US20190209463A1 - Intranasal delivery of dihydroergotamine by precision olfactory device - Google Patents

Intranasal delivery of dihydroergotamine by precision olfactory device Download PDF

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US20190209463A1
US20190209463A1 US16/240,639 US201916240639A US2019209463A1 US 20190209463 A1 US20190209463 A1 US 20190209463A1 US 201916240639 A US201916240639 A US 201916240639A US 2019209463 A1 US2019209463 A1 US 2019209463A1
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Prior art keywords
canceled
dhe
dose
propellant
canister
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Abandoned
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US16/240,639
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English (en)
Inventor
John D. Hoekman
Kelsey H. Satterly
Stephen B. Shrewsbury
Scott Youmans
Christopher Fuller
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Impel Pharmaceuticals Inc
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Impel Neuropharma Inc
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Priority to US16/240,639 priority Critical patent/US20190209463A1/en
Assigned to IMPEL NEUROPHARMA, INC. reassignment IMPEL NEUROPHARMA, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: SHREWSBURY, STEPHEN B., HOEKMAN, JOHN D., SATTERLY, KELSEY H., FULLER, CHRISTOPHER, YOUMANS, SCOTT
Publication of US20190209463A1 publication Critical patent/US20190209463A1/en
Priority to US17/062,364 priority patent/US11185497B2/en
Assigned to AVENUE VENTURE OPPORTUNITIES FUND, L.P. reassignment AVENUE VENTURE OPPORTUNITIES FUND, L.P. SECURITY INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: IMPEL NEUROPHARMA, INC.
Assigned to IMPEL NEUROPHARMA, INC. reassignment IMPEL NEUROPHARMA, INC. RELEASE BY SECURED PARTY (SEE DOCUMENT FOR DETAILS). Assignors: AVENUE VENTURE OPPORTUNITIES FUND, L.P.
Priority to US17/492,136 priority patent/US20220105030A1/en
Abandoned legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/0012—Galenical forms characterised by the site of application
    • A61K9/0043—Nose
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K31/00—Medicinal preparations containing organic active ingredients
    • A61K31/33—Heterocyclic compounds
    • A61K31/395—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins
    • A61K31/435—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins having six-membered rings with one nitrogen as the only ring hetero atom
    • A61K31/47—Quinolines; Isoquinolines
    • A61K31/48—Ergoline derivatives, e.g. lysergic acid, ergotamine
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    • A61K31/00—Medicinal preparations containing organic active ingredients
    • A61K31/33—Heterocyclic compounds
    • A61K31/395—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins
    • A61K31/495—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins having six-membered rings with two or more nitrogen atoms as the only ring heteroatoms, e.g. piperazine or tetrazines
    • A61K31/505—Pyrimidines; Hydrogenated pyrimidines, e.g. trimethoprim
    • A61K31/519—Pyrimidines; Hydrogenated pyrimidines, e.g. trimethoprim ortho- or peri-condensed with heterocyclic rings
    • A61K31/52—Purines, e.g. adenine
    • A61K31/522—Purines, e.g. adenine having oxo groups directly attached to the heterocyclic ring, e.g. hypoxanthine, guanine, acyclovir
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    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
    • A61K47/06—Organic compounds, e.g. natural or synthetic hydrocarbons, polyolefins, mineral oil, petrolatum or ozokerite
    • A61K47/26—Carbohydrates, e.g. sugar alcohols, amino sugars, nucleic acids, mono-, di- or oligo-saccharides; Derivatives thereof, e.g. polysorbates, sorbitan fatty acid esters or glycyrrhizin
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
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    • A61K9/08—Solutions
    • 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
    • A61M11/00—Sprayers or atomisers specially adapted for therapeutic purposes
    • A61M11/001—Particle size control
    • A61M11/002—Particle size control by flow deviation causing inertial separation of transported particles
    • A—HUMAN NECESSITIES
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    • 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
    • A61M11/00—Sprayers or atomisers specially adapted for therapeutic purposes
    • A61M11/02—Sprayers or atomisers specially adapted for therapeutic purposes operated by air or other gas pressure applied to the liquid or other product to be sprayed or atomised
    • A—HUMAN NECESSITIES
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    • 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
    • A61M11/00—Sprayers or atomisers specially adapted for therapeutic purposes
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    • A61M15/0001—Details of inhalators; Constructional features thereof
    • A61M15/002—Details of inhalators; Constructional features thereof with air flow regulating means
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    • 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
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    • A61M15/00—Inhalators
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    • A61M15/08—Inhaling devices inserted into the nose
    • A—HUMAN NECESSITIES
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    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/82—Internal energy supply devices
    • A61M2205/8218—Gas operated
    • A61M2205/8225—Gas operated using incorporated gas cartridges for the driving gas

Definitions

  • DHE Dihydroergotamine
  • DHE oral bioavailability of DHE is poor, and DHE is commonly administered parenterally as the mesylate salt by subcutaneous, intramuscular or intravenous injection, and where approved, by nasal spray. Because migraine headaches are episodic and occur unpredictably, administration by nasal spray is far more convenient for treatment of acute migraine than is administration by injection. However, the previously approved nasal spray drug-device combination product provides only 32% of the bioavailability of the intravenous injection, and variable efficacy (among other factors) has led to its withdrawal from market in the EU and other countries, although it remains available in the United States.
  • INP104 provided 4-fold higher mean maximal plasma concentration, nearly 3-fold higher mean systemic drug exposure, and reached maximal DHE plasma concentration faster than Migranal®.
  • the higher maximal plasma concentration and systemic drug exposure were achieved with a lower administered dose of the identical formulation of DHE mesylate, 1.45 mg for INP104 versus 2.0 mg for Migranal®, and without requiring a 15-minute wait between administration of divided sub-doses, as required for Migranal®.
  • systemic delivery of DHE was more consistent with INP104 than with Migranal®, with lower coefficient of variation (CV %) in DHE AUC 0-inf and C max observed across subjects.
  • methods for acutely treating migraine headache with or without aura.
  • the methods comprise administering to a subject with migraine headache an effective dose of a liquid pharmaceutical composition comprising dihydroergotamine (DHE) or a salt thereof, wherein the dose is administered by an intranasal delivery device that provides, following intranasal administration, (a) a mean peak plasma DHE concentration (C max ) of at least 750 pg/ml, (b) with a mean time to C max (T max ) of DHE of less than 45 minutes, and (c) a mean plasma AUC 0-inf of DHE of at least 2500 pg*hr/ml.
  • DHE dihydroergotamine
  • the dose is no more than 2.0 mg DHE or salt thereof, less than 2.0 mg DHE or salt thereof, 1.2-1.8 mg DHE or salt thereof, or 1.4-1.6 mg DHE or salt thereof. In a particular embodiment, the dose is about 1.45 mg DHE or salt thereof.
  • the dose is administered as a plurality of divided doses. In certain embodiments, the dose is administered as two divided doses. In a particular embodiment, one divided dose is administered to each nostril. In typical divided dose embodiments, the dose is administered over no more than 1 minute, over no more than 45 seconds, or over no more than 30 seconds. In various embodiments, the volume of liquid composition administered per divided dose is 140-250 ⁇ L, 175 ⁇ L-225 ⁇ L, about 200 ⁇ L, or about 180 ⁇ L.
  • the liquid composition comprises a salt of DHE.
  • the liquid composition comprises DHE mesylate.
  • the liquid composition comprises DHE mesylate at a concentration of 2.5-7.5 mg/ml, 3.5-6.5 mg/ml, or more particularly, 4.0 mg/ml DHE mesylate.
  • the mean C max of DHE is at least 1000 pg/ml, or at least 1200 pg/ml. In various embodiments, following administration of the dose, the mean plasma AUC 0-inf of DHE is at least 3000 pg*hr/ml, 4000 pg*hr/ml, 5000 pg*hr/ml, or 6000 pg*hr/ml.
  • the mean peak plasma concentration (C max ) of 8′-OH-DHE is at least 50 pg/ml or at least 55 pg/ml. In some embodiments, following administration of the dose, the mean plasma AUC 0-inf of 8′-OH-DHE is at least 1000 pg*hr/ml.
  • the intranasal delivery device is a manually actuated, propellant-driven, metered-dose intranasal administration device.
  • the liquid pharmaceutical composition and propellant prior to first manual actuation, are not in contact within the device.
  • the liquid pharmaceutical composition is contained in a vial and the propellant is contained in a canister.
  • the canister may further be a pressurized canister.
  • the liquid pharmaceutical composition in the vial and propellant in the canister are not in contact within the device.
  • each manual actuation brings a metered volume of liquid pharmaceutical composition and a separately metered volume of propellant into contact within a dose chamber of the device.
  • contact of propellant with liquid pharmaceutical composition within the dose chamber of the device creates a spray of liquid pharmaceutical composition as the formulation is expelled through a nozzle of the device.
  • the nozzle has a plurality of lumens, and the spray is ejected simultaneously through a plurality of nozzle lumens.
  • the propellant is a hydrofluoroalkane propellant, and in specific embodiments, the propellant is hydrofluoroalkane-134a.
  • the vial prior to first actuation, is nonintegral to the device and is configured to be attachable thereto. In some of these embodiments, the vial is configured to be threadably attachable to the device.
  • the subject has migraine headache with aura. In some embodiments, the subject has migraine headache without aura. In some embodiments, the subject has had onset of at least one prodromal symptom of migraine. In a variety of embodiments, the subject has menstrual-associated migraine. In certain embodiments, the subject has triptan-resistant migraine.
  • the subject self-administers the liquid pharmaceutical composition.
  • a second, related, aspect improved methods of acutely treating migraine headache with or without aura by intranasal administration of dihydroergotamine (DHE) or salt thereof are provided.
  • the improvement comprises administering a dose of a liquid pharmaceutical composition comprising dihydroergotamine (DHE) or salt thereof by an intranasal delivery device that provides, following intranasal administration, (a) a mean peak plasma DHE concentration (C max ) of at least 750 pg/ml, (b) with a mean time to C max (T max ) of DHE of less than 45 minutes, and (c) a mean plasma AUC 0-inf of DHE of at least 2500 pg*hr/ml.
  • C max mean peak plasma DHE concentration
  • T max mean time to C max
  • T max mean plasma AUC 0-inf of DHE of at least 2500 pg*hr/ml.
  • the intranasal delivery device is a manually actuated, metered-dose, propellant-driven intranasal administration device as used in methods of the first aspect.
  • contact of propellant with liquid pharmaceutical composition within a dose chamber of the device ejects a spray of liquid pharmaceutical composition through a nozzle of the device.
  • the nozzle has a plurality of lumens, and the spray is ejected simultaneously through a plurality of nozzle lumens.
  • kits for acutely treating migraine with or without aura.
  • the kits comprise a vial, within which is sealably contained at least one effective dose of a liquid pharmaceutical composition comprising dihydroergotamine (DHE) or salt thereof, and a device, wherein the vial is configured to be attachable to the device, and wherein the device, upon attachment of the vial, is a manually actuated, metered-dose, propellant-driven intranasal administration device capable of providing, after intranasal administration of a dose of liquid pharmaceutical composition, (a) a mean peak plasma DHE concentration (C max ) of at least 750 pg/ml, (b) with a mean time to C max (T max ) of DHE of less than 45 minutes, and (c) a mean plasma AUC 0-inf of DHE of at least 2500 pg*hr/ml.
  • DHE dihydroergotamine
  • the device within the kit comprises a canister, wherein the canister is a pressurized canister containing propellant.
  • the liquid pharmaceutical composition and propellant are not in contact within the device.
  • the liquid pharmaceutical composition in the vial and propellant in the canister are not in contact within the device.
  • each manual actuation brings a metered volume of liquid pharmaceutical composition and a separately metered volume of propellant into contact within a dose chamber of the device, and contact of propellant with liquid pharmaceutical composition within the dose chamber of the device creates a spray of liquid pharmaceutical composition as the formulation is expelled through a nozzle of the device.
  • the liquid pharmaceutical composition within the vial comprises a salt of DHE.
  • the liquid composition comprises DHE mesylate.
  • the liquid composition comprises DHE mesylate at a concentration of 2.5-7.5 mg/ml, or about 4.0 mg/ml DHE mesylate.
  • the liquid composition comprises 4.0 mg/ml DHE mesylate, 10.0 mg/ml caffeine, and 50 mg/ml dextrose.
  • the vial contains no more than 2 ml of liquid pharmaceutical composition. In some embodiments, the vial contains approximately 1 ml of liquid pharmaceutical composition.
  • the pressurized canister contains an amount of propellant sufficient to administer no more than 1 dose of liquid pharmaceutical composition.
  • FIG. 1 shows a cross section of an embodiment of a handheld, manually actuated, metered-dose, propellant-driven intranasal administration device useful for precision olfactory delivery of dihydroergotamine (DHE).
  • DHE dihydroergotamine
  • FIG. 2 shows a cross section of the in-line nasal delivery device of FIG. 1 in the stages of rest and actuation.
  • FIG. 2A shows the in-line nasal delivery device at rest with FIG. 2B showing the actuation of the pump and FIG. 2C showing actuation of the propellant valve.
  • FIG. 3 shows a cross section of another implementation of the in-line nasal delivery device.
  • FIG. 4 shows a cross section of the diffuser as seated within the device.
  • FIG. 5A shows an exploded view of the dose chamber and the Y-junction unassembled.
  • FIG. 5B shows an exploded view of the dose chamber and Y-junction in cooperation.
  • FIG. 6 shows arrows representing both dose and propellant flow.
  • FIG. 7 shows the actuator grip and conical spring arrangement.
  • FIG. 8 shows a cross section of the optional nose cone and a side elevation of the optional nose cone.
  • FIGS. 9A and 9B illustrate the device used in the phase I clinical trial described in Example 2, with further description of the numbered parts set forth in Table 1.
  • FIGS. 10A and 10B plot plasma concentrations of DHE versus time as measured in the phase I comparative bioavailability clinical trial described in Example 2, with FIG. 10A plotting data from 0 to 8 hours and FIG. 10B plotting data from 0 to 24 hours.
  • FIGS. 11A and 11B plot plasma concentrations of the 8′-OH-DHE metabolite of DHE versus time as measured in the phase I comparative bioavailability clinical trial described in Example 2, with FIG. 11A plotting data from 0 to 8 hours and FIG. 11B plotting data from 0 to 24 hours.
  • FIG. 12A shows a cross section of an alternate implementation of the in-line nasal delivery device.
  • FIG. 12B shows a zoomed-in view of the cross section of FIG. 12A .
  • FIG. 13A shows a cross section of the diffuser as seated within the device, according to an additional embodiment.
  • FIG. 13B shows an exploded view of the nozzle and the Y-junction, according to an additional embodiment.
  • FIG. 14 illustrates the nose cone, according to an additional embodiment.
  • Ranges throughout this disclosure, various aspects of the invention are presented in a range format. Ranges include the recited endpoints. It should be understood that the description in range format is merely for convenience and brevity and should not be construed as an inflexible limitation on the scope of the invention. Accordingly, the description of a range should be considered to have specifically disclosed all the possible subranges as well as individual numerical values within that range. For example, description of a range such as from 1 to 6 should be considered to have specifically disclosed subranges such as from 1 to 3, from 1 to 4, from 1 to 5, from 2 to 4, from 2 to 6, from 3 to 6 etc., as well as individual numbers within that range, for example, 1, 2, 2.7, 3, 4, 5, 5.3, and 6. This applies regardless of the breadth of the range.
  • the terms “a”, “an”, and “the” are understood to be singular or plural. That is, the articles “a” and “an” are used herein to refer to one or to more than one (i.e., to at least one) of the grammatical object of the article.
  • an element means one element or more than one element.
  • the term “about” is understood as within a range of normal tolerance in the art, for example within 2 standard deviations of the mean and is meant to encompass variations of ⁇ 20% or ⁇ 10%, more preferably ⁇ 5%, even more preferably ⁇ 1%, and still more preferably ⁇ 0.1% from the stated value.
  • INP104 provided nearly 3-fold higher mean systemic drug exposure, nearly 4-fold higher mean maximal plasma concentration, and reached maximal DHE plasma concentration faster than Migranal®.
  • the higher systemic drug exposure and higher maximal plasma concentration were achieved with a lower administered dose of the identical formulation of DHE mesylate, 1.45 mg for INP104 versus 2.0 mg for Migranal®, and without requiring a 15-minute wait between administration of divided sub-doses, as required for Migranal®.
  • bolus intravenous administration of 1 mg DHE mesylate provided less than 2-fold greater systemic drug delivery, measured as AUC 0-inf , as compared to INP104 intranasal delivery.
  • the 8′OH-DHE metabolite of DHE is known to be active, and to contribute to the long-lasting effect of DHE on migraine.
  • INP104 intranasal administration of 1.45 mg DHE mesylate by INP104 provides equivalent systemic exposure to the active metabolite of DHE as bolus intravenous administration of 1.0 mg DHE mesylate.
  • the 8′-OH DHE metabolite could be detected in only a minority of subjects administered Migranal®.
  • methods are provided for acutely treating migraine headache with or without aura.
  • the methods comprise administering to a subject with migraine headache an effective dose of a liquid pharmaceutical composition comprising dihydroergotamine (DHE) or a salt thereof, wherein the dose is administered by an intranasal delivery device that provides, following intranasal administration, (a) a mean peak plasma DHE concentration (C max ) of at least 750 pg/ml, (b) with a mean time to C max (T max ) of DHE of less than 45 minutes, and (c) a mean plasma AUC 0-inf of DHE of at least 2500 pg*hr/ml.
  • DHE dihydroergotamine
  • the dose is no more than 2.0 mg DHE or salt thereof. In typical embodiments, the dose is less than 2.0 mg DHE or DHE salt.
  • the dose is 1.2-1.8 mg DHE or salt thereof, 1.4-1.6 mg DHE or salt thereof, or 1.4-1.5 mg DHE or salt thereof. In some embodiments, the dose is about 1.2, 1.25, 1.3, 1.35, 1.4, 1.45, 1.5, 1.55, 1.6, 1.65, or 1.7 mg DHE or salt thereof. In a currently preferred embodiment, the dose is about 1.45 mg DHE or salt thereof.
  • the dose is administered as a single undivided dose. In these embodiments, the dose is administered to either the left or right nostril.
  • the dose is administered as a plurality of divided doses. In some of these embodiments, the dose is administered as 2, 3, or 4 divided doses. In particular embodiments, the dose is administered as 2 divided doses. In currently preferred embodiments, the dose is administered as 2 divided doses, with one divided dose administered to each nostril.
  • the entire effective dose is typically administered over no more than 1 minute—that is, all of the plurality of divided doses are administered within 1 minute of administration of the first divided dose.
  • the dose is administered over no more than 45 seconds. In certain divided dose embodiments, the dose is administered over no more than 30 seconds.
  • the volume of liquid composition administered per divided dose is typically 140-250 ⁇ L. In certain embodiments, the volume of liquid composition administered per divided dose is 145 ⁇ L-225 ⁇ L. In some embodiments, the volume of liquid composition administered per divided dose is 175 ⁇ L-225 ⁇ L. In particular embodiments, the volume of liquid composition administered per divided dose is about ⁇ 180 ⁇ L or ⁇ 200 ⁇ L.
  • the liquid pharmaceutical composition comprises dihydroergotamine (DHE) or salt thereof.
  • DHE dihydroergotamine
  • the liquid pharmaceutical composition comprises a salt of DHE.
  • the liquid composition comprises DHE mesylate.
  • Dihydroergotamine mesylate ergotamine hydrogenated in the 9,10 position as the mesylate salt—is known chemically as ergotaman-3′,6′,18-trione, 9,10-dihydro-12′-hydroxy-2′-methyl-5′-(phenylmethyl)-, (5′ ⁇ )-, monomethane-sulfonate. Its molecular weight is 679.80 and its empirical formula is C 33 H 37 N 5 O 5 .CH 4 O 3 S. The structure is shown in formula (I) below:
  • the liquid pharmaceutical composition comprises DHE mesylate at a concentration of at least 1 mg/ml, 1.5 mg/ml, 2.0 mg/ml, 2.5 mg/ml, 3.0 mg/ml, 3.5 mg/ml, 4.0 mg/ml, 4.5 mg/ml or 5.0 mg/ml.
  • the liquid pharmaceutical composition comprises DHE mesylate at a concentration of 2.5-7.5 mg/ml.
  • the liquid pharmaceutical composition comprises 3.0-5.0 mg/ml or 3.5-6.5 mg/ml DHE mesylate.
  • the liquid pharmaceutical composition comprises 4.0 mg/ml DHE mesylate.
  • the composition further comprises caffeine.
  • the composition comprises caffeine at a concentration of 1 mg/ml-20 mg/ml, 5 mg/ml-15 mg/ml, or 7.5 mg/ml-12.5 mg/ml.
  • the composition comprises 10.0 mg/ml caffeine.
  • the composition further comprises dextrose.
  • the composition comprises dextrose at a concentration of 5 mg/ml, 10 mg/ml, 15 mg/ml, 20 mg/ml, 25 mg/ml, 30 mg/ml, 35 mg/ml, 40 mg/ml, 45 mg/ml, or 50 mg/ml.
  • the composition comprises dextrose at a concentration of at least 50 mg/ml.
  • the liquid pharmaceutical composition comprises 4.0 mg/ml DHE mesylate, 10.0 mg/ml caffeine, and 50 mg/ml dextrose.
  • the methods comprise administering to a subject with migraine headache an effective dose of a liquid pharmaceutical composition comprising dihydroergotamine (DHE) or a salt thereof, wherein the dose is administered by an intranasal delivery device that provides, following intranasal administration, (a) a mean peak plasma DHE concentration (C max ) of at least 750 pg/ml, (b) with a mean time to C max (T max ) of DHE of less than 45 minutes, and (c) a mean plasma AUC 0-inf of DHE of at least 2500 pg*hr/ml.
  • DHE dihydroergotamine
  • the mean peak plasma DHE concentration (C max ) achieved following administration of a dose, whether administered as an undivided dose or a plurality of divided doses is at least 750 pg/ml, 800 pg/ml, 900 pg/ml, 1000 pg/ml, 1100 pg/ml, or 1200 pg/ml.
  • the mean DHE C max achieved following administration of a dose is at least 1250, 1300, 1350, 1400, 1450 or 1500 pg/ml.
  • the mean DHE C max achieved following administration of a dose is at least 750 pg/ml, 800 pg/ml, 900 pg/ml, 1000 pg/ml, 1100 pg/ml, or 1200 pg/ml. In certain embodiments, the mean DHE C max achieved following administration of a dose is at least 1250, 1300, 1350, 1400, 1450 or 1500 pg/ml. In particular embodiments, the mean DHE C max achieved following administration of a dose is 1000-1500 pg/ml, 1100-1400 pg/ml, or 1200-1300 pg/ml.
  • the mean time to C max (T max ) of DHE following administration is less than 55 minutes. In typical embodiments, the DHE T max is less than 50 minutes, 45 minutes, 40 minutes, or 35 minutes. In some embodiments, the T max of DHE following administration is 30-50 minutes, or 35-45 minutes. In particular embodiments, the DHE T max is no more than 35 minutes, 40 minutes, or 45 minutes.
  • the mean plasma AUC 0-inf of DHE following administration is at least 3000 pg*hr/ml, 4000 pg*hr/ml, 5000 pg*hr/ml, or 6000 pg*hr/ml. In various embodiments, the mean plasma AUC 0-inf of DHE following administration is at least 7000 pg*hr/ml, 8000 pg*hr/ml, 9000 pg*hr/ml, or 10,000 pg*hr/ml.
  • the mean plasma AUC 0-inf of DHE following administration is at least 5000, 5100, 5200, 5300, 5400, 5500, 5600, 5700, 5800, 5900, or 6000 pg*hr/ml. In some embodiments, the mean plasma AUC 0-inf of DHE following administration is greater than 6000, 5900, 5800, 5700, 5600, 5500, 5400, 5300, 5200, 5100 or 5000 pg*hr/ml.
  • the mean peak plasma concentration (C max ) of 8′-OH-DHE is at least 50 pg/ml. In certain embodiments, the mean C max of 8′-OH-DHE is at least 55 pg/ml.
  • the mean plasma AUC 0-inf of 8′-OH-DHE is at least 500 pg*hr/ml. In some embodiments, the mean plasma AUC 0-inf of 8′-OH-DHE is at least 600 pg*hr/ml, 700 pg*hr/ml, 800 pg*hr/ml, 900 pg*hr/ml, or even at least 1000 pg*hr/ml.
  • the mean plasma AUC 0-inf of 8′-OH-DHE is at least 1100 pg*hr/ml, 1200 pg*hr/ml, 1250 pg*hr/ml, 1300 pg*hr/ml, 1400 pg*hr/ml, or 1500 pg*hr/ml.
  • the methods described herein are used to acutely treat migraine headache, with or without aura.
  • the subject has had onset of at least one prodromal symptom of migraine, without onset of headache pain. In certain embodiments, the subject has had onset of at least one prodromal symptom selected from neck stiffness, facial paresthesia, photosensitivity, acoustic sensitivity, and visual aura.
  • the subject has had onset of at least one symptom associated with acute migraine.
  • the subject has had onset of at least one symptom selected from visual aura; headache pain, including dull, throbbing, or pulsing pain; photosensitivity; acoustic sensitivity; nausea; vomiting.
  • Visual aura and headache pain may be unilateral or bilateral, focal or diffuse.
  • administration is performed within 5 minutes, 10 minutes, 15 minutes, or 30 minutes of onset of at least one prodromal symptom. In various embodiments, administration is performed within 5 minutes, 10 minutes, 15 minutes, or 30 minutes of onset of at least one acute symptom.
  • migraine to be treated is associated with menstruation. In some embodiments, migraine to be treated has proven resistant to triptans.
  • the methods are used for acute treatment of cluster headaches rather than migraine.
  • the dose is administered by an intranasal delivery device that provides, following intranasal administration, (a) a mean peak plasma DHE concentration (C max ) of at least 750 pg/ml, (b) with a mean time to C max (T max ) of DHE of less than 45 minutes, and (c) a mean plasma AUC 0-inf of DHE of at least 2500 pg*hr/ml.
  • C max mean peak plasma DHE concentration
  • T max mean time to C max
  • T max mean plasma AUC 0-inf of DHE of at least 2500 pg*hr/ml.
  • the intranasal administration device is a “compound delivery device” as described in U.S. Pat. No. 9,550,036, the disclosure of which is incorporated herein by reference in its entirety.
  • the intranasal administration device is a “medical unit dose container” device as described in WO 2014/179228, the disclosure of which is incorporated herein by reference in its entirety.
  • the intranasal delivery device is a manually actuated, propellant-driven, metered-dose intranasal administration device.
  • the liquid pharmaceutical composition and propellant are not in contact within the device prior to first manual actuation, and, optionally, not in contact within the device between successive manual actuations.
  • the device typically comprises a vial and a canister, wherein the liquid pharmaceutical composition is contained in the vial and the propellant is contained in the canister.
  • the canister is a pressurized canister of propellant.
  • the propellant is a hydrofluoroalkane propellant suitable for pharmaceutical use.
  • the propellant is hydrofluoroalkane-134a.
  • each manual actuation brings a metered volume of liquid pharmaceutical composition and a separately metered volume of propellant into contact within a dose chamber of the device.
  • Contact of propellant with liquid pharmaceutical composition within the dose chamber of the device propels the dose towards the nozzle of the device, creating a spray as the dose is expelled through the nozzle of the device.
  • the nozzle has a plurality of lumens, and the spray is ejected simultaneously through a plurality of nozzle lumens.
  • the device delivers at least a portion of the dose of liquid pharmaceutical composition to the nasal cavity beyond the nasal valve, including delivery to the turbinates and/or the olfactory region. In certain embodiments, the device delivers at least 25%, 30%, 40%, 50%, 60%, or 70% of the dose of liquid pharmaceutical composition beyond the nasal valve. In certain embodiments, the device delivers liquid pharmaceutical composition so that at least 25%, 30%, 40%, 50%, 60%, or 70% of the dose of liquid pharmaceutical composition is brought into contact with the upper third of the nasal cavity (nasal epithelium) of the subject.
  • the in-line nasal delivery device 1 includes a housing 10 , diffuser 20 , tip 35 , nozzle 40 , dose chamber 45 , an actuator 50 , and a pump 25 to move the liquid pharmaceutical composition into the dose chamber 45 .
  • the in-line nasal device 1 is associated and cooperative with a propellant canister 5 , a propellant valve 15 , and a vial 30 of liquid pharmaceutical composition cooperative with the pump 25 to move the liquid pharmaceutical composition into the dose chamber 45 .
  • the diffuser 20 is a frit 21 (not shown in FIG. 1 ).
  • the diffuser provides for the conversion of the liquefied propellant in the propellant canister 5 to gas and/or an increase in temperature of the propellant.
  • the propellant valve 15 is a metered dose propellant valve 16 .
  • the liquid pharmaceutical composition is supplied in the form of a sealed vial 30 , e.g., of glass.
  • the vial 30 has a neck 31 (not shown) that is sealed by a removable closure 32 (not shown), for example but not limited to sealed with a plastic cover, crimped metal seal, and rubber stopper (for stability and sterility purposes).
  • a removable closure 32 for example but not limited to sealed with a plastic cover, crimped metal seal, and rubber stopper (for stability and sterility purposes).
  • the closure 32 is removed, the device 1 can be engaged with the vial 30 .
  • device 1 can be engaged with vial 30 by cooperation with the neck 31 of the vial 30 .
  • sealed vial 30 and device 1 can be co-packaged into a kit to be assembled at time of use.
  • vial 30 is a 3.5-mL amber glass vial.
  • a pump 25 moves the liquid pharmaceutical composition into the dose chamber 45 .
  • the propellant canister 5 is a canister of a compressed gas or a liquefied propellant.
  • Compressed gases include but are not limited to compressed air and compressed hydrocarbons.
  • the compressed gas is nitrogen or carbon dioxide.
  • Liquefied propellants include but are not limited to chlorofluorocarbons and hydrofluoroalkanes.
  • propellant canister 5 contains HFA-134a.
  • the canister 5 will generally be provided with a propellant valve 15 by which the gas flow can be controlled.
  • the tip 35 includes a nozzle 40 .
  • the nozzle 40 has a plurality of nozzle openings 41 (not shown) (synonymously, nozzle lumens). Through the plurality of nozzle openings 41 , the liquid pharmaceutical composition and propellant is delivered to the nasal cavity.
  • FIG. 2 shows the device 1 at rest ( FIG. 2A ) and in actuation ( FIGS. 2B and 2C ).
  • the staging of the device 1 actuation is as follows.
  • the housing 10 is compressed to prime the propellant canister 5 .
  • an actuator 50 remains stationary in the housing 10 while the propellant canister 5 and the vial 30 move towards the actuator 50 .
  • the propellant valve 15 associated with the propellant canister 5 is not actuated by compression.
  • the actuator 50 acts upon the pump 25 compressing the pump 25 and the liquid pharmaceutical composition from the vial 30 is moved into the dose chamber 45 .
  • the actuator 50 acts upon the propellant valve 15 and the propellant valve 15 begins to compress.
  • the continued depression of the actuator 50 releases the propellant from the propellant canister 5 .
  • the propellant pushes the liquid pharmaceutical composition as it exits the device 1 through the nozzle openings (lumens) 41 (not shown) of the nozzle 40 located in the tip 35 .
  • the actuator 50 provides for first actuation of the pump 25 , then once the pump 25 bottoms out, the continued depression of the actuator 50 provides for release of the propellant from the canister 5 .
  • FIG. 3 shows yet another implementation of the device 100 .
  • the device 100 can deliver a single or multiple dose from a vial 30 or other container.
  • the device 100 allows for multiple doses to be delivered from the vial 30 , or a single dose.
  • the vial 30 may contain a volume of liquid pharmaceutical composition for multiple doses, while the user may decide to only deliver a single dose from the vial 30 .
  • the liquid pharmaceutical composition may be a drug, active pharmaceutical ingredient, or a pharmaceutical formulation.
  • the vial 30 may be separate from the rest of the assembled device 100 .
  • the device 100 and vial 30 are taken out of their respective packaging.
  • the vial 30 will generally be sealed.
  • the vial 30 is covered by a plastic cover, metal seal and stopper, the plastic cover and metal seal are pulled away from the top of the vial 30 , and the rubber stopper is removed from the vial 30 .
  • the vial 30 may be screwed into a pump fitment 180 located at the base of the device 100 .
  • the vial 30 may have female threads which can be screwed into male threads on a pump fitment 180 , or vice versa.
  • the vial 30 may contain, for example but not limited to, inclusive of end points, 2-3 ml, in another embodiment 2-2.5 ml of liquid pharmaceutical composition.
  • the device 100 includes a housing 110 .
  • the housing 110 contains components of the device 100 including the Y-junction 120 .
  • the Y-junction 120 has three branches radiating from a common base.
  • the Y-junction and its three branches may be a molded component.
  • the Y-junction 120 establishes both fluid and gas paths within the device 100 , and connects the metered dose pump 130 , the dose chamber 150 , and the propellant canister 140 when the propellant canister 140 is assembled with the device.
  • the user will generally orient the device 100 with the propellant canister 140 assembled and located at the top and the vial 30 assembled and located at the bottom.
  • the optional check-valve 160 (attached to the metered dose pump 130 stem) press fits into a receiving hub of a first branch of the Y-junction 120 .
  • An internal bore provides fluid communication from the metered dose pump 130 , through the optional check-valve 160 and to a third branch of the Y-junction 120 , which connects to the dose chamber 150 .
  • the check valve 160 is an elastomeric component that installs within a plastic housing between the metered dose pump 130 and the Y-junction 120 .
  • the optional check valve 160 (a) reduces or eliminates dose leakage which could occur through the metered dose pump 130 if the pump stem was depressed and the propellant canister 140 was actuated; (b) allows for improved consistency in dose delivery by the device 100 ; and/or provides that liquid pharmaceutical composition is not pushed back down the internal dose loading channel 230 of the Y-junction 120 and into the metered dose pump 130 .
  • the propellant canister 140 When oriented as to be used in operation, housed within the device's 100 housing 110 , towards the top of the device 100 , the propellant canister 140 press fits into a second branch of the Y-junction 120 , establishing the gas path through internal bores, through the diffuser 170 and to the dose chamber 150 .
  • the diffuser 170 is annular. As shown in FIG. 4 , the annular diffuser 170 sits inside a bore on the back end of the dose chamber 150 . The external diameter of the annular diffuser 170 is in a compression fit with the dose chamber 150 . In other embodiments, not shown, the annular diffuser is fixed to the dose chamber using means other to or in addition to compression fit.
  • An internal dose loading channel 230 which is molded as a portion of the Y-junction 120 fits into the inner bore of the annual diffuser 170 when the dose chamber 150 is installed onto the Y-junction 120 .
  • the inner diameter of the annular diffuser 170 is in compression with the internal dose loading channel 230 portion of the Y-junction 120 .
  • the annular diffuser 170 is seated between the outer wall of the internal dose loading channel 230 and the inner wall of the dose chamber 150 , sealing against both of those surfaces to form the bottom of the dose chamber 150 . Additional embodiments of the diffuser 170 , dose chamber 150 , and Y-junction 120 are discussed with regards to FIGS. 12-13 .
  • the diffuser 170 is a frit 171 (not shown). In other embodiments, the diffuser 170 is a component that is homogenously or heterogeneously porous. In some embodiments, the diffuser 170 may be a disk-shaped member.
  • the diffuser 170 (a) provides for the conversion of the liquefied propellant in the propellant canister 140 to gas; (b) provides an increase in temperature of the propellant; (c) acts to prevent the propellant from flowing back into the device 100 ; (d) acts to prevent the liquid pharmaceutical composition from flowing back into the device 100 ; and/or (e) acts to allows gas flow into the dose chamber 150 while preventing the liquid pharmaceutical composition from leaking out.
  • the diffuser may be made of a porous polymer material.
  • the relationship in operation of the device 100 between the liquid pharmaceutical composition, the diffuser 170 , the inner dose loading tube 230 , the dose chamber 150 and the Y-junction 120 are shown at least in FIG. 6 .
  • the liquid pharmaceutical composition being loaded into the dose chamber 150 takes the less restrictive route, flowing out of the vial 30 and filling the dose chamber 150 rather than loading backwards through the diffuser 170 and into the delivery path of the propellant of the Y-junction 120 .
  • the staging of operation and the amount of time required for operation of the device allows the diffuser 170 to restrict liquid pharmaceutical composition from flowing back into the Y-junction 120 for the period of time needed, as the propellant canister 140 is activated after liquid pharmaceutical composition loading.
  • the entire actuation of the device 100 is approximately a second or less than a second.
  • the loaded dose in the dose chamber 150 does not have enough time to flow backwards into the Y-junction 120 .
  • the propellant expels the liquid pharmaceutical composition from the device 100 .
  • the dose chamber 150 press fits into the Y-junction 120 , completing the flow paths for both gas and fluid through the device.
  • the angle is 30 degrees, 35 degrees, 40 degrees, 45 degrees, 50 degrees, 55 degrees, 60 degrees, inclusive of endpoints and intervening degrees.
  • the Y-junction 120 may contain engagement ribs (not shown) to help secure and position the assembly within the housing 110 of the device 100 .
  • the device 100 includes a pump fitment 180 .
  • the pump fitment 180 secures the metered dose pump 130 to the vial 30 and holds both components in place during device 100 use.
  • One series of embodiments of the pump fitment 180 is that it consists of engagement ribs that retain it within the housing 110 , provide vertical displacement, and prevent rotation during installation of the vial 30 .
  • the device 100 includes a dose chamber 150 .
  • the dose chamber 150 receives and stores the liquid pharmaceutical composition that has been pushed out of the inner tube of the Y-junction 120 .
  • the propellant canister 140 is actuated, the Y-junction 120 and dose chamber 150 are pressurized and the propellant gas expels the liquid pharmaceutical composition out of the dose chamber 150 .
  • the dose chamber 150 is press fit into the Y-junction 120 .
  • the nozzle 190 is installed into the end of the dose chamber 150 opposite where it is press fit into the Y-junction 120 .
  • the nozzle 190 is installed into the distal end (end opposite where the dose chamber 150 is press fit into the Y-junction 120 ) of the dose chamber 150 , forming a liquid and gas-tight seal around the outer diameter.
  • propellant evacuates liquid pharmaceutical composition from the dose chamber 150 , pushing it out the nozzle 190 .
  • the nozzle 190 forms the narrow plume angle (for example, an angle of 1 to 40 degrees, including endpoints and angles intermittent there between; in one series of embodiments the angle is 5 degrees, 10 degrees, 15 degrees, 20 degrees, 25 degrees, 30 degrees, 35 degrees) multi-stream deposition.
  • the nozzle 190 and resultant angle of the plume produced promotes delivery of the liquid pharmaceutical composition to the olfactory region of the user's nasal cavity.
  • the device 100 may include an optional nose cone 200 .
  • the external geometries of the nose cone 200 assist in providing proper alignment of the device 100 during insertion into the nose.
  • the diametrically opposed flat sides aid with placement against the septum of either naris, with the depth stop providing correct depth of insertion.
  • the nose cone 200 adds redundancy to nozzle 190 retention through mechanical interference incorporated into the design.
  • there is an opening in the nose cone 200 which aligns with the nozzle 190 .
  • the nose cone 200 is not part of the pressurized flow path.
  • the housing 110 represents the body of the device 100 .
  • the housing 110 includes two different “clamshells” concealing the components of the device 100 and retaining all components to ensure functionality.
  • the housing 110 houses the metered dose pump 130 and pump fitment 180 , the actuator grip 210 , the Y-junction 120 , the propellant canister 140 , and the dose chamber 150 .
  • the nose cone 200 engages onto the outer geometry of the housing 110 , or may be optionally integrated into the design of the clamshells. An additional embodiment of the nose cone 200 is discussed with regards to FIG. 14 .
  • the housing 110 is designed to assemble easily through the use of, for example but not limited to, mattel pins, snaps, post or screws, or a combination thereof, molded into the geometry.
  • the actuator grip 210 provides for actuation displacement by the user.
  • the actuator grip 210 is composed of two parts, actuator grip A and actuator grip B and surround the Y-junction 120 and reside within the housing 110 .
  • FIG. 7 shows two finger grip notches 215 are designed into the actuator grip 210 to allow the user to engage the device 100 with the fingers, for example but not limited to, the index and middle finger. These finger grip notches 215 allow the user to apply downward movement leading to device 100 actuation.
  • the metered dose pump 130 draws liquid pharmaceutical composition up from the vial 30 to the Y-junction 120 .
  • the metered dose pump 130 may utilize a custom pump fitment 180 to promote functionality within the device 100 , and allow attachment of the vial 30 via threads.
  • the metered dose pump 130 may deliver, for example but not limited to, volumes of 130 ⁇ l, 140 ⁇ l, 150 ⁇ l, 160 ⁇ l, 170 ⁇ l, 180 ⁇ l, 190 ⁇ l, 200 ⁇ l, or 230 ⁇ l during actuation. Commercially available metered dose pumps 130 can be used.
  • the metered dose pump 130 For the device 100 to consistently deliver liquid pharmaceutical composition, the metered dose pump 130 must first deliver liquid pharmaceutical composition, followed by propellant canister 140 actuation to expel the liquid pharmaceutical composition. As shown in FIG. 7 , one manner in which to accomplish this is via a conical spring 220 between the propellant canister 140 and Y-junction 120 to create the necessary propellant canister 140 actuation force resulting in the correct order of actuation between the metered dose pump 130 and propellant canister 140 . In one implementation, a conical spring 220 is used, although this force is not limited to being produced by a conical spring 220 as other mechanisms can be used.
  • the conical spring 220 has a near zero preload, with a k value of about 25.5 lbf in and a maximum load of 3.2 lbf. Selection of the spring or mechanism will include the considerations of: (a) providing for proper device 100 staging; (b) physical space in the device 100 ; and/or (c) and user feedback regarding how stiff of a conical spring 220 still allows a variety of users to activate the device 100 .
  • the conical spring 220 is installed inline between the propellant canister 140 and Y-junction 120 .
  • the actuator grip 210 physically holds the propellant canister 140 .
  • the user activates the device 100 by, for example, applying an in-line force acting down from the actuator grips 210 , and up from the vial 30 . This force simultaneously acts to activate both the metered dose pump 130 and the propellant canister 140 .
  • the conical spring 220 acts in parallel to the internal propellant canister metering valve spring, increasing the necessary force required to activate the propellant canister 140 .
  • the device 100 By choosing the conical spring 220 such that the necessary force required to actuate the propellant canister 140 is in excess of the maximum necessary force required to completely actuate the metered dose pump 130 , the device 100 provides that dose is loaded into the dose chamber 150 before propellant gas begins to expel liquid pharmaceutical composition from the device 100 .
  • an extension spring is used in lieu of a conical spring.
  • the extension spring is discussed with regards to FIG. 12A .
  • the metered dose pump 130 draws liquid pharmaceutical composition up from the vial 30 at the bottom of the device 100 via the Y-junction 120 , through the internal dose loading channel 230 and into the dose chamber 150 .
  • the internal dose loading channel 230 provides a clear route for the liquid pharmaceutical composition to be loaded ahead of the diffuser 170 , without needed to physically pass through the porous material of the diffuser 170 .
  • small arrow heads represent the flow of the propellant while large arrow heads represent the flow of the liquid pharmaceutical composition.
  • Priming shots may be required to completely fill the metered dose pump 130 and internal dose loading channel 230 of the Y-junction 120 prior to user dosing.
  • An optional dose cap (not shown) may cover the nose cone 200 of the device 100 and captures the priming shots while also providing a means of visual indication to the user that the device is primed.
  • the propellant canister 140 releases propellant which enters through the top of the Y-junction 120 , following the path shown by smaller arrow heads in FIG. 6 .
  • the propellant flows physically through the porous material of the diffuser 170 , which promotes the vaporization of the propellant.
  • the diffuser 170 and the path along which the propellant travels convert liquid propellant into gas propellant, resulting in expansion and propulsion of the propellant.
  • the propellant first contacts the liquid pharmaceutical composition at the proximal (distal being closer to the nozzle 190 , proximal being farther away from the nozzle 190 ) face of the diffuser 170 as seated in the device 100 . As the propellant continues to expand, it pushes the liquid pharmaceutical composition forward (toward the nozzle 190 ) in the dose chamber 150 , exiting though the nozzle 190 at the end of the dose chamber 150 .
  • the propellant canister 140 provides the propulsive energy for the device 100 .
  • the stem of the propellant valve seats into the top receiver of the Y-junction 120 .
  • the user presses down on the actuator grips 210 which pulls the propellant canister 140 body down, actuating the propellant valve. This releases a metered volume of liquid propellant.
  • the liquid pharmaceutical composition is forced toward the distal end of dose chamber 150 and out through the nozzle 190 .
  • the propellant canister 140 uses HFA 134A as the propellant for the system.
  • Other propellants are envisioned.
  • the device, propellant canister, and vial containing liquid pharmaceutical composition are provided separately, optionally co-packaged into a kit, and thereafter assembled for use.
  • propellant canister 140 is provided assembled within device 100 and the vial containing liquid pharmaceutical composition is provided separately, optionally with the device (with integrated canister) and vial co-packaged into a kit.
  • the device, propellant canister, and vial containing liquid pharmaceutical composition are provided to the user fully assembled.
  • the device comprises the following parts; part numbering is as depicted in FIGS. 9A and 9B .
  • ABS acrylonitrile butadiene styrene
  • CMO contract manufacturing organization
  • HDPE high density polyethylene
  • HFA hydrofluoroalkane-134a
  • LCP liquid crystal polymer
  • LDPE low density polyethylene
  • PE polyethylene
  • POM polyacetal copolymer
  • PP polypropylene
  • the vial contains liquid pharmaceutical composition in an amount sufficient for at least one total dose of DHE, or salt thereof, to be delivered by the device, in a single undivided or a plurality of divided doses.
  • the vial contains liquid pharmaceutical composition in an amount sufficient for at most one total dose of DHE, or salt thereof, to be delivered by the device, in a single undivided or a plurality of divided doses.
  • the propellant canister contains pressurized propellant in an amount sufficient for optional priming of the device followed by delivery of at least one total dose of DHE, or salt thereof, to be delivered by the device, in a single undivided or a plurality of divided doses.
  • the propellant canister contains pressurized propellant in an amount sufficient for optional priming of the device followed by delivery of at most one total dose of DHE, or salt thereof, to be delivered by the device, in a single undivided or a plurality of divided doses.
  • the quantity of pressurized liquid hydrofluoroalkane is sufficient to permit a predetermined number of device actuations. In some of these embodiments, the quantity is sufficient to permit 2, 3, 4, 5, 6, 7 or 8 actuations. In some embodiments, the quantity is sufficient to permit 10, 11, 12, 13, 14, 15, or even 20 actuations. In certain embodiments, a majority of the pressurized liquid hydrofluoroalkane is converted to gaseous hydrofluoroalkanes after 2, 3, 4, 5, 6, 7, or 8 actuations. In certain embodiments, a majority of the pressurized liquid hydrofluoroalkane is converted to gaseous hydrofluoroalkanes after 10, 11, 12, 13, 14, 15, or 20 actuations.
  • FIG. 12A shows a cross section of an alternate implementation of the in-line nasal delivery device 1200 .
  • the in-line nasal delivery device 1200 may be an embodiment of the in-line nasal delivery device 100 .
  • the device 1200 may use the same or similar components as the device 100 , as described with regards to FIGS. 3-9 . Additionally, components of device 1200 and device 100 may be used interchangeably or in some combination thereof.
  • the device 1200 includes a housing 12110 , a Y-junction 12120 , a metered dose pump 12130 , a propellant canister 12140 , a dose chamber 12150 (shown in FIG. 13 A), a check valve 12160 , a diffuser 12170 (shown in FIG.
  • the housing 12110 includes an upper portion 1205 and a bottom portion 1210 .
  • the device 1200 additionally includes an extension spring 1215 and a check valve adapter 1220 .
  • the actuator grip 12210 provides for actuation displacement by the user.
  • the actuator grip 12210 surrounds the Y-junction 12120 and resides within the housing 12110 .
  • FIG. 12A shows two finger grip notches 12215 that are designed into the actuator grip 12210 to allow the user to engage the device 1200 with the fingers, for example but not limited to, the index and middle finger.
  • the finger grip notches 12215 allow the user to engage or grip the device in order to cause device 1200 actuation.
  • the actuator grip 12210 includes a guiding feature 1225 that extends along a length of the housing 12110 behind (as illustrated in FIG. 12A ) the propellant canister 12140 and captures an end of the propellant canister 12140 .
  • the end is the bottom of the propellant canister 12140 , which is opposite from the end containing the valve for propellant dispersal.
  • the guiding feature 1225 may capture the end of the propellant canister 12140 by folding above or adhering to the end.
  • the propellant canister 12140 is nested within the guiding feature 1225 such that the guiding feature 1225 securely supports the propellant canister 12140 .
  • the guiding feature 1225 is securely coupled to a larger, more rigid surface area of the propellant canister 12140 than when coupled to a narrow surface, such as the propellant valve 15 in the embodiment of device 1 .
  • the guiding feature 1225 transmits the downward force to the propellant canister 12140 , thereby actuating the propellant canister 12140 .
  • the guiding feature 1225 actuates the propellant canister 12140 in a stable manner and is less likely to lose its physical coupling to the propellant canister 12140 .
  • the propellant canister 12140 is entirely enclosed within the housing 12110 .
  • the propellant canister 12140 is enclosed by the upper portion of the housing 1205 , which may be formed during manufacturing from at least two separate parts.
  • the Y-junction 12120 is fixed in place with the bottom housing portion 1210 , with the guiding feature 1225 extending upward to establish the position of the propellant canister 12140 with respect to the Y-junction 12120 . This structure ensures that the propellant canister 12140 moves relative to the Y-junction 12120 during actuation, to which it is fluidly coupled.
  • the extension spring 1215 creates an actuation force that ensures a desired order of actuation between the metered dose pump 12130 and the propellant canister 12140 .
  • the metered dose pump 12130 first delivers liquid pharmaceutical composition to the dose chamber 12150 , followed by propellant canister 12140 actuation to expel the liquid pharmaceutical composition.
  • the force of the extension spring 1215 is established to both provide proper order of actuation and enable ease of actuation by users.
  • the extension spring 1215 is coupled to the housing upper portion 1205 and the actuator grip 12210 . As illustrated in FIG. 12A , a first end of the extension spring 1215 couples to a boss 1230 on the housing upper portion 1205 , and a second end of the extension spring 1215 couples to a boss 1235 on the actuator grip 12210 . In the embodiment of FIG. 12A , the housing upper portion 1205 and the actuator grip 12210 translate relative to one another during actuation of the device 1200 . The extension spring 1215 is coupled to each component such that the extension spring 1215 creates a resisting force when the housing upper portion 1205 and the actuator grip 12210 translate away from each other.
  • the user activates the device 1200 by, for example, applying an in-line force acting down from the actuator grips 12210 , and up from the vial containing the pharmaceutical composition.
  • This applied force actuates both the metered dose pump 12130 of the vial and the propellant canister 12140 .
  • a threshold (higher) force to actuate the propellant canister 12140 is achieved after a threshold (lower) force to actuate the metered dose pump 12130 is achieved, such that the applied force first exceeds the threshold force of the metered dose pump 12130 .
  • actuation of the device 1200 first activates the metered dose pump 12130 and then activates the propellant canister 12140 such that dose is loaded into the dose chamber 12150 before propellant begins to expel liquid pharmaceutical composition from the device 1200 .
  • the extension spring 1215 may be used in lieu of or in addition to the conical spring 220 .
  • the configuration of the extension spring may streamline the assembly process of the device relative to the configuration of the conical spring, as the conical spring may create a resisting force between the propellant canister 140 and Y-junction 120 such that the components are pushed apart during assembly, whereas the extension spring may pull the components towards each other.
  • the configuration of the extension spring may prolong the shelf life and overall lifetime of the device relative to the configuration of the conical spring.
  • the check valve adapter 1220 is an adapter that couples the check valve 12160 and the Y-junction 12120 .
  • the check valve 12160 may be an embodiment of check valve 160 .
  • the check valve adapter 1220 is a cylindrical component having a first end that inserts into a channel of the Y-junction 12120 and mates with the check valve 12160 positioned within the channel of the Y-junction 12120 and a second end that mates with the metered dose pump 130 . As illustrated in the zoomed-in view in FIG.
  • an end of the check valve 12160 comprises a flange that is captured at an end of the channel of the Y-junction 12120 and mates with a respective interface of the check valve adapter 1220 .
  • the check valve 12160 and/or check valve adapter 1220 may be secured at each end with an adhesive, ultrasonic welding, an interference fit (e.g., press fit, friction fit, or similar), or some combination thereof.
  • the check valve adapter 1220 may augment the function of the check valve 12160 by improving the seal between the check valve 12160 and the Y-junction 12120 . As discussed with regards to FIG.
  • a check valve may: (a) reduce or eliminate dose leakage which could occur through the metered dose pump if the pump stem was depressed and the propellant canister was actuated; (b) allow for improved consistency in dose delivery by the device; and/or (c) provide that liquid pharmaceutical composition is not pushed back down an internal dose loading channel of the Y-junction and into the metered dose pump.
  • FIG. 13A shows a cross section of a diffuser 12170 as seated within the device 1200 , according to an additional embodiment.
  • the diffuser 12170 may be an embodiment of the diffuser 170 .
  • the diffuser 12170 is annular.
  • the diffuser 12170 sits on a shelf 1305 inside a bore 1310 of the Y-junction 12120 , and the dose chamber 12150 is inserted into the bore 1310 of the Y-junction 12120 .
  • the diffuser 12170 is seated between the shelf of the bore of the Y-junction 12120 and a bottom face of the dose chamber 12150 , sealing against both of those surfaces.
  • the diffuser 12170 may further be sealed along its inner diameter to the Y-junction 12120 .
  • the diffuser 12170 creates an interference seal along its inner diameter, its upper face, and its lower outer edge (in contact with the shelf 1305 ).
  • This configuration may allow expansion of the diffuser 12170 , for example, as propellant flows through the diffuser 12170 due to changes in temperature or as a result of device assembly. Sealing the diffuser 12170 along its inner diameter may improve the consistency and/or quality of the seal and/or performance of the diffuser 12170 relative to sealing the diffuser 12170 along its top and bottom faces in a compression fit, which could compress the diffusion path within (the path along which propellant travels and is diffused).
  • the tolerances of the outer diameter of the diffuser 12170 may not need to be as precisely controlled to prevent bending of the diffuser 12170 such that flatness of the diffuser 12170 is maintained to ensure a proper compression fit along its faces.
  • the interference seal may or may not be liquid or gas tight.
  • FIG. 13B shows an exploded view of the dose chamber 12150 and the Y-junction 12120 , according to an additional embodiment.
  • FIG. 13B illustrates the bore 1310 and the shelf 1305 of the Y-junction 12120 .
  • the dose chamber 12150 may include a chamfer 1315 around an outer edge of its bottom face such that the dose chamber 12150 may be easily inserted into the bore 1310 .
  • the configuration of the dose chamber 12150 and Y-junction 12120 may be reversed such that the dose chamber 12150 includes a bore into which a diffuser and an end of the Y-junction 12120 is inserted.
  • FIG. 14 illustrates the nose cone 12200 , according to an additional embodiment.
  • the nose cone 12200 may be an embodiment of the nose cone 200 .
  • the external geometries of the nose cone 12200 assist in providing proper alignment of the device 1200 during insertion into the nose.
  • the nose cone 12200 comprises an opening 1405 that aligns with the nozzle (not shown).
  • the dose chamber 12150 (not shown in this view) may be positioned between two bosses 1410 a , 1410 b that maintain the alignment of the dose chamber 12150 and the nozzle within the nose cone 12200 .
  • the nose cone 12200 is integrated into the design of the clamshells.
  • the nose cone 12200 and the clamshells may be molded together during manufacturing, decreasing the overall part count of the device 1200 and enabling easy assembly of the device 1200 .
  • kits are provided for acutely treating migraine with or without aura.
  • the kit comprises a vial and a device.
  • the vial is sealed, and sealably contains at least one effective dose of a liquid pharmaceutical composition comprising dihydroergotamine (DHE) or salt thereof.
  • DHE dihydroergotamine
  • the vial is configured to be attachable to the device.
  • the device is reciprocally configured to receive the vial.
  • the device Upon attachment of the vial to the device by the user, the device becomes a manually actuated, propellant-driven, metered-dose intranasal administration device capable of providing, after intranasal administration of a dose of liquid pharmaceutical composition, (a) a mean peak plasma DHE concentration (C max ) of at least 750 pg/ml, (b) with a mean time to C max (T max ) of DHE of less than 45 minutes, and (c) a mean plasma AUC 0-inf of DHE of at least 2500 pg*hr/ml.
  • C max mean peak plasma DHE concentration
  • T max mean time to C max
  • T max mean time to C max
  • the device upon attachment of the vial to the device, the device becomes a manually actuated, propellant-driven, metered-dose intranasal administration device as described in Section 5.3.5.3 above.
  • the device upon attachment of the vial to the device, the device becomes a manually actuated, propellant-driven, metered-dose intranasal administration device as particularly described in Section 5.3.5.3.1 above.
  • the propellant-containing canister is a pressurized canister that is sealed within the device and is not accessible to the user.
  • the vial is a sealed glass vial. In currently preferred embodiments, the vial is a 3.5-mL amber sealed glass vial.
  • the liquid pharmaceutical composition that is sealably contained within the vial is a liquid pharmaceutical composition as described in Section 5.3.2 above.
  • the vial comprises a liquid pharmaceutical composition having the following composition: a clear, colorless to faintly yellow solution in an amber glass vial containing:
  • dihydroergotamine mesylate USP 4.0 mg caffeine, anhydrous, USP 10.0 mg dextrose, anhydrous, USP 50.0 mg carbon dioxide, USP qs purified water, USP qs 1.0 mL.
  • the vial contains liquid pharmaceutical composition in an amount sufficient for at least one total dose of DHE, or salt thereof, to be delivered by the device, in a single undivided or a plurality of divided doses.
  • the vial contains liquid pharmaceutical composition in an amount sufficient for at most one total dose of DHE, or salt thereof, to be delivered by the device, in a single undivided or a plurality of divided doses.
  • the propellant canister within the device that is co-packaged with the vial in the kit contains pressurized propellant in an amount sufficient for optional priming of the device followed by delivery of at least one total dose of DHE, or salt thereof, to be delivered by the device either in a single undivided or a plurality of divided doses.
  • the propellant canister contains pressurized propellant in an amount sufficient for optional priming of the device followed by delivery of at most one total dose of DHE, or salt thereof, to be delivered by the device, in a single undivided or a plurality of divided doses.
  • Table 2 provides experimental data on one implementation of the in-line device described in Section 5.3.5.1.1 above.
  • dose refers to a volume delivered in a single device actuation.
  • DHE dihydroergotamine mesylate
  • the study was a three-period, three-way, randomized, open-label, single-dose, cross-over, comparative bioavailability study.
  • INP104 was self-administered using the I123 PODTM Device (Impel NeuroPharma, Seattle). The dose of DHE mesylate was divided, with one spray in each nostril delivering a total target dose of 1.45 mg DHE mesylate.
  • the I123 POD Device is a handheld, manually actuated, propellant-driven, metered-dose administration device intended to deliver a drug formulation to the nasal cavity.
  • Drug delivery to the nasal cavity via the I123 POD Device is driven by hydrofluoroalkane-134a (HFA) propellant.
  • HFA hydrofluoroalkane-134a
  • the I123 POD Device functions as an intranasal delivery device; the HFA propellant in the 1123 POD Device is not intended to deliver drug to the lungs and does not contact the DHE formulation until the time of delivery.
  • the INP104 drug component, DHE DP is a 3.5-mL amber glass vial filled with DHE mesylate 4 mg/mL.
  • the formulation is identical to that in the Migranal® Nasal Spray device: a clear, colorless to faintly yellow solution in an amber glass vial containing:
  • dihydroergotamine mesylate USP 4.0 mg caffeine, anhydrous, USP 10.0 mg dextrose, anhydrous, USP 50.0 mg carbon dioxide, USP qs purified water, USP qs 1.0 mL.
  • the DHE DP vial attaches to the I123 POD Device.
  • the I123 POD Device may have a nominal output between 175 ⁇ L/actuation pump and 205 ⁇ L/actuation pump (inclusive). In some embodiments, the I123 POD Device may have a nominal output that is about 175, 176, 177, 178, 179, 180, 181, 182, 183, 184, 185, 186, 187, 188, 189, 190, 191, 192, 193, 194, 195, 196, 197, 198, 199, 200, 201, 202, 203, 204, or 205 ⁇ L/actuation pump.
  • a single manual actuation of the device by the user results in the operation of the metering pump to fill the dose chamber with the DHE formulation and subsequent, but almost instantaneous, activation of the propellant canister to expel the formulation through the nozzle, as a spray, resulting in delivery to the nasal cavity of the user.
  • the device is designed to be disposed of after successful single divided-dose drug delivery (1 spray per nostril). Actuation of the I123 POD Device releases approximately 63 ⁇ L of HFA-134a propellant, similar to HFA exposure from metered-dose inhalers.
  • D.H.E. 45® (Valeant Pharmaceuticals, NDA 005929) was administered in a volume of 1 mL intravenously over 1 minute.
  • Migranal® (Valeant Pharmaceuticals, NDA 20148) Nasal Spray (2 mg) was self-administered with equal dosing to both nostrils.
  • one spray (0.5 mg) was administered in each nostril initially, followed by an additional spray (0.5 mg) in each nostril 15 minutes later.
  • PK samples for PK analysis were obtained, according to the clinical trial site's standard operating procedures (SOPs), within 15 minutes prior to dosing and at 5, 10, 20, 30, 40 and 50 minutes, and 1, 1.25, 1.5, 1.75, 2, 3, 4, 8, 12, 24, 36 and 48 hours after dosing.
  • SOPs standard operating procedures
  • the PK sampling timeclock was started following administration of the first dose of Migranal® Nasal Spray.
  • Pharmacokinetic parameters were computed from the individual plasma DHE and 8′-OH-DHE concentrations using a non-compartmental approach.
  • Appropriate validated PK software e.g., Phoenix WinNonlin v6.3 was used. The parameters that were determined and their definitions are provided in Table 4 below.
  • T max Time to maximum observed drug concentration. If the maximum value occurs at more than one time- point, T max is defined as the first time point with this value.
  • AUC 0-t Area under the drug concentration-time curve, calculated using linear-up log-down trapezoidal summation from time zero to the time of the last Measurable concentration.
  • k el Apparent terminal elimination rate constant, calculated by linear regression of the terminal linear portion of the log concentration vs. time curve.
  • AUC 0-inf Area under the drug concentration-time curve from time zero to infinity, calculated as AUC 0-t + Ct/k el .
  • t 1/2 Apparent elimination half-life, calculated as ln(2)/k el .
  • PK parameters were summarized by administration method using descriptive statistics (arithmetic means, SD, coefficients of variation [CV], sample size [N] minimum, maximum, median and geometric mean). Geometric mean was calculated for AUC 0-t , AUC 0-inf , and C max .
  • a comparative bioavailability assessment was undertaken to demonstrate (i) that the lower 90% confidence interval of the DHE after INP104 to DHE after Migranal Nasal Spray geometric mean ratios for C max and AUC (AUC 0-t , AUC 0-inf ) is not less than 80%, and (ii) the upper 90% confidence interval of the DHE after INP104 to D.H.E. 45 Injection (IV) geometric mean ratios for C max and AUC (AUC 0-t , AUC 0-inf ) not greater than 125%—i.e., to demonstrate that exposure is equal to or greater than 80% and equal to or less than 125% range observed between Migranal Nasal Spray and D.H.E. 45 Injection (IV), respectively.
  • Ratios of geometric means were calculated using the exponentiation of the difference between treatment LSM from the analyses on the ln-transformed AUC 0-t , AUC 0-inf and C max . These ratios were expressed as a percentage relative to the reference (comparator) treatment, i.e. INP104 [test]/Comparator [reference]. Consistent with the two one-sided tests for bioequivalence, 90% confidence intervals were obtained for the ratio of the geometric means for AUC 0-t , AUC 0-inf and C max .
  • INP104 As compared to Migranal Nasal Spray, INP104 provides nearly 3-fold higher mean systemic drug exposure, with an AUC 0-inf of 6,291 pg*hr/ml as compared to 2,248 pg*hr/ml for Migranal®. INP104 also provides nearly 4-fold higher mean maximal plasma concentration, with a C max of 1,258 pg/ml as compared to 318 pg/ml for Migranal®. Maximal DHE plasma concentration is reached faster with INP104, with a mean T max of 34 minutes versus 55 minutes for Migranal®.
  • the 8′OH-DHE metabolite of DHE is known to be active, and to contribute to the long-lasting effect of DHE on migraine.
  • the time course of plasma 8′-OH-DHE concentrations is plotted in FIGS. 11A and 11B .
  • Initial summary statistics for plasma concentrations of 8′OH-DHE are provided in Table 6, below.

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