U.S. patent application number 10/693318 was filed with the patent office on 2005-12-22 for method and device for delivering aerosolized medicaments.
Invention is credited to Patton, John S., Platz, Robert M..
Application Number | 20050279349 10/693318 |
Document ID | / |
Family ID | 24912427 |
Filed Date | 2005-12-22 |
United States Patent
Application |
20050279349 |
Kind Code |
A1 |
Patton, John S. ; et
al. |
December 22, 2005 |
Method and device for delivering aerosolized medicaments
Abstract
A device for accurately delivering aerosolized doses of a
medicament disperses a measured amount of drug in a measured volume
of carrier gas and transfers the resulting aerosol to a chamber
prior to inhalation by a patient. The chamber is filled efficiently
with the aerosol, and inhalation by the patient draws the aerosol
dose into the lungs. This is followed by the inhalation of
atmospheric air that will push the initial dose well into the lung
interiors. The apparatus optimally includes a dose regulator, a
counter, a clock, a dose memory and a signal to indicate when a
dose is ready for inhalation. Optimal chamber designs are
disclosed.
Inventors: |
Patton, John S.; (Portola
Valley, CA) ; Platz, Robert M.; (Half Moon Bay,
CA) |
Correspondence
Address: |
NEKTAR THERAPEUTICS
150 INDUSTRIAL ROAD
SAN CARLOS
CA
94070
US
|
Family ID: |
24912427 |
Appl. No.: |
10/693318 |
Filed: |
October 24, 2003 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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10693318 |
Oct 24, 2003 |
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09561690 |
May 1, 2000 |
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6681767 |
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09561690 |
May 1, 2000 |
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08979024 |
Nov 26, 1997 |
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6138668 |
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08979024 |
Nov 26, 1997 |
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08576885 |
Dec 22, 1995 |
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5775320 |
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08576885 |
Dec 22, 1995 |
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08313707 |
Sep 27, 1994 |
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08313707 |
Sep 27, 1994 |
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07910048 |
Jul 8, 1992 |
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5458135 |
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07910048 |
Jul 8, 1992 |
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07724915 |
Jul 2, 1991 |
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Current U.S.
Class: |
128/200.14 ;
128/203.15 |
Current CPC
Class: |
A61M 15/0086 20130101;
A61M 2205/073 20130101; A61M 2202/064 20130101; A61M 11/002
20140204; A61M 15/0015 20140204; A61M 15/008 20140204; A61M 2206/16
20130101; A61M 15/0066 20140204; A61M 16/0063 20140204; A61M 16/107
20140204 |
Class at
Publication: |
128/200.14 ;
128/203.15 |
International
Class: |
A61M 015/00; A61M
016/00 |
Claims
1. (canceled)
2. Au apparatus for producing aerosolized medicament, the apparatus
comprising: a reservoir containing a powder medicament to be
aerosolized, the powder medicament comprising a protein or
polypeptide; and a chamber comprising an inlet and a mouthpiece,
wherein gas may flow into the chamber through the inlet and may
flow out of the chamber through the mouthpiece and wherein the flow
of gas aerosolizes the powder medicament, wherein at least 40
percent by weight of the powder medicament is suspended by the gas
in the chamber for delivery rough the mouthpiece.
3. An apparatus according to claim 2 wherein the chamber volume is
from 100 ml to 750 ml.
4. An apparatus according to claim 2 further comprising a source of
compressed gas, wherein the compressed gas may be released if the
source of compressed gas to cause the flow of gas to aerosolize the
medicament.
5. An apparatus according to claim 2 wherein the chamber is adapted
contain the aerosolized medicament for subsequent delivery to a
patient during a patient's inhalation.
6. An apparatus according to claim 2 wherein the chamber is
cylindrical.
7. An apparatus according to claim 2 when the aerosolizes
medicament comprises small particles of medicament, the particles
being sized to be deliverable to the alveolar regions of the lungs
of a patient.
8. An apparatus according to claim 7 wherein the particles are
predominantly 1 to 5 micrometers in diameter.
9. An apparatus according to claim 2 wherein at least 55 percent by
weight of the powder medicament is suspended by the gas in the
chamber for delivery through die mouthpiece.
10. An apparatus according to claim 2 wherein at least 70 percent
by weight of the powder medicament is suspended by the gas in the
chamber for delivery through the mouthpiece.
11. An apparatus for producing aerosolized medicament, the
apparatus comprising: a reservoir containing a powder medicament to
be aerosolized, the powder medicament comprising a protein or
polypeptide; and a chamber comprising an inlet and a mouthpiece,
wherein gas may flow into the chamber through the inlet and may
flow out of the chamber through the mouthpiece and wherein the flow
of gas aerosolizes the powder medicament, wherein the volume of the
aerosolized medicament is from 9.24 percent to 21.5 percent of the
volume of the chamber.
12. An apparatus according to claim 11 wherein the chamber volume
is from 100 ml to 750 ml.
13. An apparatus according to claim 11 further comprising a source
of compressed gas, wherein the compressed gas may be released from
the source of compressed gas to cause the flow of gas to aerosolize
the medicament.
14. An apparatus according to claim 11 wherein the chamber is
adapted contain the aerosolized medicament for subsequent delivery
to a patient during a patient's inhalation.
15. An apparatus according to claim 11 wherein the chamber is
cylindrical.
16. An apparatus according to claim 11 wherein the aerosolizes
medicament comprises small particles of medicament, the particles
being sized to be deliverable to the alveolar regions of the lungs
of a patient.
17. An apparatus according to claim 16 wherein the particles are
predominately 1 to 5 micrometers in diameter.
18. An apparatus according to claim 11 wherein at least 40 percent
by weight of the powder medicament is suspended by the gas in the
chamber for delivery through the mouthpiece.
19. An apparatus according to claim 11 where at least 70 percent by
weight of the powder medicament is suspended by the gas in the
chamber for delivery trough the mouthpiece.
Description
[0001] The present invention is a continuation of U.S. application
Ser. No. 08/979,024, filed Nov. 26, 1997; U.S. application Ser. No.
08/576,885, filed Dec. 22, 1995; Ser. No. 08/313,707, filed Sep.
27, 1994; Ser. No. 07/910,048, filed Jul. 8, 1992; and a
continuation-in-part of application Ser. No. 07/724,915, filed on
Jul. 2, 1991, the full disclosures of which are incorporated herein
by reference.
BACKGROUND OF THE INVENTION
[0002] 1. Field of the Invention
[0003] This invention relates to a structure and method of
administering precisely measured doses of a therapeutic by
inhalation.
[0004] An accurate mechanism for delivering precise doses of
aerosol drugs into the interior of human lungs has been an
objective of many workers in the art. One of the most popular
aerosol delivery devices is the propellent-driven metered dose
inhaler (MDI), which releases a metered dose of medicine upon each
actuation. Although these devices may be useful for many medicines,
only a small variable percentage of the medicine is delivered to
the lungs. The high linear speed with which the dosage leaves the
device, coupled with incomplete evaporation of the propellants,
causes much of the medicine to impact and stick to the back of the
throat. This impacting and sticking creates a local concentration
of drugs much of which is eventually swallowed. In the trade, this
impact area is called a "hot spot" and can cause local
immuno-suppression and the development of fungal infections with
bronchosteriods. With broncodilators, for instance, the swallowed
dose can contribute to unwanted systemic side effects such as
tremor and tachycardia.
[0005] MDI's also require a degree of coordination between
activation and inhalation. Many patients are incapable of this
task, especially infants, small children and the elderly. In an
effort to overcome some of the above limitations of MDI's, others
have interposed "spacers" between the conventional MDI and the
patient. The primary function of these spacers is to provide extra
volume to allow time for increased propellent droplet evaporation
prior to inhalation and to reduce the velocity and impact of the
medicine at the back of the throat. Although spacers do compensate
for some of the inadequacies in the conventional MDI, it has been
found that much of the medicine that may have ordinarily been
deposit d on the throat remains in the spacer and the total dose
deposited in the lungs is small. It has been found that only
approximately 8% of the medicine reaches the interior of the lung
with conventional MDI's. Approximately 13% of the medicine reaches
the lung when it is equipped with a spacer.
[0006] Other workers in the art have attempted to provide a metered
dose of a medicant by using dry powder inhalers (DPI). Such devices
normally rely on a burst of inspired air that is drawn through the
unit. However, these units are disadvantaged in that the force of
inspiration varies considerably from person to person. Some
patients are unable to generate sufficient flow to activate the
unit. DPI's have many of the disadvantages of MDI's in that a large
percentage of the medicant is deposited in the throat because of
incomplete particle dispersion and the impact at the rear of the
throat. Although pocket size MDI's and DPI's are very convenient
they have disadvantages some of which are cited above.
[0007] Other workers in the art have refined aqueous nebulization
delivery systems. Although such systems require a continuous gas
compressor, making them less portable than the MDI's and the DPI's,
many nebulizers provide a low velocity aerosol which can be slowly
and deeply inhaled into the lungs. Precision of dosage delivery,
however, remains a serious problem and it is difficult to determine
how much medicament the patient has received. Most nebulizers
operate continuously during inhalation and exhalation. Dosage is
dependent on the number and duration of each breath. In addition to
breath frequency and duration, the flow rate, i.e., the strength of
the breath that is taken from a nebulizer can effect the particle
size of the dose inhaled. The patient's inhalation acts as a vacuum
pump that reduces the pressure in the nebulizer. A strong breath
can draw larger unwanted particles of medicant out of the
nebulizer. A weak breath, on the other hand, will draw insufficient
medicant from the nebulizer.
[0008] Electro-mechanical ventilators and devices have also been
used in recent years to deliver inhalable materials to a patient.
These devices permit mixing of a nebulized medicant into breathing
circuit air only during pre-set periods of a breathing cycle. An
example of this type of machine is the system taught by Edgar et
al., in their U.S. Pat. No. 4,677,975, issued in July of 1987 where
a nebulizer is connected to a chamber which in turn is connected to
a mouthpiece, an exhaust valve, and an inlet valve. A breath
detector and timer are used to deliver nebulized materials to the
patient during a portion of the breathing cycle. However, in Edgar
and others of this type, the patient's intake strength can effect
the nebulizer operation with many of the consequences heretofore
mentioned. Moreover, the amount of nebulized material delivered in
each breath can vary significantly, contributing to inaccurate
total dosages. In a modification of Edgar et al. (Elliott, et al.
(1987) Australian Paediatr. J. 23:293-297), filling of the chamber
with aerosol is timed to occur during the exhalation phase of the
breathing cycle so that the patient is not inhaling through the
device during nebulization. This design, however, requires that the
patient maintain a constantly rhythmic breathing pattern into and
out of the device, which is inconvenient and can contaminate the
device with oval microbes. Moreover, no provision is made on the
devices to efficiently capture the aerosol in the chamber so that
as many as 80 breaths or more must be taken to obtain a dose of
medication.
[0009] The delivery of therapeutic proteins and polypeptides by
inhalation presents additional problems. Many protein drugs are
produced recombinantly and can thus be very expensive. It is
therefore important that loss of a protein drug within the delivery
device be reduced or preferably eliminated. That is, substantially
all drug initially charged within the device should be aerosolized
and delivered to the patient without loss within the device or
released externally of the device. The protein drugs should further
be delivered to the patient under conditions which permit their
maximum utilization. In particular, protein drugs should be
completely dispersed into small particles in the preferred 1 .mu.m
to 5 .mu.m size range which is preferentially delivered to the
alveolar region of the lungs. The amount of protein drug delivered
to the patient in each breath must also be precisely measured so
that the total dosage of drug can be accurately controlled.
Finally, it will be desirable to permit the delivery of highly
concentrated aerosols of the protein drug so that the number of
breaths required for a given dosage can be reduced, thus increasing
accuracy and reducing the total time required for
administration.
[0010] 2. Description of the Background Art
[0011] U.S. Pat. Nos. 4,926,852 and 4,790,305, describe a type of
"spacer" for use with a metered dose inhaler. The spacer defines a
large cylindrical volume which receives an axially directed burst
of drug from a propellant-driven drug supply. U.S. Pat. No.
5,027,806, is an improvement over the '852 and '305 patents, having
a conical holding chamber which receives an axial burst of drug.
U.S. Pat. No. 4,624,251, describes a nebulizer connected to a
mixing chamber to permit a continuous recycling of gas through the
nebulizer. U.S. Pat. No. 4,677,975, is described above. European
patent application 347,779 describes an expandable spacer for a
metered dose inhaler having a one-way valve on the mouthpiece. WO
90/07351 describes a dry powder oral inhaler having a pressurized
gas source (a piston pump) which draws a measured amount of powder
into a venturi arrangement.
SUMMARY OF TEE INVENTION
[0012] The present invention provides methods and apparatus for
producing an aerosolized dose of a medicament for subsequent
inhalation by a patient. The method comprises first dispersing a
preselected amount of the medicament in a predetermined volume of
gas, usually air. The dispersion may be formed from a liquid, for
example by injecting an air stream through a liquid reservoir of
the drug, or from a dry powder, for example by drawing the powder
into a flowing air stream from a reservoir using a venturi or other
dispersion nozzle. The present invention relies on flowing
substantially the entire aerosolized dose into a chamber which is
initially filled with air and open through a mouthpiece to the
ambient. The aerosolized dose of medicament flows into the chamber
under conditions which result in efficient displacement of the air
with the aerosolized material. By "efficient displacement," it is
meant that at least 40% by weight of the aerosolized material
entering the chamber will remain aerosolized and suspended within
the chamber, thus being available for subsequent inhalation through
the mouthpiece. It is further meant that very little or none of the
aerosolized material will escape from the chamber prior to
inhalation by the patient. Efficient displacement of air and
filling of the chamber can be achieved by proper design of the
chamber, as discussed below.
[0013] After the aerosolized medicament has been transferred to the
chamber, the patient will inhale the entire dose in a single
breath. Usually, the total volume of aerosolized medicament and air
within the chamber will be substantially less than an average
patient's inspiratory capacity, typically being about 100 ml to 750
ml. In this way, the patient can first inhale the entire amount of
drug present in the dose and continue in the same breath to take in
air from the ambient which passes through the chamber and which
helps drive the medicament further down into the alveolar region of
the lungs. Conveniently, the steps of aerosolizing the medicament,
filling the chamber, and inhalation of the chamber contents may be
repeated as many times as necessary to provide a desired total
dosage of the medicament for the patient.
[0014] Apparatus according to the present invention comprise both a
dispersion device for aerosolizing the medicament, either from a
liquid or dry powder formulation of the medicament, and a chamber
having an air inlet and patient mouthpiece for receiving the
aerosolized medicament from the dispersion device. The chamber is
designed and connected to the dispersion device in such a way that
the aerosolized medicament will flow into the chamber and
efficiently displace the internal air volume, as described above.
The volume of the chamber will be at least as large as the maximum
expected volume of aerosolized medicament to be transferred from
the dispersion device. Usually, the chamber volume will be greater
than the aerosol volume in order to reduce losses through the
mouthpiece, with exemplary chamber volumes being in the range from
100 ml to 750 ml, as described above. The volume of aerosolized
medicament will usually be in the range from 50 ml to 750 ml when
the dispersion device is a liquid nebulizer and from 10 ml to 200
ml when the dispersion device is a dry powder disperser, as
described in more detail below. In order to enhance efficient
filling, the chamber will preferably define an internal flow path
so that the entering aerosolized medicament will follow the path
and displace air within the chamber without substantial loss of the
medicament through the mouthpiece. Alternatively, the chamber may
include a baffle which acts to entrap a high velocity aerosol,
particularly those associated with dry powder dispersions.
[0015] In a preferred aspect, the chamber is generally cylindrical
and is connected to the dispersion device by a tangentially
disposed aerosol inlet port located at one end of the cylinder The
mouthpiece is then located at the opposite end of the cylinder, and
aerosolized medicament flowing into the chamber will follow a
generally vortical flow path defined by the internal wall of the
chamber. By also providing an ambient air inlet at the same end of
the cylindrical chamber, the patient can first inhale the
medicament and thereafter breath in substantial amounts of ambient
air, thus sweeping the interior of the chamber to efficiently
remove substantially all aerosolized medicament present and help
drive the medicament further into the patient's lungs.
[0016] In further preferred aspects, the ambient air inlet of the
chamber will be protected, typically through a one-way valve
structure which permits air inflow but blocks aerosol outflow, so
that aerosol will not be lost as it enters the chamber. The chamber
may also comprise vortical baffles, typically in the form of an
axially aligned tube or conical cylinder within the interior of the
chamber, to restrict dispersion of the aerosol within the chamber
and improve delivery efficiency.
[0017] In an alternate preferred aspect, the chamber is generally
cylindrical with an axially oriented aerosol inlet port located at
one end. The mouthpiece is located at the other end of the
cylinder, and an internal baffle is located between the aerosol
inlet and the mouthpiece to prevent direct passage of the aeros 1
to the mouthpiece (which could result in loss of medicament well
before the chamber has been efficiently filled). The internal
baffle is preferably hemispherical in shape with a concave surface
oriented toward the aerosol inlet. Such a construction has been
found particularly useful in initially containing dry powder
dispersions which are often introduced using a high velocity
(frequently sonic) gas stream. The chamber further includes a
tangential ambient air inlet port disposed in the chamber wall
between the aerosol inlet and the internal baffle. By inhaling
through the mouthpiece, the patient is able to establish a vortical
flow of ambient air which will sweep the contained aerosol past the
baffle and through the mouthpiece.
[0018] In yet another aspect of the present invention, the
apparatus for producing aerosolized doses of a medicament comprises
the dispersing device, means for delivering pressurized gas to the
dispersing device, the aerosol chamber, and a controller capable of
selectively controlling the amount of pressurized air delivered to
the dispersing device in order to produce the desired single doses
of medicament and deliver said doses to the chamber. The controller
may include means for timing the actuation of a compressor or means
for controlling the amount of gas released from a pressurized
cylinder, as well as a mechanism for counting and displaying the
number of doses delivered from the chamber during a particular
period of use. Still further, the controller may include a
microprocessor and a keypad for inputting information to the
microprocessor.
[0019] In exemplary devices, the controller may comprise a timer
connected to selectively actuate a valve, such as a solenoid valve,
on a gas cylinder. Alternatively, the timer may turn on and off an
air compressor to regulate the amount of air delivered to the
dispersing device. In portable and hand-held apparatus, the
controller may simply be a release button or mechanism that
actuates a spring or air driven piston to deliver a specific amount
of gas. The controller could also be a metered valve which could
release a fixed amount of liquid propellant to the dispersing
device (in a manner similar to a metered dose inhaler).
[0020] The method and the apparatus of the present invention are
particularly effective for delivering high value drugs, such as
polypeptides and proteins, to a patient with minimal loss of the
drug in the device. Moreover, the method and device provide for a
very accurate measurement and delivery of the doses, while
employing relatively simple and reliable equipment. Further
advantages of the present invention include the ability to vary the
total dosage delivered, either by controlling the number of breaths
taken or by controlling the amount of medicament in each breath.
Still further, the method and device of the present invention
permit the delivery of relatively concentrated doses of the
medicament in order to reduce the amount of time and number of
breaths required for the delivery of a total dosage of the
medicament, particularly when using dry powder medicament
formulations.
BRIEF DESCRIPTION OF THE DRAWINGS
[0021] FIG. 1 is a schematic-diagrammatic view of the
invention;
[0022] FIG. 2 is a diagrammatic cross-sectional view of a holding
chamber;
[0023] FIG. 3 is a diagrammatic view of the holding chamber;
[0024] FIG. 4 is a cross-section along the line 4-4 of FIG. 3;
[0025] FIG. 5 is a cross-section along the line 5-5 of FIG. 3;
[0026] FIG. 6A-6D are diagrammatic views disclosing the stages of
operation; and
[0027] FIG. 7 illustrates a venturi nozzle which may be used for
dispersing dry powder medicament formulations when used in systems
constructed in accordance with the principles of the present
invention;
[0028] FIGS. 8-11 illustrate various exemplary chambers which may
be used in the aerosol delivery systems of the present
invention.
DESCRIPTION OF THE SPECIFIC EMBODIMENTS
[0029] The method and device of the present invention are useful
for delivering a wide variety of medicaments, drugs, biologically
active substances, and the like, to a patient's lung, particularly
for systemic delivery of the medicament or the like. The present
invention is particularly useful for delivering high value
medicaments and drugs, such as proteins and polypeptides, where
efficient delivery and minimum loss are of great concern.
[0030] The apparatus of the present invention will usually comprise
the following basic components: a means for producing a metered
volume of gas, a mixing chamber for generating an aerosol bolus
from either a liquid or a powder, a reservoir that contains the
medicament, and a holding chamber that efficiently captures the
aerosol bolus to maintain the aerosolized particles in suspension
and allow a patient to inhale the aerosol by a slow, deep
inspiration, thereby effectively distributing the aerosolized
medicament to the distal region of the lungs.
[0031] A gas source will usually deliver a preselected volume of
gas at greater than about 15 psig in order to produce a sonic
velocity jet in an aerosol producing region (although sonic
velocity is not always necessary). The pressurized gas is required
to efficiently atomize the liquid or break apart the powder
producing an aerosol having particles that are predominantly 1 to 5
.mu.m in diameter. In addition, the volume of the gas bolus must be
less than a fraction of a patient's inspiratory volume, preferably
between 100 to 750 ml. Suitable gas sources include:
[0032] 1) an air compressor with a timer to control the operating
period of the compressor (where the timer comprises at least a
portion of the controller discussed hereinafter);
[0033] 2) a compressed gas cylinder with a solenoid valve
controlled by a timer;
[0034] 3) a liquid propellant with a metering valve and an
evaporation chamber;
[0035] 4) a spring piston pump; and
[0036] 5) a pneumatic pump.
[0037] The means for producing the aerosol will usually consist of
a constricted orifice that produces a high velocity gas flow to
atomize a liquid or break apart powder agglomerates. The present
invention is designed to be used with a conventional jet nebulizer
that operate with airflow rates in the range from 3 to 13 L/min at
about 15 psig, with the flow rate depending largely on the nozzle
geometry of the nebulizer. The present invention further provides a
means of controlling the volume of air delivered to the nebulizer
in order to produce an aerosol bolus having a specific volume that
can be contained in the aerosol holding chamber. By controlling the
gas source to deliver a specific volume of gas, the system can
employ a variety of nebulizers available from commercial vendors,
such as Marquest, Hudson, Baxter, and Puritan Bennett.
[0038] The present invention can also operate with a powder jet
disperser as a means of generating an aerosol. A pressurized gas
jet produces a highly turbulent gas flow that serves to break apart
powder agglomerates producing an aerosol having single particles of
the preformed powder. An example of a suitable powder/gas mixing
chamber is a simple nozzle with a venturi ejector, as shown in FIG.
7. An advantage of this type of powder mixer is that the gas flow
through the nozzle is only a fraction of the entrained airflow
through the venturi. This reduces the air capacity so that the
required volume of gas for dispersing the powder could be delivered
from a small "pocket-sized" gas source.
[0039] In addition, the powder dispersing apparatus must produce a
pressure pulse having a long enough duration (typically 0.01 to 1
second) to adequately fluidize the powder and efficiently dispense
the powder from the reservoir. A small diameter nozzle, less than
0.020 inch is acceptable and less than 0.015 inch is preferable, in
order to achieve an acceptable duration of the pressure pulse at
peak pressures exceeding 15 psig with a volume of gas that is small
enough to be contained in a small holding chamber.
[0040] Referring now to the drawings wherein like numerals indicate
like parts, the numeral 10 generally indicates an exemplary
apparatus constructed in accordance with the principles of this
invention. The apparatus is powered by an electrical source 12 that
provides energy for a controller, typically in the form of a
microprocessor 18. The present invention, however, does not require
the use of an electrical or digital controller, so long as some
means is provided for supplying preselected gas volumes for aerosol
bolus.
[0041] The microprocessor 18 is a general purpose microcontroller
unit (MCU) such as that sold by Motorola under their Model Number
68HC05. This unit has on-chip peripheral capabilities and the
on-board memory system 30. The on-chip peripheral capability of the
Motorola unit includes multiple input ports, one of which receives
the input data from the keypad 13 via line 16. The microprocessor
18 has a plurality of output ports and its functioning will be more
fully understood as the components of the invention are
described.
[0042] Keypad 13 has six input keys that are important to
performance, namely; 13a, 13b, 13c, 13d, 13e and 13f. The volume or
amount of each aerosolized dose is selected by controlling the
length of time a compressor 22 is turned on by pressing the "puff
size" button 13a. The keypad 12 is programmed so that a first press
of button 13a will display a choice of puff sizes on an LCD 32.
Additional pressings of the button will select the desired size. A
"puff counter actuator" button 13b is pressed which will cause the
LCD 32 display "00". A second press of 13b energizes the air
compressor 22 via output line 38 for a 13a. This produces the first
aerosolized dose or bolus of a medicament for inhalation. The LCD
display 32 will change from 00 to 01 and the LCD will increase by
one upon each additional activation of the compressor. The patient
will continue activating puffs with button 13b until the prescribed
number of puffs have been taken. As these puff events are
occurring, the time and number are stored in memory 30.
[0043] T view a record of previous uses of the device, a dosage
recall button 13c is pressed which causes LCD 32 to display prior
dates, times, puff sizes and number of puff formation events.
Successive pressings of the button 13c will enable scrolling of the
patient's dosage history. Reversal of scroll direction is
accomplished by pressing button 13d and then continuing to scroll
with 13c. The button 13e is a clock/calendar button. Pressing the
button 13e causes the LCD 32 to display the current date and time.
After the device is used and a series of puffs have been taken, the
system will automatically default five minutes after the last puff
to display the actual time and date on the LCD display. Thus, the
device is a clock/calendar when not in actual use and during the
use and date or time can be viewed by pressing 13e.
[0044] Air from compressor 22 is communicated to a mixer 40. The
mixer 40 may be a nebulizer, a dry powder dispenser or other type
of nebulizer known to the prior art. When unit 40 is a dry powder
dispenser, the compressed air from compressor 22 may optionally be
first subjected to coalescing filter 41 and a desiccant filter 41a.
When unit 40 is a nebulizer, a particle filter 21 may optionally be
placed at the intake 23 of the compressor to filter out articles
before the air is compressed. In either case, the medicament or
drug will preferably be in the form of a small particulate, usually
having an aerodynamic size in the range from 1 .mu.m to 5 .mu.m. It
is known that particles in this size range are most efficiently
delivered to the alveolar regions of the lungs.
[0045] An exemplary dry powder venturi nozzle 200 is illustrated in
FIG. 7. The venturi nozzle 200 includes a side port 202 which
receives an initial charge of powder medicament M, typically a
lyophilized protein or polypeptide. The powder is drawn into
dispersion chamber 204 at the point where nozzle orifice 206
introduces a high velocity gas stream in the direction of arrow
208. The high velocity gas stream will result from pressurized gas
or air in plenum 210, which may be provided by a separate air
compressor 22 (FIG. 1) or an air or gas cylinder (not illustrated).
The low pressure caused by the air or gas stream will draw the
powder continuously into the dispersion chamber 204 where
agglomerates of the powder are broken into smaller sizes within the
preferred 1 .mu.m to 5 .mu.m range by the turbulent shear effect in
the chamber.
[0046] In any event, unit 40 is of a type that will nebulize or mix
a defined amount of medicant with the preselected amount of
compressed air received from compressor 22. This defined amount,
referred to as a dosage or bolus, flows into a chamber 42 via the
conduit 39. The chamber 42 is transparent, typically having a
glass, transparent plastic, or similar wall 44.
[0047] A critical aspect of the present invention is the ability to
transfer the aerosolized medicament from the mixer 40 into the
chamber 42 without substantial loss of medicament through the
mouthpiece or within the chamber. Such losses will be minimized so
that at least about 40% by weight of the medicament delivered to
the chamber will remain aerosolized and suspended within the
chamber after the entire volume has been transferred. Preferably,
at least about 55% will remain suspended, more preferable at least
about 70%. Such low losses are desirable since the total amount of
drug which may be introduced into the chamber for each transfer is
maximized, and thus the amount which may be inhaled in each breath
by a patient is increased. Additionally, even small losses of high
valued drugs, such as proteins and polypeptides, can become
significant over time. Still further, the ability to deliver a
concentrated aerosol dispersion of drug into the chamber will
increase the concentration of drug delivered to the patient with
each breath. Such high concentration dosages are preferable since
they can reduce the total number of breaths necessary to deliver a
prescribed amount of drug, thus increasing the total amount of time
required for the treatment.
[0048] Loss of aerosolized medicament can be reduced by minimizing
mixing between the aerosolized medicament and the displaced air as
the chamber is being filled. Minimum mixing between the aerosol
transferred from the mixing chamber 40 and the displaced air within
chamber 42 can be enhanced by properly designing the chamber 42 as
well as the inlet flow geometry of the aerosol into the chamber.
Particularly preferred geometries are illustrated in FIGS. 2-5 and
8-11, as described in more detail hereinbelow.
[0049] A light 50 and/or an audible signal 52 will alert the user
that a puff is ready to be withdrawn from chamber 42 when the
compressor 22 shuts down. At this point in time, the aerosolized
bolus of medicine is quite visible. From the holding chamber 42 the
medicament is inhaled by the patient via a conduit 45 through a
mouthpiece 46 or in the case of small children or infants , a face
mask 48. A one-way check valve 47 is disposed across conduit 45 to
prevent exhalation into chamber 42. The signals 50 and 52 are set
to begin immediately after operation of the compressor 22 ceases.
The cessation of the compressor sound will also alert the patient
that bolus formation is complete. This sequence is repeated for
each bolus and the microprocessor 18 will count and record each
instance of compressor activation so that the prescribed number of
aerosolized boluses have been administered. The number of boluses,
their hour and date and their size (time f compressor use), are
recorded, stored and recallable at a future time f r display on LCD
32 by pressing dosage history button 13c.
[0050] One embodiment of the aerosol holding chamber 42 is best
seen in cross-section in FIG. 2. The chamber 42 is comprised
basically of a top 54, the previously mentioned transparent
sidewall 44 and a bottom 58. The chamber 42 is equipped with an
aerosol intake stub fitting 60 at the lower portion thereof. The
chamber top is equipped with an inhalation stub 62. Also at the
bottom 58 is an atmospheric intake stub 64. The stubs are formed to
accept conventional connector fittings 70, 72 and 74 respectively.
The fittings connect the conduits 45, 96 and 80 to the
stub-fillings 60, 62 and 64. The fittings permit the ready
interchange of chambers having different volumetric capacities.
[0051] Disposed in a conduit 39, between unit 40 and chamber 42, is
a valve 80 that is opened before use of the device and closed
between uses. The valve 80 serves as a vapor lock to prevent
evaporation of fluid from unit 40 when the nebulizer is not in use.
Valve 80 can be controlled by hand like a stop-clock, or it may be
electronically controlled by the MCU 18 so that upon pressing the
puff counter/actuator button 13b, valve 80 opens and then closes by
default if the machine is not used for a set period. Disposed
across inhale line 45 is a one-way check valve 47. A one-way check
valve 94 is also disposed across the air intake conduit 96.
[0052] Particularly preferred chamber geometries are illustrated in
FIGS. 8-11. Chamber 100 in FIG. 8 comprises a cylindrical body 102
with a tangential aerosol inlet port 104. The tangential aerosol
inlet port 104 will be connected to a suitable aerosol dispersing
device, usually either a nebulizer or a dry powder device (as
described above), preferably a nebulizer, and the aerosol will
enter and assume a vortical flow pattern, as indicated by arrows
106. The entry of the aerosol will displace air initially present
in the chamber 100 through mouthpiece 108. Usually, but not
necessarily, the chamber 100 will be oriented vertically with the
mouthpiece at the top. After the entire aerosol bolus has entered
the chamber 100 (typically only partially filling the chamber
leaving a "buffer" of air near the mouthpiece 108), the patient
will inhale through the mouthpiece 108, drawing in ambient air
through ambient air inlet 110, thus sweeping the chamber of the
aerosolized medicament. Ambient air inlet 110 will usually have a
one-way valve, such as a flap or diaphragm valve (not illustrated)
in order to prevent loss of aerosol as the aerosol is introduced
through port 104.
[0053] Chamber 120 in FIG. 9 is similar to chamber 100, except that
an inlet tube 122 extends into the chamber interior, forming a
vortical baffle. Apertures 124 are disposed about the inlet tube
122 to permit entry of air as the patient inhales through
mouthpiece 126. Ambient air inlet 128 is similar to inlet 104 in
FIG. 8.
[0054] A horizontally disposed chamber 140 is illustrated in FIG.
10. Chamber 140 includes both a tangential aerosol inlet 142 and
tangential mouthpiece 144. Thus, aerosolized medicament will enter
through the inlet 142 and move horizontally across the chamber
interior toward the mouthpiece 144. An advantage of this design is
that the aerosol particles will tend to drop below the level of the
mouthpiece 144 as they cross the chamber. Thus, loss of the
medicament through the mouthpiece 144 will be minimized. Ambient
air inlet 146 is provided to permit air infusion as the patient
inhales through the mouthpiece 144.
[0055] A preferred chamber 150 for use with dry powder dispersion
devices, such as venturi nozzle 200 in FIG. 7, is illustrated in
FIG. 1A. The chamber 150 will generally be maintained with its axis
oriented vertically, with an aerosol inlet 152 at its lower end and
a mouthpiece 154 at its upper end. The chamber 150 further includes
an internal baffle 156 which is suspended from a rod 158 attached
to the upper end of the chamber. The baffle 156 is preferably
hemispherical, with its open or concave end oriented downwardly
toward aerosol inlet 152. The purpose of the baffle 156 is to
contain the initial plume of aerosol created by the high velocity
air or gas stream. The hemispherical design is preferred since it
will redirect the initial flow of aerosol back downward, creating a
recirculation as indicated by the arrows in FIG. 11B. Other
geometries for the baffle, including flat plates, perforated
plates, cylinders, cones, and the like, might also find use, with
the primary requirement being that the baffle design be able to
provide an initial containment zone within the chamber.
[0056] After an aerosolized dose or bolus of medicament has been
introduced to the chamber 150, the patient will inhale through the
mouthpiece 154, drawing ambient air in through ambient air inlet
158. The inlet 158 includes a one-way flap or diaphragm valve 160
which permits the inflow of air but prevents the initial loss of
medicament as the aerosolized dose enters through the inlet 152.
The ambient air inlet 158 is disposed tangentially on the chamber
150, and entry of ambient air through the inlet cause a vortical
(as illustrated in FIG. 11C) which will cause the suspended
medicament particles to move radically outward (due to the induced
cyclone effect) and be carried upward by the airflow through the
annular region 162 between the periphery of the baffle 156 and the
interior wall of the chamber 150.
[0057] Surprisingly, the design of chamber 150 has been found to be
able to receive a volume of aerosolized medicament greater than the
chamber volume without substantial loss of medicament through the
mouthpiece. It is believe that the baffle 156 can act as a
"concentrator," which contains the medicament particles in the
region below the baffle while permitting air flow through the
annular region 162. Such concentration is achieved while still
maintaining the aerosolized particles in suspension and with the
ability to subsequently transfer the medicament particles to the
mouthpiece by introducing a vortical flow of ambient air through
inlet 158, as described above.
[0058] In operation, the patient or medical attendant will ready
the device by operating the puff size button 13a. Button 13b is
pressed a second time to energize compressor 22 and a pre-selected
amount of air under a constant pressure is delivered to unit 40 for
mixing or nebulizing to form the first puff. The medicament begins
filling the chamber 42 from the bottom (FIG. 6A) through valve 80
and stub fitting 60 and a cloudy, observable "puff" is formed as
seen in FIG. 6B. During this time interval, valve 94 is closed.
[0059] After the vessel or chamber 42 is filled, the signals 50 and
52 are activated for several seconds by the timer function of the
microprocessor 18. The duration of both signals will be preset in
the control program 24. As a breath is taken, valves 47 and 94 will
open to permit the puff to enter the lungs and to permit additional
atmospheric air to enter the chamber from the bottom through
conduit 96.
[0060] The volumetric size of chamber 42 is only a fraction of the
capacity of the patients' lungs usually being from 200 ml to 1000
ml, typically being about 500 ml. Inhalation by the patient will
thus initially draw the entire dose of medicament into the lungs.
The volume of aerosol transferred to the chamber will typically be
about 10 ml to 750 ml, and the air that enters through valve 94 can
thus act as an air piston to drive the smaller volume of aerosol
deep into the user's lungs. The bottom to top filling and vertical
flow pattern result in a minimum of dispersion and dilution of the
aerosol. Moreover, the sweeping of chamber 50 with air after each
inhalation helps assure substantially complete delivery of the drug
to the patient.
[0061] The atmospheric or pure air and the medicament bolus, each
moves from the chamber 42 through the one-way check valve 47 into
the patient's mouth via the conduit 45. A mask 48 with a one-way
exhalation port is used for patients that require same. A one-way
valve 47 may be used to prevent the patient from accidentally
exhaling into the chamber 42.
[0062] FIG. 6A-6D show illustrations of the sequence of bolus
generation and withdrawal from the aerosol holding chamber 42.
[0063] The following examples are offered by way of illustration,
not by way of limitation.
[0064] Experimental Equipment
[0065] Air supply--a nitrogen cylinder with a regulator, a needle
valve, a pressure gauge, and a solenoid valve that is operated with
a timer with a resolution of 0.01 second.
[0066] Jet Nebulizer--Rapid-Flo.TM., (Allersearch, Vt. Victoria,
Australia)
[0067] Powder Disperser--A venturi (as illustrated in FIG. 7)
having a 0.013 inch diameter jet nozzle.
[0068] Aerosol Holding Chambers--Fabricated from plastic with
internal volumes of 750 ml. Design 1--3-inch cylindrical chamber
with spherical top and bottom and one 90.degree.-port at the base,
one 45.degree.-port at the top and one tangential port on the side
(as illustrated in FIG. 8). Design 2--3-inch cylindrical chamber
with spherical top and bottom and a 1 inch cylindrical spacer
located axially along the center of the chamber. Three ports--one
90.degree.-port at the base, one 45.degree.-port at the top and one
tangential port on the side (as illustrated in FIG. 9). Design
3--3-inch cylindrical chamber with spherical top and bottom; a 21/2
inch hemispherical baffle held in the center of the chamber with a
rod. The baffle was located approximately 2inches above the base of
the chamber. Three ports--aerosol intake: 90.degree.-port at the
base, mouthpiece: 45.degree.-port at the top and makeup air intake:
tangential port on the side (as illustrated in FIG. 11). Design
4--3-inch cylindrical chamber with spherical top and bottom; a 21/2
inch hemispherical baffle located 23/4 inches above the base on a c
ne (as illustrated in FIG. 11).
[0069] Methods
[0070] The four aerosol chamber designs were tested using either
the jet nebulizer or the powder dispenser. Design 1 was tested
using either the 90.degree.-port at the base for the aerosol intake
or the tangential port as the aerosol intake.
[0071] The total airflow through the apparatus, the aerosol
generator and the holding chamber, was measured with a rotameter
connected to the mouthpiece of the holding chamber. The flow was
set to the desired rate with the needle valve. The pressure was
maintained above 15 psig to ensure sonic velocity in the nozzle of
the aerosol generator.
[0072] Once the airflow was set, the sample was loaded into the
aerosol generator. The operating period was set on the timer. A
toggle switch on the timer opened the solenoid valve sending air
through the aerosol generator and producing the aerosol. We
observed the distribution of the aerosol in the holding chamber and
could observe when the aerosol began to flow out of the chamber.
The maximum length of time that the aerosol generator could be
operated and still capture all of the aerosol in the holding
chamber was determined by adjusting the operating period on the
timer and repeating the steps listed above. The aerosol dose volume
was calculated from the flow rate and the time the solenoid was
open. A vacuum line was connected to the holding chamber following
an actuation to clear the chamber of the aerosol before actuating
again.
[0073] A 0.9% saline solution was used in testing the different
holding chamber configurations with a Rapid-Flow nebulizer. The
nebulizer was operated at flow rate of 19 L/min which resulted in
24 psig across the jet of the nebulizer.
[0074] The powder disperser was tested at a pressure of 30 psig
which resulted in a flow rate of 10.4 L/min through the apparatus.
Approximately 5 mg of a test powder, prepared by spray drying a
solution of mannitol and bovine serum albumin, was loaded into the
venturi intake and the solenoid valve was actuated. We checked for
powder remaining in the venturi intake to determine whether there
was an adequate air supply to disperse the powder. The particle
size distribution measured from the chamber using an Aerosizer
(API, Hadley, Mass.) particle size analyzer showed that the aerosol
contained particles between 1 and 4 .mu.m in diameter.
[0075] Results
[0076] Results comparing the different chamber designs for
containing the aerosol are reported in Table 1. The maximum volume
of the aerosol contained by the chamber was calculated from the
maximum operating time and the total airflow. The proportion of the
aerosol volume to the volume of the chamber given in the % Chamber
Volume column is a way of comparing the effectiveness of the
different chamber designs for containing the aerosol. The air
volume needed to disperse 5 mg of powder could be efficiently
captured in all of the chamber configurations tested. The designs
that induced a vertical airflow pattern in the chamber retained a
larger volume of aerosol.
1TABLE 2 Aerosol Capture Efficiency for several Holding Chamber
Designs Nebulizer Powder Disperser % of Increase % of Increase
Cham- Aerosol Chamber over Aerosol Chamber over ber Volume Volume
base Volume Volume base De- 348 mL 45.8% -- 69. mL 9.24% -- sign 1
bottom fill De- 665 mL 86.7% 1.94 95.3 mL 12.7% 1.38 sign 1 tangen-
tial fill De- 728 mL 97.1% 2.12 104 mL 13.9% 2.50 sign 2 center
baffle De- 950 mL 127% 2.77 164 mL 21.9% 2.37 sign 3 hemi- sphere
baffle De- 855 mL 114% 2.49 161 mL 21.5% 2.33 sign 4
Conclusions
[0077] An aerosol holding chamber can be designed that efficiently
captures a measured volume of aeros 1. A chamber designed to induce
vortical airflow pattern in the chamber by a tangential aerosol
intake or using baffles distributes the aerosol more evenly in the
chamber without loss from the mouthpiece. For use with a nebulizer,
a vortical airflow produces a higher concentration of medicament in
the chamber so that an effective dose could be taken with fewer
puffs. The results with the powder disperser show that the vortical
flow and properly designed baffles are effective in containing a
powder aerosol produced by a turbulent jet.
[0078] It should be understood that the preferred embodiments of
the present invention have been disclosed by way of example and
that other modifications may occur to those skilled in the art
without departing from the scope and spirit of the appended
claims.
* * * * *