポレイテツド | Dosage counter for metered dose inhalers |
WO2008048234A2 (en) * | 2005-08-26 | 2008-04-24 | North Carolina State University | Inhaler system for targeted maximum drug-aerosol delivery |
AU2006284832B2 (en) * | 2005-08-31 | 2011-06-02 | T2 Biosystems Inc. | NMR device for detection of analytes involving magnetic particles |
CN104324362B (en) | 2005-09-14 | 2018-04-24 | 曼金德公司 | Method for preparation of drug based on improving affinity of the active agent to crystalline microparticle surfaces |
US20070181119A1 (en) * | 2006-02-08 | 2007-08-09 | Weinstein Robert E | Inhaler Device |
CN104383546B (en) | 2006-02-22 | 2021-03-02 | 曼金德公司 | Method for improving the pharmaceutical properties of microparticles comprising diketopiperazines and an active agent |
BRPI0708856A2 (en) * | 2006-03-20 | 2011-06-14 | Novo Nordisk As | electronic module for mechanical dispensing devices |
US7675425B2 (en) * | 2006-04-10 | 2010-03-09 | Canon Kabushiki Kaisha | Liquid discharge device capable of self-diagnosis of discharge functions |
US7779835B2 (en) * | 2006-04-17 | 2010-08-24 | Canon Kabushiki Kaisha | Liquid ejection device |
US8021310B2 (en) | 2006-04-21 | 2011-09-20 | Nellcor Puritan Bennett Llc | Work of breathing display for a ventilation system |
ES2707548T3 (en) | 2006-05-15 | 2019-04-04 | United Therapeutics Corp | Administration of treprostinil using a metered dose inhaler |
DE102006026786A1 (en) * | 2006-06-07 | 2007-12-13 | Joachim Kern | metered dose inhaler |
WO2008008281A2 (en) | 2006-07-07 | 2008-01-17 | Proteus Biomedical, Inc. | Smart parenteral administration system |
US8141550B2 (en) | 2006-08-01 | 2012-03-27 | Trudell Medical International | Dispensing device |
US20080058772A1 (en) * | 2006-08-31 | 2008-03-06 | Robertson Timothy L | Personal paramedic |
US7535235B2 (en) * | 2006-09-04 | 2009-05-19 | Fluke Corporation | Integrated digital thermal air flow sensor |
US7784461B2 (en) | 2006-09-26 | 2010-08-31 | Nellcor Puritan Bennett Llc | Three-dimensional waveform display for a breathing assistance system |
US20080072896A1 (en) * | 2006-09-27 | 2008-03-27 | Nellcor Puritan Bennett Incorporated | Multi-Level User Interface for a Breathing Assistance System |
WO2008067254A2 (en) * | 2006-11-27 | 2008-06-05 | Abbott Respiratory Llc | Nasal drug delivery device and method |
WO2008091838A2 (en) | 2007-01-22 | 2008-07-31 | Intelliject, Inc. | Medical injector with compliance tracking and monitoring |
US20080210231A1 (en) * | 2007-01-31 | 2008-09-04 | Abbott Laboratories | Metered dose inhaler cleaning method and apparatus |
US8342172B2 (en) * | 2007-02-05 | 2013-01-01 | The Brigham And Women's Hospital, Inc. | Instrumented metered-dose inhaler and methods for predicting disease exacerbations |
WO2008112661A2 (en) | 2007-03-09 | 2008-09-18 | Alexza Pharmaceuticals, Inc. | Heating unit for use in a drug delivery device |
US7898407B2 (en) | 2007-03-30 | 2011-03-01 | Toronto Rehabilitation Institute | Hand hygiene compliance system |
US8237558B2 (en) | 2007-03-30 | 2012-08-07 | University Health Network | Hand hygiene compliance system |
US20080255874A1 (en) * | 2007-04-16 | 2008-10-16 | Cerner Innovation, Inc. | System and method for delivering clinical notifications |
JP2010529894A (en) | 2007-06-15 | 2010-09-02 | スパンドーファー,マイケル | Drug delivery and monitoring system for ventilators |
US8297280B2 (en) * | 2007-07-20 | 2012-10-30 | Canon Kabushiki Kaisha | Inhaler |
WO2011163272A1 (en) | 2010-06-21 | 2011-12-29 | Mannkind Corporation | Dry powder drug delivery system and methods |
WO2009055733A1 (en) | 2007-10-25 | 2009-04-30 | Proteus Biomedical, Inc. | Fluid transfer port information system |
WO2009067463A1 (en) | 2007-11-19 | 2009-05-28 | Proteus Biomedical, Inc. | Body-associated fluid transport structure evaluation devices |
WO2009079078A1 (en) | 2007-12-14 | 2009-06-25 | Labogroup S.A.S. | Delivering aerosolizable food products |
JP2009195669A (en) * | 2008-01-25 | 2009-09-03 | Canon Inc | Medicine ejection apparatus and control method thereof |
US9550031B2 (en) * | 2008-02-01 | 2017-01-24 | Reciprocal Labs Corporation | Device and method to monitor, track, map, and analyze usage of metered-dose inhalers in real-time |
US8082873B2 (en) | 2008-05-05 | 2011-12-27 | Trudell Medical International | Drive mechanism for an indicating device |
USD994111S1 (en) | 2008-05-12 | 2023-08-01 | Kaleo, Inc. | Medicament delivery device cover |
US8021344B2 (en) * | 2008-07-28 | 2011-09-20 | Intelliject, Inc. | Medicament delivery device configured to produce an audible output |
JP4892519B2 (en) * | 2008-05-20 | 2012-03-07 | シャープ株式会社 | Multilayer electrophotographic photosensitive member and image forming apparatus having the same |
US8181591B1 (en) | 2008-05-23 | 2012-05-22 | Trudell Medical International | Domed actuator for indicating device |
DK2293833T3 (en) | 2008-06-13 | 2016-05-23 | Mannkind Corp | DRY POWDER INHALER AND MEDICINAL ADMINISTRATION SYSTEM |
US8485180B2 (en) | 2008-06-13 | 2013-07-16 | Mannkind Corporation | Dry powder drug delivery system |
KR101628410B1 (en) | 2008-06-20 | 2016-06-08 | 맨카인드 코포레이션 | An interactive apparatus and method for real-time profiling of inhalation efforts |
DE102008030536A1 (en) * | 2008-06-27 | 2010-01-07 | Sendsor Gmbh | Spirometer with exchangeable flow tube |
TWI494123B (en) | 2008-08-11 | 2015-08-01 | Mannkind Corp | Use of ultrarapid acting insulin |
WO2010023591A2 (en) * | 2008-08-25 | 2010-03-04 | Koninklijke Philips Electronics N.V. | Respiratory drug delivery apparatus which provides audio instructions |
EP2179760B1 (en) | 2008-10-22 | 2013-02-27 | Trudell Medical International | Modular Aerosol Delivery System |
US8314106B2 (en) | 2008-12-29 | 2012-11-20 | Mannkind Corporation | Substituted diketopiperazine analogs for use as drug delivery agents |
DK2405963T3 (en) | 2009-03-11 | 2013-12-16 | Mannkind Corp | DEVICE, SYSTEM AND PROCEDURE FOR MEASURING RESISTANCE IN AN INHALATOR |
GB2469068B (en) * | 2009-03-31 | 2011-03-09 | Naseem Bari | Usage indicator |
NZ575943A (en) * | 2009-04-01 | 2009-07-31 | Nexus6 Ltd | Improvements in or Relating to Medicament Delivery Devices |
AU2010246984A1 (en) * | 2009-05-11 | 2012-01-19 | Koninklijke Philips Electronics N.V. | Aerosol drug delivery apparatus and method |
BRPI1013154B1 (en) | 2009-06-12 | 2020-04-07 | Mannkind Corp | MICROPARTICLES OF DICETOPIPERAZINE WITH SPECIFIC SURFACE AREAS DEFINED, DRY POWDER UNDERSTANDING THE REFERRED MICROPARTICLES, METHOD FOR FORMATION OF THE REFERENCESMICROPARTICLES AND THE FORMATION OF MICROPARTYSTEMS |
WO2011014562A1 (en) | 2009-07-28 | 2011-02-03 | North Carolina State University | Methods and devices for targeted injection of microspheres |
US20110031038A1 (en) * | 2009-08-07 | 2011-02-10 | Sagatulo, Inc. | Method and device for indicating doses in a drug delivery system |
US10130779B2 (en) | 2009-08-15 | 2018-11-20 | Koninklijke Philips N.V. | System and method of remotely monitoring and/or managing the treatment of a plurality of subjects with aerosolized medicament |
BR112012003055A2 (en) | 2009-08-15 | 2017-05-02 | Koninklijke Philips Electronics Nv | SYSTEM CONFIGURED TO ALLOW ONE OR MORE USERS TO MONITOR THE THERAPY OF A PLUS OF INDIVIDUALS AND METHOD IMPLEMENTED ON A COMPUTER TO ALLOW ONE OR MORE USERS TO MONITOR THE THERAPY OF A PLUS OF INDIVIDUALS REMOTELY |
US8539945B2 (en) | 2009-08-18 | 2013-09-24 | Teva Pharmaceutical Industries Ltd. | Dose counter and recording method |
US10869638B2 (en) * | 2009-09-25 | 2020-12-22 | Krispin Johan Leydon | Systems, devices and methods for rendering key respiratory measurements accessible to mobile digital devices |
US9138167B1 (en) * | 2009-09-25 | 2015-09-22 | Krispin Johan Leydon | Means for rendering key respiratory measurements accessible to mobile digital devices |
EP2496295A1 (en) | 2009-11-03 | 2012-09-12 | MannKind Corporation | An apparatus and method for simulating inhalation efforts |
CN101727651B (en) * | 2009-11-16 | 2012-04-18 | 东莞光阵显示器制品有限公司 | Method for realizing disposable medicinal products and control system |
US9119925B2 (en) | 2009-12-04 | 2015-09-01 | Covidien Lp | Quick initiation of respiratory support via a ventilator user interface |
US8335992B2 (en) | 2009-12-04 | 2012-12-18 | Nellcor Puritan Bennett Llc | Visual indication of settings changes on a ventilator graphical user interface |
US8924878B2 (en) | 2009-12-04 | 2014-12-30 | Covidien Lp | Display and access to settings on a ventilator graphical user interface |
WO2011073806A1 (en) | 2009-12-16 | 2011-06-23 | Koninklijke Philips Electronics N.V. | Color identification for drug delivery system |
US8499252B2 (en) | 2009-12-18 | 2013-07-30 | Covidien Lp | Display of respiratory data graphs on a ventilator graphical user interface |
US9262588B2 (en) | 2009-12-18 | 2016-02-16 | Covidien Lp | Display of respiratory data graphs on a ventilator graphical user interface |
BR112012016540B1 (en) * | 2010-01-07 | 2020-03-24 | Koninklijke Philips N.V. | RESPIRATORY MEDICINE ADMINISTRATION AND FEEDBACK DEVICE AND COMPLIANCE FOR USE WITH A MEDICINE STORAGE AND ADMINISTRATION DEVICE |
US9180261B2 (en) | 2010-01-12 | 2015-11-10 | Dance Biopharm Inc. | Preservative free insulin formulations and systems and methods for aerosolizing |
US9545488B2 (en) | 2010-01-12 | 2017-01-17 | Dance Biopharm Inc. | Preservative-free single dose inhaler systems |
US20130269684A1 (en) | 2012-04-16 | 2013-10-17 | Dance Pharmaceuticals, Inc. | Methods and systems for supplying aerosolization devices with liquid medicaments |
CN102905612A (en) | 2010-02-01 | 2013-01-30 | 普罗秋斯数字健康公司 | Two-wrist data gathering system |
EP2531099B1 (en) | 2010-02-01 | 2018-12-12 | Proteus Digital Health, Inc. | Data gathering system |
US20110225008A1 (en) * | 2010-03-09 | 2011-09-15 | Respira Dv, Llc | Self-Similar Medical Communications System |
US20110253139A1 (en) | 2010-04-15 | 2011-10-20 | Spectrum Health Innovations, LLC | Inhaler module and related system |
US8869793B1 (en) | 2010-05-18 | 2014-10-28 | Idtx Systems, Inc. | Compact self-contained automated MDI adapters or units for ventilators |
ES2758976T3 (en) * | 2010-06-18 | 2020-05-07 | Boehringer Ingelheim Int | Inhaler |
DE102010042007B4 (en) * | 2010-10-05 | 2013-04-04 | Aptar Radolfzell Gmbh | Discharge device for pharmaceutical media |
CN103370005A (en) * | 2010-12-20 | 2013-10-23 | 皇家飞利浦电子股份有限公司 | System and method of providing feedback to a subject receiving respiratory therapy via a client device associated with the subject |
US8915869B2 (en) | 2011-01-10 | 2014-12-23 | Bioguidance Llc | Patient monitoring device |
US8827930B2 (en) | 2011-01-10 | 2014-09-09 | Bioguidance Llc | System and method for patient monitoring |
US9084849B2 (en) | 2011-01-26 | 2015-07-21 | Kaleo, Inc. | Medicament delivery devices for administration of a medicament within a prefilled syringe |
US8627816B2 (en) | 2011-02-28 | 2014-01-14 | Intelliject, Inc. | Medicament delivery device for administration of opioid antagonists including formulations for naloxone |
US8939943B2 (en) | 2011-01-26 | 2015-01-27 | Kaleo, Inc. | Medicament delivery device for administration of opioid antagonists including formulations for naloxone |
SG194034A1 (en) | 2011-04-01 | 2013-11-29 | Mannkind Corp | Blister package for pharmaceutical cartridges |
DE102011007008B4 (en) * | 2011-04-07 | 2015-08-06 | Aptar Radolfzell Gmbh | media dispenser |
WO2012174472A1 (en) | 2011-06-17 | 2012-12-20 | Mannkind Corporation | High capacity diketopiperazine microparticles |
NZ595367A (en) | 2011-09-23 | 2012-02-24 | Nexus6 Ltd | A dose counting mechanism adapted to enclose a medicament delivery device |
AU2012328885B2 (en) | 2011-10-24 | 2017-08-31 | Mannkind Corporation | Methods and compositions for treating pain |
GB201202926D0 (en) * | 2012-02-21 | 2012-04-04 | Central Manchester University Hospitals Nhs Foundation Trust | Inhaler spacer |
WO2013132427A2 (en) | 2012-03-07 | 2013-09-12 | Koninklijke Philips N.V. | An apparatus for use with a nebulizer and a method of operating a nebulizer |
US20130269694A1 (en) * | 2012-04-16 | 2013-10-17 | Dance Pharmaceuticals, Inc. | Inhaler controlled by mobile device |
BR112014026201A2 (en) * | 2012-04-24 | 2017-06-27 | Koninklijke Philips Nv | portable pressure support system configured to provide a pressurized flow of breathable gas to an individual's airway; and method of providing an individual's airway breathable pressurized gas flow with a pressure support system including a housing |
US9522235B2 (en) | 2012-05-22 | 2016-12-20 | Kaleo, Inc. | Devices and methods for delivering medicaments from a multi-chamber container |
US9872965B2 (en) * | 2012-06-15 | 2018-01-23 | Breathe Technologies, Inc. | Method and system for operating a patient ventilation device |
CA3176610A1 (en) | 2012-06-25 | 2014-01-03 | Gecko Health Innovations, Inc. | Devices, systems, and methods for adherence monitoring and patient interaction |
DE102012211576B4 (en) * | 2012-07-04 | 2015-02-12 | Johnson Matthey Catalysts (Germany) Gmbh | Apparatus and method for the management and provision of the smallest amount of energy generated by a power generation unit |
US9427534B2 (en) * | 2012-07-05 | 2016-08-30 | Clement Clarke International Ltd. | Drug delivery inhaler devices |
US10362967B2 (en) | 2012-07-09 | 2019-07-30 | Covidien Lp | Systems and methods for missed breath detection and indication |
CN108057154B (en) | 2012-07-12 | 2021-04-16 | 曼金德公司 | Dry powder drug delivery system and method |
FR2993783B1 (en) * | 2012-07-26 | 2015-06-05 | Protecsom | INHALATION DEVICE FOR ADMINISTERING DRUG SUBSTANCE DURING INHALATION TREATMENT |
US10507294B2 (en) | 2012-08-13 | 2019-12-17 | Koninklijke Philips N.V. | Handheld dyspnea treatment device with drug and gas delivery |
GB2506385A (en) * | 2012-09-27 | 2014-04-02 | Realtime Technologies Ltd | Inhaler with wireless transmitter |
JP6465303B2 (en) | 2012-10-04 | 2019-02-06 | ベーリンガー インゲルハイム インターナショナル ゲゼルシャフト ミット ベシュレンクテル ハフツング | System, method and use for training an inhalation process |
GB2507104A (en) | 2012-10-19 | 2014-04-23 | Nicoventures Holdings Ltd | Electronic inhalation device |
WO2014066856A1 (en) | 2012-10-26 | 2014-05-01 | Mannkind Corporation | Inhalable influenza vaccine compositions and methods |
EP2938376A4 (en) | 2012-12-27 | 2017-01-25 | Kaleo, Inc. | Devices, systems and methods for locating and interacting with medicament delivery systems |
CA156938S (en) * | 2013-02-14 | 2014-07-08 | Clement Clarke Int Ltd | Spacer for an asthma inhaler |
EP3650067A1 (en) | 2013-03-11 | 2020-05-13 | John R. Collins | Inhalator device and method |
ES2928365T3 (en) | 2013-03-15 | 2022-11-17 | Mannkind Corp | Microcrystalline diketopiperazine compositions, methods of preparation and use thereof |
WO2014147550A1 (en) | 2013-03-21 | 2014-09-25 | Koninklijke Philips N.V. | System and method for monitoring usage of a respiratory medication delivery device |
GB201306709D0 (en) * | 2013-04-12 | 2013-05-29 | Clement Clarke Int Ltd | Training device |
US10229607B2 (en) | 2013-04-30 | 2019-03-12 | Elwha Llc | Systems and methods for competency training and use authorization for dispensing an agent |
US9390457B2 (en) | 2013-04-30 | 2016-07-12 | Elwha Llc | Devices and methods for competency training and use authorization for dispensing an agent |
US10220166B2 (en) | 2013-05-21 | 2019-03-05 | Reciprocal Labs Corporation | Usage monitoring attachment for medicament dispenser |
WO2014204511A2 (en) * | 2013-06-18 | 2014-12-24 | Isonea Limited | Compliance monitoring for asthma inhalers |
WO2016049066A1 (en) * | 2014-09-23 | 2016-03-31 | Oscillari Llc | Vibration sensor based drug delivery monitor |
EP3021834A1 (en) | 2013-07-18 | 2016-05-25 | MannKind Corporation | Heat-stable dry powder pharmaceutical compositions and methods |
DE102013214601B3 (en) * | 2013-07-25 | 2014-05-22 | Aptar Radolfzell Gmbh | Housing for container unit of inhalation device e.g. metered-dose inhaler, for oral administration of pharmaceutical medium, has membrane reversibly deformed based on pressure in pressure chamber and acting together with pushbutton |
CN105517607A (en) | 2013-08-05 | 2016-04-20 | 曼金德公司 | Insufflation apparatus and methods |
KR102569136B1 (en) | 2013-08-28 | 2023-08-22 | 게코 헬스 이노베이션즈, 인크. | Devices, systems, and methods for adherence monitoring and devices, systems, and methods for monitoring use of consumable dispensers |
DK3038685T3 (en) | 2013-08-30 | 2021-01-04 | Adherium Nz Ltd | MONITORING MONITOR FOR A MEDICINE INHALER |
TWI572377B (en) * | 2013-10-04 | 2017-03-01 | 財團法人國家實驗研究院 | Medication recording apparatus and method |
US10019555B2 (en) | 2013-10-19 | 2018-07-10 | Cohero Health, Inc. | Interactive respiratory device usage tracking system |
US11424017B2 (en) | 2013-10-19 | 2022-08-23 | Aptargroup, Inc. | Respiratory system and method that monitors medication flow |
WO2015109259A1 (en) * | 2014-01-16 | 2015-07-23 | Focusstart Respiratory Llc | Systems and methods for managing pulmonary medication delivery |
US10286163B1 (en) | 2014-03-04 | 2019-05-14 | Philip J. Paustian | On demand aerosolized delivery inhaler |
WO2015138454A1 (en) | 2014-03-10 | 2015-09-17 | Respeq Inc. | Systems and methods for delivering an agent to a user's lungs and for simultaneously monitoring lung health |
WO2015144442A1 (en) | 2014-03-25 | 2015-10-01 | Koninklijke Philips N.V. | Inhaler with two microphones for detection of inhalation flow |
US10307464B2 (en) | 2014-03-28 | 2019-06-04 | Mannkind Corporation | Use of ultrarapid acting insulin |
NZ722174A (en) | 2014-04-07 | 2021-07-30 | Boehringer Ingelheim Int | Inhalation training device and system for practicing of an inhalation process of a patient |
US10391270B2 (en) | 2014-04-07 | 2019-08-27 | Boehringer Ingelheim International Gmbh | Method, electronic device, inhalation training system and information storage medium for practicing and/or controlling an inhalation process of a patient |
US10173025B2 (en) | 2014-04-21 | 2019-01-08 | Idtx Systems, Inc. | Automated drug delivery systems |
US10610651B2 (en) | 2014-06-09 | 2020-04-07 | Aerami Therapeutics, Inc. | Self-puncturing liquid drug cartridges and associated dispenser |
US10857313B2 (en) * | 2014-07-01 | 2020-12-08 | Aerami Therapeutics, Inc. | Liquid nebulization systems and methods |
US10471222B2 (en) | 2014-07-01 | 2019-11-12 | Dance Biopharm Inc. | Aerosolization system with flow restrictor and feedback device |
US11273271B2 (en) | 2014-07-01 | 2022-03-15 | Aerami Therapeutics, Inc. | Aerosolization system with flow restrictor and feedback device |
US9517307B2 (en) | 2014-07-18 | 2016-12-13 | Kaleo, Inc. | Devices and methods for delivering opioid antagonists including formulations for naloxone |
US10987048B2 (en) * | 2014-08-13 | 2021-04-27 | Elwha Llc | Systems, methods, and devices to incentivize inhaler use |
WO2016033421A1 (en) * | 2014-08-28 | 2016-03-03 | Microdose Therapeutx, Inc. | Compliance monitoring module for an inhaler |
WO2016033419A1 (en) * | 2014-08-28 | 2016-03-03 | Microdose Therapeutx, Inc. | Compliance monitoring module for a breath-actuated inhaler |
WO2016041576A1 (en) * | 2014-09-16 | 2016-03-24 | Medituner Ab | Computer controlled dosage system |
US10561806B2 (en) | 2014-10-02 | 2020-02-18 | Mannkind Corporation | Mouthpiece cover for an inhaler |
US9950129B2 (en) | 2014-10-27 | 2018-04-24 | Covidien Lp | Ventilation triggering using change-point detection |
US10569028B2 (en) * | 2014-11-05 | 2020-02-25 | Insuline Medical Ltd. | Drug tracking device |
US10561814B2 (en) | 2014-11-19 | 2020-02-18 | Idtx Systems, Inc. | Automated drug dispensing systems with automated HME bypass for ventilator circuits |
CA2968361A1 (en) * | 2014-11-20 | 2016-05-26 | Cognita Labs, LLC | Method and apparatus to measure, aid and correct the use of inhalers |
US10058661B2 (en) * | 2014-12-04 | 2018-08-28 | Norton (Waterford) Limited | Inhalation monitoring system and method |
EP3037120A1 (en) * | 2014-12-23 | 2016-06-29 | PARI Pharma GmbH | Aerosol delivery device and operating method for the aerosol delivery device |
EP3242702B1 (en) | 2015-01-09 | 2020-10-07 | Adherium (NZ) Limited | Monitor for a medicament inhaler |
USD774178S1 (en) * | 2015-03-10 | 2016-12-13 | Reciprocal Labs Corporation | Usage monitoring attachment for a dry powder inhaler |
USD757926S1 (en) * | 2015-03-10 | 2016-05-31 | Reciprocal Labs Corporation | Usage monitoring attachment for a soft mist inhaler |
AU2016235054B2 (en) | 2015-03-24 | 2020-07-16 | Kaleo, Inc. | Devices and methods for delivering a lyophilized medicament |
CN107735135B (en) | 2015-04-02 | 2020-06-26 | 希尔-罗姆服务私人有限公司 | Manifold for a respiratory device |
USD837969S1 (en) * | 2015-06-04 | 2019-01-08 | Adherium (Nz) Limited | Compliance monitor for a medicament inhaler |
US10088464B2 (en) * | 2015-06-16 | 2018-10-02 | Lunatech, Llc | Systems and methods for analyzing pharmaceuticals |
US20160370337A1 (en) * | 2015-06-16 | 2016-12-22 | Lunatech, Llc | Analysis System For Biological Compounds, And Method Of Operation |
GB2556479B (en) | 2015-06-30 | 2022-09-07 | Kaleo Inc | Auto-injectors for administration of a medicament within a prefilled syringe |
KR102641177B1 (en) | 2015-07-20 | 2024-02-26 | 펄 테라퓨틱스 인코포레이티드 | Aerosol delivery systems and related methods |
GB201517089D0 (en) | 2015-09-28 | 2015-11-11 | Nicoventures Holdings Ltd | Vaping heat map system and method for electronic vapour provision systems |
US10255412B2 (en) | 2015-11-13 | 2019-04-09 | Reciprocal Labs Corporation | Real time adaptive controller medication dosing |
WO2017112452A1 (en) * | 2015-12-21 | 2017-06-29 | 3M Innovative Properties Company | Flow governor assemblies for use in medicinal inhalers |
AU201613321S (en) * | 2015-12-23 | 2016-07-12 | Adherium Nz Ltd | A Compliance Monitor for a Medicament Inhaler |
AU2017208170B2 (en) * | 2016-01-11 | 2022-01-20 | Syqe Medical Ltd. | Method and system for controlling the delivery of active agents |
CA3011901A1 (en) | 2016-01-21 | 2017-07-27 | T2 Biosystems, Inc. | Nmr methods and systems for the rapid detection of bacteria |
US11042916B1 (en) | 2016-02-29 | 2021-06-22 | Canary Medical Inc. | Computer-based marketplace for information |
CA3019203A1 (en) * | 2016-03-24 | 2017-09-28 | Trudell Medical International | Respiratory care system with electronic indicator |
USD808515S1 (en) | 2016-04-05 | 2018-01-23 | 3M Innovative Properties Company | Inhaler |
US11610510B2 (en) | 2016-04-12 | 2023-03-21 | Noble International, Inc. | Metered dose inhaler training device |
WO2017178865A1 (en) | 2016-04-12 | 2017-10-19 | Biocorp Production S.A | Metered dose inhaler add-on device, observance improvement system and method for improving observance of use in metered dose inhalers |
KR102122887B1 (en) | 2016-05-03 | 2020-06-16 | 뉴마 레스퍼러토리 인코포레이티드 | Droplet delivery device and method of use for delivery of fluids to the waste relationship |
CN109475711B (en) * | 2016-05-19 | 2022-04-15 | 曼金德公司 | Device, system and method for detecting and monitoring inhalation |
US10850050B2 (en) | 2016-05-19 | 2020-12-01 | Trudell Medical International | Smart valved holding chamber |
US20170361036A1 (en) * | 2016-06-15 | 2017-12-21 | Virgilant Technologies Limited | Electronic inhaling device |
WO2017221242A1 (en) * | 2016-06-20 | 2017-12-28 | Timestamp Ltd. | Usage recording device |
USD882064S1 (en) * | 2016-06-23 | 2020-04-21 | Adherium (Nz) Limited | Compliance monitor for a medicament inhaler |
WO2018007997A1 (en) | 2016-07-08 | 2018-01-11 | Trudell Medical International | Smart oscillating positive expiratory pressure device |
US10786638B2 (en) | 2016-07-08 | 2020-09-29 | Trudell Medical International | Nebulizer apparatus and method |
DE102016219759A1 (en) | 2016-07-22 | 2018-01-25 | Centre for Research and Technology Hellas - InformationTechnologies Institute (CERTH/ITI) | Sensor unit for an inhaler, inhaler and monitoring device |
CN106039495A (en) * | 2016-07-26 | 2016-10-26 | 宁波睿诺电子科技有限公司 | Intelligent inhaler |
TWI664024B (en) * | 2016-07-27 | 2019-07-01 | 和淞科技股份有限公司 | Atomizing device |
US20180056018A1 (en) * | 2016-08-31 | 2018-03-01 | Cephalon, Inc. | Inhalation Systems, Devices and Methods |
CA3043965A1 (en) * | 2016-11-18 | 2018-05-24 | Norton (Waterford) Limited | Drug delivery device with electronics |
ES2920151T3 (en) * | 2016-12-09 | 2022-08-01 | Trudell Medical Int | smart nebulizer |
JP6724254B2 (en) | 2016-12-16 | 2020-07-15 | コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. | Training device for inhalers and inhalers |
WO2018109224A1 (en) * | 2016-12-16 | 2018-06-21 | Koninklijke Philips N.V. | Training device for an inhaler, and an inhaler |
JP7014797B2 (en) | 2016-12-23 | 2022-02-01 | カレオ,インコーポレイテッド | Drug delivery devices and methods for delivering drugs to babies and children |
US10799653B2 (en) | 2017-01-09 | 2020-10-13 | United Therapeutics Corporation | Aerosol delivery device and method for manufacturing and operating the same |
AU2018210313A1 (en) | 2017-01-17 | 2019-06-20 | Kaleo, Inc. | Medicament delivery devices with wireless connectivity and event detection |
US11529476B2 (en) | 2017-05-19 | 2022-12-20 | Pneuma Respiratory, Inc. | Dry powder delivery device and methods of use |
GB2564407A (en) * | 2017-07-06 | 2019-01-16 | Corefox Oy | Portable inhalator device |
AU2018300447A1 (en) * | 2017-07-11 | 2020-01-30 | Cipla Limited | Adherence-tracking and monitoring device for metered-dose inhaler |
US11833333B2 (en) | 2017-07-12 | 2023-12-05 | Insuline Medical Ltd | Drug tracking device |
EP3658211B1 (en) | 2017-07-25 | 2022-09-28 | Adherium (NZ) Limited | Adherence monitoring method and device |
JP2020536614A (en) | 2017-10-04 | 2020-12-17 | ニューマ・リスパイラトリー・インコーポレイテッド | In-line droplet delivery device and usage that is electrically operated by breathing |
WO2019079461A1 (en) | 2017-10-17 | 2019-04-25 | Pneuma Respiratory, Inc. | Nasal drug delivery apparatus and methods of use |
CN111479604B (en) | 2017-11-08 | 2022-12-30 | 精呼吸股份有限公司 | Electrically breath actuated in-line droplet delivery device with small volume ampoule and method of use |
ES2875352T3 (en) * | 2017-11-20 | 2021-11-10 | Presspart Gmbh & Co Kg | Inhalation system |
MX2020007026A (en) | 2018-01-04 | 2020-12-03 | Trudell Medical Int | Smart oscillating positive expiratory pressure device. |
US20190217027A1 (en) * | 2018-01-17 | 2019-07-18 | Indose Inc | Device for vaporized substance dosage metering based on an input dosage |
CN108187202A (en) * | 2018-02-09 | 2018-06-22 | 上海华瑞气雾剂有限公司 | A kind of intelligent driver |
US11804303B2 (en) | 2018-03-01 | 2023-10-31 | Reciprocal Labs Corporation | Evaluation of respiratory disease risk in a geographic region based on medicament device monitoring |
US11040243B2 (en) | 2018-03-23 | 2021-06-22 | Breathe With B, Inc. | Breathing device |
US20190298941A1 (en) * | 2018-04-03 | 2019-10-03 | John R. Collins | Adjunct Diagnostic Device and Method |
JP7427660B2 (en) | 2018-06-04 | 2024-02-05 | トゥルーデル メディカル インターナショナル | Holding chamber with smart valve |
WO2020018433A1 (en) | 2018-07-16 | 2020-01-23 | Kaleo, Inc. | Medicament delivery devices with wireless connectivity and compliance detection |
PL238372B1 (en) | 2018-09-27 | 2021-08-16 | Findair Spolka Z Ograniczona Odpowiedzialnoscia | Method and device for medicine use monitoring |
US11064727B2 (en) | 2019-02-06 | 2021-07-20 | Altria Client Services Llc | Sensor apparatuses and systems |
US11406786B2 (en) | 2019-04-22 | 2022-08-09 | Sunovion Pharmaceuticals Inc. | Nebulizer monitoring device, system and method |
CN109966600A (en) * | 2019-04-30 | 2019-07-05 | 邵明芝 | A kind of portable multifunctional Ultrasonography atomizer |
US11419995B2 (en) | 2019-04-30 | 2022-08-23 | Norton (Waterford) Limited | Inhaler system |
US11554226B2 (en) | 2019-05-17 | 2023-01-17 | Norton (Waterford) Limited | Drug delivery device with electronics |
JP2022543523A (en) | 2019-08-09 | 2022-10-13 | カレオ,インコーポレイテッド | Device and method for delivery of substances in pre-filled syringes |
EP4021542A4 (en) | 2019-08-27 | 2023-09-06 | Trudell Medical International | Smart oscillating positive expiratory pressure device |
AU2020356529A1 (en) | 2019-09-25 | 2022-05-19 | Janssen Pharmaceuticals, Inc. | Interconnection of drug administration systems |
US11727826B2 (en) | 2020-03-02 | 2023-08-15 | Ryan Ziegler | Resuscitation training device and method of use |
GB2594048B (en) * | 2020-04-04 | 2022-12-14 | Purcell Global Ltd | Inhaler systems |
WO2021211916A1 (en) | 2020-04-17 | 2021-10-21 | United Therapeutics Corporation | Treprostinil for use in the treatment of intersitial lung disease |
DE102020110867A1 (en) * | 2020-04-22 | 2021-10-28 | Aesculap Ag | Intelligent oil spray adapter |
US11672934B2 (en) | 2020-05-12 | 2023-06-13 | Covidien Lp | Remote ventilator adjustment |
WO2022271848A1 (en) | 2021-06-22 | 2022-12-29 | Pneuma Respiratory, Inc. | Droplet delivery device with push ejection |
WO2023278551A1 (en) * | 2021-06-30 | 2023-01-05 | Pneuma Respiratory, Inc. | Droplet delivery device with optimized mixing of suspensions |
TWI817860B (en) * | 2022-12-06 | 2023-10-01 | 財團法人國家實驗研究院 | Integrated device for inhalation medication and peak flow measurement and method of using the same |
Family Cites Families (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3991304A (en) * | 1975-05-19 | 1976-11-09 | Hillsman Dean | Respiratory biofeedback and performance evaluation system |
EP0013534A1 (en) * | 1979-01-11 | 1980-07-23 | Technobiotic Ltd. | Inhalation device |
US4942544A (en) * | 1985-02-19 | 1990-07-17 | Kenneth B. McIntosh | Medication clock |
FR2593951B1 (en) * | 1986-02-03 | 1989-01-06 | Bertin & Cie | METHOD AND SYSTEM FOR REMOTE CONTROL OF AT LEAST ONE INFUSION STATION |
US4984158A (en) * | 1988-10-14 | 1991-01-08 | Hillsman Dean | Metered dose inhaler biofeedback training and evaluation system |
SE466684B (en) * | 1989-03-07 | 1992-03-23 | Draco Ab | DEVICE INHALATOR AND PROCEDURE TO REGISTER WITH THE DEVICE INHALATOR MEDICATION |
GB2233795A (en) * | 1989-07-14 | 1991-01-16 | Lasermax Corp | Medication reminder |
US5152456A (en) * | 1989-12-12 | 1992-10-06 | Bespak, Plc | Dispensing apparatus having a perforate outlet member and a vibrating device |
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1991
- 1991-12-20 US US07/811,398 patent/US5363842A/en not_active Expired - Lifetime
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1992
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- 1992-12-18 WO PCT/US1992/010804 patent/WO1993012823A2/en active IP Right Grant
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WO1993012823A2 (en) | 1993-07-08 |
WO1993012823A3 (en) | 1993-08-19 |
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