U.S. patent application number 14/166882 was filed with the patent office on 2014-07-24 for pulsed nebulizer.
This patent application is currently assigned to PNEUMOFLEX SYSTEMS, LLC. The applicant listed for this patent is PNEUMOFLEX SYSTEMS, LLC. Invention is credited to W. Robert ADDINGTON, Stuart P. Miller.
Application Number | 20140207016 14/166882 |
Document ID | / |
Family ID | 51356358 |
Filed Date | 2014-07-24 |
United States Patent
Application |
20140207016 |
Kind Code |
A1 |
ADDINGTON; W. Robert ; et
al. |
July 24, 2014 |
PULSED NEBULIZER
Abstract
A nebulizer includes a nebulizer body having an air channel
section, medication reservoir and nebulizer outlet. An air line has
an inlet at one end and extends through the air channel section and
has a venturi nozzle oriented horizontally when in use and an
outlet and configured to form a low pressure mixing chamber. The
air line provides a pulsed flow of gas between the inlet and outlet
end. The venturi nozzle and medication reservoir are received
within an oral cavity of a patient when in use. A primary suction
line extends from the medication reservoir to the low pressure
mixing chamber through which medication is drawn upward and mixed
with gas passing through the venturi nozzle and nebulized for
pulsed discharge through the nebulizer outlet during
nebulization.
Inventors: |
ADDINGTON; W. Robert;
(Melbourne Beach, FL) ; Miller; Stuart P.;
(Indialantic, FL) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
PNEUMOFLEX SYSTEMS, LLC |
Melbourne |
FL |
US |
|
|
Assignee: |
PNEUMOFLEX SYSTEMS, LLC
Melbourne
FL
|
Family ID: |
51356358 |
Appl. No.: |
14/166882 |
Filed: |
January 29, 2014 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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13799196 |
Mar 13, 2013 |
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14166882 |
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13353611 |
Jan 19, 2012 |
8671934 |
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13799196 |
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61434613 |
Jan 20, 2011 |
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Current U.S.
Class: |
600/538 ;
128/200.21 |
Current CPC
Class: |
A61M 2205/8225 20130101;
A61M 16/201 20140204; A61J 17/001 20150501; A61M 2205/13 20130101;
A61M 15/0036 20140204; A61M 16/202 20140204; A61B 5/097 20130101;
A61B 5/087 20130101; A61M 2205/3592 20130101; A61J 7/0053 20130101;
A61B 5/7282 20130101; A61M 2016/0039 20130101; A61M 2205/3569
20130101; A61M 15/0021 20140204; A61M 16/14 20130101; A61B 5/0823
20130101; A61M 11/06 20130101; A61M 15/0091 20130101; A61M 2206/14
20130101; A61M 2016/0027 20130101; A61M 15/0086 20130101; A61M
2205/502 20130101; A61B 5/4839 20130101 |
Class at
Publication: |
600/538 ;
128/200.21 |
International
Class: |
A61M 16/14 20060101
A61M016/14; A61B 5/08 20060101 A61B005/08; A61M 16/00 20060101
A61M016/00; A61B 5/00 20060101 A61B005/00; A61M 11/06 20060101
A61M011/06; A61J 17/00 20060101 A61J017/00; A61B 5/087 20060101
A61B005/087; A61B 5/097 20060101 A61B005/097 |
Claims
1. A nebulizer, comprising: a nebulizer body comprising an air
channel section, medication reservoir and nebulizer outlet; an air
line having an inlet at one end and extending through the air
channel section and having a venturi nozzle oriented horizontally
when in use and an outlet end configured to form a low pressure
mixing chamber, wherein the airline provides a pulsed flow of gas
between the input and outlet end, and the venturi nozzle and
medication reservoir are received within an oral cavity of a
patient when in use; and a primary suction line extending from the
medication reservoir to the low pressure mixing chamber through
which medication is drawn upward and mixed with gas passing through
the venturi nozzle and nebulized for pulsed discharge through the
nebulizer outlet during nebulization.
2. The nebulizer according to claim 1, wherein a pulse duration for
each pulse of the flow of gas is from about 0.5 to 2.0 seconds
during nebulization.
3. The nebulizer according to claim 1, wherein the flow of gas is
actuated as a pulse from about 10 to 20 times during
nebulization.
4. The nebulizer according to claim 1, and further comprising a
diffuser upon which the nebulized medication and air exiting the
venturi nozzle and low pressure mixing chamber impacts to aid
nebulization.
5. The nebulizer according to claim 4, and further comprising a
rainfall chamber into which the venturi nozzle and low pressure
mixing chamber are positioned.
6. The nebulizer according to claim 5, and further comprising a
secondary suction line within the rainfall chamber that draws
nebulized medication that drops down before discharge through the
nebulizer outlet.
7. The nebulizer according to claim 1, and further comprising an
air flow sensor positioned within the air channel section and
configured to generate signals indicative of air flow generated by
a patient's involuntary reflex cough event occurring at
nebulization.
8. The nebulizer according to claim 1, and further comprising a
processor interfaced with the air flow sensor and configured to
evaluate the involuntary reflex cough event.
9. The nebulizer according to claim 1, wherein the venturi nozzle,
primary suction line, low pressure mixing chamber and air channel
section are connected together and dimensioned such that at
standard temperature and pressure (STP), a differential pressure
results in no medication being drawn upward through the primary
suction line for nebulization and discharge through the nebulizer
outlet until a predetermined negative inspiratory pressure is
created from inhalation by a user, and upon user inhalation that
creates the negative inspiratory pressure, air flow begins through
the venturi nozzle and medication is drawn upward through the
primary suction line and nebulizes the air flowing through the
venturi nozzle to be discharged through the nebulizer outlet.
10. The nebulizer according to claim 9, wherein nebulization begins
at a negative inspiratory pressure of from about -3 cmH.sub.2O to
about -52 cmH.sub.2O.
11. A nebulizer, comprising: a nebulizer body comprising an air
channel section, medication reservoir and nebulizer outlet; an air
line having an inlet at one end and extending through the air
channel section and having a venturi nozzle oriented horizontally
when in use and an outlet end configured to form a low pressure
mixing chamber; a canister port located at the inlet end of the air
line that receives a gas canister and a valve positioned at the
canister port and actuable to provide a pulsed flow of gas from the
canister into the air line between the input and outlet end,
wherein the venturi nozzle and medication reservoir are received
within an oral cavity of a patient when in use; and a primary
suction line extending from the medication reservoir to the low
pressure mixing chamber through which medication is drawn upward
and mixed with air passing through the venturi nozzle and nebulized
for pulsed discharge through the nebulizer outlet during
nebulization.
12. The nebulizer according to claim 11, wherein a pulse duration
for each pulse of the flow of air is from about 0.5 to 2.0 seconds
during nebulization.
13. The nebulizer according to claim 11, wherein the flow of air is
actuated as a pulse from about 10 to 20 times during
nebulization.
14. The nebulizer according to claim 11, and further comprising a
diffuser upon which the nebulized medication and air exiting the
venturi nozzle and low pressure mixing chamber impacts to aid
nebulization.
15. The nebulizer according to claim 14, and further comprising a
rainfall chamber into which the venturi nozzle and low pressure
mixing chamber are positioned.
16. The nebulizer according to claim 15, and further comprising a
secondary suction line within the rainfall chamber that draws
nebulized medication that drops down before discharge through the
nebulizer outlet.
17. The nebulizer according to claim 11, and further comprising an
air flow sensor positioned within the air channel section and
configured to generate signals indicative of air flow generated by
a patient's involuntary reflex cough event occurring at
nebulization.
18. The nebulizer according to claim 17, and further comprising a
processor interfaced with the air flow sensor and configured to
evaluate the involuntary reflex cough event.
19. The nebulizer according to claim 11, wherein the venturi
nozzle, primary suction line, low pressure mixing chamber and air
channel section are connected together and dimensioned such that at
standard temperature and pressure (STP), a differential pressure
results in no medication being drawn upward through the primary
suction line for nebulization and discharge through the nebulizer
outlet until a predetermined negative inspiratory pressure is
created from inhalation by a user, and upon user inhalation that
creates the negative inspiratory pressure, air flow begins through
the venturi nozzle and medication is drawn upward through the
primary suction line and nebulizes the air flowing through the
venturi nozzle to be discharged through the nebulizer outlet.
20. The nebulizer according to claim 19, wherein nebulization
begins at a negative inspiratory pressure of from about -3
cmH.sub.2O to about -52 cmH.sub.2O.
21. A nebulizer, comprising: a nebulizer body comprising an air
channel section, medication reservoir and nebulizer outlet; an air
line having an inlet at one end that receives a flow of gas and
extending through the air channel section and having a venturi
nozzle oriented horizontally when in use and an outlet end
configured to form a low pressure mixing chamber; a valve
positioned at the inlet of the air line and actuable based on a
predetermined sensed SNIP (Sniff Nasal Inspiratory Pressure) to
provide a pulsed flow of gas into the air line between the input
and outlet end, wherein the venturi nozzle and medication reservoir
are received within an oral cavity of a patient when in use; and a
primary suction line extending from the medication reservoir to the
low pressure mixing chamber through which medication is drawn
upward and mixed with air passing through the venturi nozzle and
nebulized for pulsed discharge through the nebulizer outlet during
nebulization.
22. The nebulizer according to claim 21, further comprising a
nebulizer suction member enclosing the body and formed as an infant
pacifier.
23. The nebulizer according to claim 21, wherein a pulse duration
for each pulse of the flow of gas is from about 0.5 to 2.0 seconds
during nebulization.
24. The nebulizer according to claim 21, wherein the flow of gas is
actuated as a pulse from about 10 to 20 times during
nebulization.
25. The nebulizer according to claim 21, and further comprising a
diffuser upon which the nebulized medication and air exiting the
venturi nozzle and low pressure mixing chamber impacts to aid
nebulization.
26. The nebulizer according to claim 25, and further comprising a
rainfall chamber into which the venturi nozzle and low pressure
mixing chamber are positioned.
27. The nebulizer according to claim 26, and further comprising a
secondary suction line within the rainfall chamber that draws
nebulized medication that drops down before discharge through the
nebulizer outlet.
28. The nebulizer according to claim 21, and further comprising an
air flow sensor positioned within the air channel section and
configured to generate signals indicative of air flow generated by
a patient's involuntary reflex cough event occurring at
nebulization.
29. The nebulizer according to claim 28, and further comprising a
processor interfaced with the air flow sensor and configured to
evaluate the involuntary reflex cough event.
Description
PRIORITY APPLICATION(S)
[0001] This application is a continuation-in-part application of
application Ser. No. 13/799,196 filed Mar. 13, 2013, which is a
continuation-in-part application of Ser. No. 13/353,611 filed Jan.
19, 2012, which claims priority to U.S. provisional application
Ser. No. 61/434,613 filed Jan. 20, 2011, the disclosures which are
hereby incorporated herein by reference in their entirety.
FIELD OF THE INVENTION
[0002] The present invention relates to the field of nebulizers,
and more particularly, this invention relates to nebulizers having
a venturi.
BACKGROUND OF THE INVENTION
[0003] Inhalation is a very old method of drug delivery. In the
twentieth century it became a mainstay of respiratory care and was
known as aerosol therapy. Use of inhaled epinephrine for relief of
asthma was reported as early as 1929, in England. Dry powder
inhalers have been used to administer penicillin dust to treat
respiratory infections. In 1956, the first metered dosed inhaler
was approved for clinical use.
[0004] The scientific basis for aerosol therapy developed
relatively late, following the 1974 Sugar Loaf conference on the
scientific basis of respiratory therapy. A more complete history of
the development of aerosol therapy and the modern nebulizer is
described in the 2004 Phillip Kitridge Memorial Lecture entitled,
"The Inhalation of Drugs: Advantages and Problems by Joseph L. Row;
printed in the March 2005 issue of Respiratory Care, vol. 50, no.
3.
[0005] Table 8 of the Respiratory Care article, referred to above,
page 381, lists the characteristics of an ideal aerosol inhaler as
follows:
TABLE-US-00001 TABLE 8 Dose reliability and reproducibility High
lung-deposition efficiency (target lung deposition of 100% of
nominal dose) Production of the fine particles .ltoreq.5 .mu.m
diameter, with correspondingly low mass median diameter Simple to
use and handle Short treatment time Small size and easy to carry
Multiple-dose capability Resistance to bacterial contamination
Durable Cost-effective No drug released to ambient-air Efficient
(small particle size, high lung deposition) for the specific drug
being aerosolized Liked by patients and health care personnel
[0006] Standard nebulizers typically fail to achieve a number of
these characteristics because they waste medication during
exhalation. Further, the particle size is often too large to reach
the bottom of the lungs where the medication may be most needed.
There is difficulty in estimating the dose of the drug being given
to a patient and there is difficulty in reproducing that dose.
There is a possibility of contamination when opening the initially
sterile kit, pouring medication into the cup, and assembling the
pieces for use by a patient. There is also considerable
inefficiency in the medication delivery, with much of it being
deposited in the throat, rather than in the lungs.
[0007] Commonly assigned U.S. Pat. No. 8,109,266, the disclosure
which is hereby incorporated by reference in its entirety,
discloses a nebulizer having a flow meter function that is applied
to venturi type intra-oral nebulizers as disclosed in commonly
assigned U.S. Pat. Nos. 7,712,466 and 7,726,306, the disclosures
which are hereby incorporated by reference in their entirety. These
nebulizers are horizontally configured, and in one example, include
a venturi at a rainfall chamber. Further enhancements to the
nebulizers are desirable.
SUMMARY OF THE INVENTION
[0008] In accordance with a non-limiting example, a nebulizer
includes a nebulizer body having an air channel section, medication
reservoir and nebulizer outlet. An air line has an inlet at one end
and extends through the air channel section and has a venturi
nozzle oriented horizontally when in use and an outlet and
configured to form a low pressure mixing chamber. The air line
provides a pulsed flow of gas between the inlet and outlet end, and
the venturi nozzle and medication reservoir are received within an
oral cavity of a patient when in use. A primary suction line
extends from the medication reservoir to the low pressure mixing
chamber through which medication is drawn upward and mixed with gas
passing through the venturi nozzle and nebulized for pulsed
discharge through the nebulizer outlet during nebulization.
[0009] In one example, the nebulizer has a pulse duration for each
pulse of the flow of gas from about 0.5 to 2.0 seconds during
nebulization. The flow of gas is actuated as a pulse from about 10
to 20 times during nebulization. The nebulizer includes a diffuser
in another example upon which the nebulized medication and air
exiting the venturi nozzle and low pressure mixing chamber impact
to aid nebulization. The nebulizer includes a rainfall chamber into
which the venturi nozzle and low pressure mixing chamber are
positioned. A secondary suction line is included within the
rainfall chamber and draws nebulized medication upward that drops
down before discharge through the nebulizer outlet.
[0010] In yet another example, an air flow sensor is positioned
within the air channel section and configured to generate signals
indicative of air flow generated by a patient's involuntary reflex
cough event occurring at nebulization. A processor is interfaced
with the air flow sensor and configured to evaluate the involuntary
reflex cough event.
[0011] In another example, the venturi nozzle, primary suction
line, low pressure mixing chamber, and air channel section are
connected together and dimensioned such that at standard
temperature and pressure (STP), a differential pressure results in
no medication being drawn upward through the primary suction line
for nebulization and discharge through the nebulizer outlet until a
predetermined negative inspiratory pressure is created from
inhalation by a user. Upon user inhalation that creates the
negative inspiratory pressure, air flow begins through the venturi
nozzle and medication is drawn upward through the primary suction
line and nebulizes the air flow through the venturi nozzle to be
discharged through the nebulizer outlet. In an example, the
nebulization begins at a negative inspiratory pressure from about
-3 cmH.sub.2O to about -52 cmH.sub.2O.
[0012] In another example, a canister port is located at the inlet
end of the air line that receives a gas canister and a valve is
positioned at the canister port and actuable to provide a pulsed
flow of gas from the canister into the air line between the input
and outlet end. In yet another example, a valve is positioned at
the inlet of the air line and actuable based on a predetermined
sensed SNIP (Sniff Nasal Inspiratory Pressure) to provide a pulsed
flow of gas into the air line between the input and outlet. A
nebulizer suction member encloses the body and is formed as an
infant pacifier in yet another example.
BRIEF DESCRIPTION OF THE DRAWINGS
[0013] Other objects, features and advantages of the present
invention will become apparent from the detailed description of the
invention which follows, when considered in light of the
accompanying drawings in which:
[0014] FIG. 1 is cross-sectional view of a nebulizer in accordance
with a non-limiting example that is activated by negative
inspiratory pressure and can be configured as a pediatric nebulizer
in one non-limiting example and include in one embodiment a flow
meter function.
[0015] FIGS. 2-3 are sectional views of the nebulizer shown in FIG.
1 and showing a flow diagram of the airflow at 2 L/min at standard
temperature and pressure (STP).
[0016] FIGS. 4-5 are flow diagrams showing the airflow through the
nebulizer of FIG. 1 at 2 L/min at -3 cmH.sub.2O.
[0017] FIGS. 6-7 are flow diagrams showing the airflow through the
nebulizer of FIG. 1 with 2 L/min at -15 cmH.sub.2O.
[0018] FIGS. 8-9 are flow diagrams showing the airflow through the
nebulizer of FIG. 1 with 2 L/min at -52 cmH.sub.2O.
[0019] FIG. 10 is a diagram showing the pressure gradient in the
nebulizer of FIG. 1 at standard temperature and pressure.
[0020] FIG. 11 is a diagram of the nebulizer of FIG. 1 showing the
pressure gradient at -3 cmH.sub.2O.
[0021] FIG. 12 is a sectional view of the nebulizer of FIG. 1
showing the pressure gradient at -15 cmH.sub.2O.
[0022] FIG. 13 is a sectional view of the nebulizer of FIG. 1
showing the pressure gradient at -52 cmH.sub.2O.
[0023] FIG. 14 is a sectional view of the nebulizer of FIG. 1
showing the medication flow upward at 2 L/min -3 cmH.sub.2O.
[0024] FIG. 15 is a sectional view of the nebulizer of FIG. 1
showing the medication flow upward at 2 L/min -15 cmH.sub.2O.
[0025] FIG. 16 is a sectional view of the nebulizer of FIG. 1
showing the medication flow upward at 2 L/min -52 cmH.sub.2O.
[0026] FIG. 17 is a table showing respiratory pressures for the
measured and predicted MIP and MEP for males and females.
[0027] FIG. 18 is a general environmental view of a child sucking
on a pediatric nebulizer such as disclosed in FIGS. 19-22 in
accordance with non-limiting examples.
[0028] FIG. 19 is a general environmental view of a pediatric
nebulizer used by the infant shown in FIG. 18 in accordance with
non-limiting examples.
[0029] FIG. 20 is a side sectional view in isometric of the
pediatric nebulizer shown in FIG. 19 that engages the patient's
mouth.
[0030] FIG. 20A is a more detailed view of the pediatric nebulizer
body with the rainfall chamber, which includes an airflow sensor in
accordance with non-limiting examples.
[0031] FIG. 21 is another side sectional view of a pediatric
nebulizer in accordance with non-limiting examples.
[0032] FIG. 22 is another side sectional view of a different
embodiment of a pediatric nebulizer in accordance with the
non-limiting example.
[0033] FIG. 23 is a sectional view of another embodiment of the
nebulizer in accordance with a non-limiting example and showing an
airflow sensor such as a spinning fan wheel and associated with the
main body, and a wireless module that includes a processor and
transceiver that can receive measured airflow and wirelessly
transmit data containing measured airflow to a separate device such
as a handheld processing device in accordance with the non-limiting
example.
[0034] FIG. 24 is a plan view of the nebulizer of FIG. 23 and
showing an air flow sensor mounted within the air channel section
of that nebulizer.
[0035] FIG. 25 is a cross-section view of another nebulizer
configuration that provides air curtains and showing an air flow
sensor mounted at the mixing end of the nebulizer in accordance
with the non-limiting example.
[0036] FIG. 26 is a fragmentary plan view of a handheld processing
device that can be used in conjunction with the nebulizers having
the airflow sensors and which can be configured to wirelessly
receive data containing air flow measurements, such as for
measuring and processing data regarding the involuntary cough
event.
[0037] FIG. 27 is a block diagram showing example components of a
hand held processing device such as shown in FIG. 26, which can
receive data from a nebulizer containing air flow measurements.
[0038] FIG. 28 is a side elevation view of the nebulizer shown in
FIGS. 1-16.
[0039] FIG. 29 is an end elevation view of the nebulizer shown in
FIG. 28.
[0040] FIG. 30 is a plan view of the nebulizer shown in FIG.
28.
[0041] FIG. 31 is a phantom diagram showing internal components of
a portion of the nebulizer body that includes the air channel
section, air line and vent in accordance with a non-limiting
example.
[0042] FIG. 32 is a perspective view in partial cut-away of the
nebulizer body showing components of the nebulizer body.
[0043] FIG. 33 is a top plan view of a portion of the nebulizer
body shown in FIG. 32 and showing details of the vent in accordance
with a non-limiting example.
[0044] FIG. 34 is another top plan view of the vent of FIG. 33.
[0045] FIG. 35 is a partial, sectional view of the nebulizer of
FIG. 28 in accordance with a non-limiting example.
[0046] FIG. 36A is an anatomical, sectional view of a patient's
oral and nasal passages and showing the positioning in the oral
cavity of an intra-oral nebulizer in accordance with a non-limiting
example and showing the nebulized medication generated in the mouth
and passing into the air passageway.
[0047] FIG. 36B is another anatomical, sectional view similar to
that of FIG. 36A and showing the positioning in the oral cavity of
a standard jet nebulizer and showing the nebulized medication
generated in the mouth and passing into the air passageway and
requiring an increased flow rate as compared to the nebulizer
example of FIG. 36A.
[0048] FIG. 37 is a graph related to secondary droplet formation in
the nebulizer as described relative to FIGS. 1-16 and showing a
critical diameter for splashing to occur on the baffle or impactor
of the nebulizer in accordance with a non-limiting example.
[0049] FIG. 38 shows a nebulizer testing set-up used to test the
nebulizer in accordance with a non-limiting example for particle
size distribution and determine a change in nebulizer MMAD (Mass
Median Aerodynamic Diameter) during nebulization.
[0050] FIG. 39 is a graph showing a particle size distribution by
mass for different flow rates of the nebulizer such as described in
the test of FIG. 38 in accordance with a non-limiting example.
[0051] FIG. 40 is another graph showing particle size distribution
by mass for the nebulizer similar as described in the test of FIG.
38 in accordance with a non-limiting example, but a smaller
diameter feed orifice as compared to the nebulizer example of FIG.
39.
[0052] FIG. 41 is a graph showing the change in nebulizer MMAD
during nebulization as described in the test of FIG. 3B.
[0053] FIG. 42 shows a nebulizer testing set-up for evaluating the
nebulizer in accordance with a non-limiting example under pulsed
conditions.
[0054] FIG. 43 is a graph showing the average peak particle size
distribution for different trials under different pulsed conditions
as described in the test of FIG. 42 in accordance with a
non-limiting example.
[0055] FIG. 44 is a graph showing the average peak particle size
distribution with the mass concentration and average for each pulse
pressure as described in the test of FIG. 42 in accordance with a
non-limiting example.
[0056] FIG. 45A is a bar chart showing the amount of delivered drug
as albuterol sulfate per actuation as described in the test of FIG.
42 in accordance with a non-limiting example.
[0057] FIG. 45B is a chart showing the total delivered drug results
from the pulsed air trials using the test set-up shown in FIG.
42.
[0058] FIG. 46 is a side elevation view of a nebulizer similar to
that shown in FIG. 28, but including a gas canister connected to a
valve to provide either a pulsed or continuous air flow through the
nebulizer that may be actuated by a negative inspiratory
pressure.
[0059] FIG. 47 is a perspective view of a metered dose nebulizer in
accordance with a non-limiting example.
[0060] FIG. 48 is a side elevation view of the metered dose
nebulizer shown in FIG. 47 in accordance with a non-limiting
example.
[0061] FIG. 49 is a front elevation view of the metered dose
nebulizer shown in FIG. 47 in accordance with a non-limiting
example.
[0062] FIG. 50 is a sectional view taken along line 50-50 of FIG.
49 of the metered dose nebulizer in accordance with a non-limiting
example.
[0063] FIG. 51 is an exploded perspective view of the metered dose
nebulizer shown in FIG. 47 in accordance with a non-limiting
example.
[0064] FIG. 52 is an enlarged isometric, partial sectional view of
the nebulizer outlet for the nebulizer shown in FIGS. 47-51 and
showing the venturi nozzle and suction line formed together and
replaceable within the nebulizer body as one unit.
[0065] FIG. 53 is an enlarged perspective view of a portion of the
underside of the nebulizer body at its nebulizer outlet and showing
the medication container that can be inserted within the medication
receiver and connected into the suction line.
[0066] FIG. 54 is a sectional view of a metered dose atomizer
similar to the nebulizer sectional view shown in FIG. 50, but
modified to form a metered dose atomizer in accordance with a
non-limiting example.
[0067] FIG. 55 is another general environmental view of a child
sucking on a pediatric nebulizer such as the nebulizer shown in
FIG. 18 and disclosed in FIGS. 19-22 and modified in accordance
with non-limiting examples and showing a sensor for SNIP (Sniff
Nasal Inspiratory Pressure) that can be used to actuate operation
of the pediatric nebulizer.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0068] Different embodiments will now be described more fully
hereinafter with reference to the accompanying drawings, in which
preferred embodiments are shown. Many different forms can be set
forth and described embodiments should not be construed as limited
to the embodiments set forth herein. Rather, these embodiments are
provided so that this disclosure will be thorough and complete, and
will fully convey the scope to those skilled in the art.
[0069] In accordance with a non-limiting example as shown in the
examples of FIGS. 1-16 and 28-35, and disclosed in the incorporated
by reference Ser. No. 13/799,196 and now allowed Ser. No.
13/353,611 applications, the nebulizer uses a vent that is formed
in the nebulizer body and communicates with the air channel section
and medication reservoir to vent the air channel section and
medication reservoir to outside ambient air. A primary suction line
extends from the medication reservoir to the low pressure mixing
chamber through which medication is drawn upward and mixed with air
passing through the venturi nozzle and nebulized for discharge
through the nebulizer outlet. This vent is configured to vent the
air channel section and medication reservoir to atmospheric
pressure such that at standard temperature and pressure (STP), a
differential pressure results between the venturi nozzle and
medication reservoir such that no medication is drawn upward
through the primary suction line for nebulization and discharge
through the nebulizer outlet into a negative inspiratory pressure
is created from inhalation by a user. The air line extends through
the air channel section and includes the venturi nozzle and is
configured at its end to form the low pressure mixing chamber. Air
is continually pressurized in the air line from an air source, but
at a low pressure that works in conjunction with the vent such that
at standard temperature and pressure (STP), the differential
pressure resulting between the venturi nozzle and medication
reservoir is such that no medication is drawn upward through the
primary suction line for nebulization and discharge. The various
pressure flow diagrams in FIGS. 2-16 show the various applied
pressures and suction and when medication is drawn upward through
the primary suction line and nebulization occurs and the forces
involved, such as through inhalation.
[0070] In accordance with a non-limiting example as disclosed in
the Ser. No. 13/799,196 and Ser. No. 13/353,611 applications, the
nebulizer initiates nebulization upon inhalation. The nebulizer is
configured as an intra-oral nebulizer and can be operated with half
liter air flow using the low pressure air source in one example.
Nebulization is activated by a patient breathing and inhaling.
Micro amounts of medication are released only when required during
inspiration and will not flow into the gut because of the low
velocity and the configuration of the nebulizer as an intra-oral
nebulizer. This is also aided because the venturi nozzle is
positioned intra-orally. Because most dosages of the nebulized
medication go into the lungs upon inhalation, if dangerous drugs
are being inhaled during nebulization, it is not likely that they
will be released into the ambient and surrounding air to harm
others.
[0071] There are various mechanics of jet nebulizers that should be
understood. A jet nebulizer is a device that is used to deliver
medication to the respiratory system using a supplied air source.
Traditional nebulizers have a vertical column of air passing
through a reservoir of medication, which has a separation at the
top of the nozzle allowing the air and medication to mix. This
mixture accounts for the initial medication droplet formation due
to the drastic change in surface area and aerodynamic effects of
the mixture region. This initial droplet formation can be estimated
from a linear stability analysis and an aerodynamic loading
analysis using parameters such as the Reynolds number, Mach number,
and Weber number. This initial droplet formation in this region is
normally not sufficient for the desired deposition of the
medication in the respiratory tract. To further reduce the droplet
size, these droplets travel at high speed and collide with a
baffle. This impact energy greatly reduces the droplet size to an
acceptable level for deposition of medicine.
[0072] This traditional approach has several draw backs. One of the
primary factors is that additional medication is required to
deliver the proper dose to the desired region of the respiratory
tract. Droplet formation occurs outside of the mouth in traditional
devices and then has to travel through tubes, masks and the mouth.
This additional travel period allows more particle to particle
interaction. These particle collisions allow for particle
combining, creating a larger diameter. Deposition will not occur
with these larger diameter droplets, and therefore waste
occurs.
[0073] Reducing these particle interactions is possible using the
nebulizer as shown in FIG. 1. This nebulizer operates to nebulize
in the mouth and operates as a horizontal nebulizer to allow for
smaller droplet sizes for deposition at a lower zone in the
respiratory tract and use less medication, resulting in less
waste.
[0074] The illustrated nebulizer operates such that the
differential pressures result with the nebulizer operating at a
flow condition when at standard atmospheric pressure. Nebulization
does not occur. As pressure decreases within the nebulizer due to
inhalation, the differential pressures result in medication as
fluid to flow up a suction line into the nozzle.
[0075] Referring now to FIG. 1, there is disclosed an improved
horizontal nebulizer 50 having a nebulizer body 51 with a breath
activated venturi nozzle 52 that together with other components
creates the differential pressure between the venturi nozzle 52 and
the medication reservoir 58 when air is passed through the venturi
nozzle 52. The nebulizer body 51 includes an air channel section 54
and medication reservoir 58 and a nebulizer outlet 60 configured to
be received within an oral cavity of the patient. The nebulizer
body is generally horizontally configured and includes a mouthpiece
portion 62. In one embodiment, a pacifier housing 64 is added as
shown by the dashed line, to form a pacifier or lollipop
configuration at the nebulizer outlet. An air line 66 extends into
the air channel section and includes the venturi nozzle 52 that is
configured with the air channel section to form at its end a low
pressure mixing chamber 68. FIGS. 2 and 3 show in greater detail
the air line 66 and venturi nozzle 52 that are configured with the
air channel section to form that low pressure mixing chamber, which
is somewhat conically shaped.
[0076] A primary suction line 70 extends from the medication
reservoir 58 to the low pressure mixing chamber 68 through which
medication is drawn upward and mixed with air from the venturi
nozzle 52 and nebulized for discharge through the nebulizer outlet
60. A compressed air line 72 can connect to the end of the body via
an appropriate fitting 74. The venturi nozzle 52, low pressure
mixing chamber 68 and air channel section 54 are configured such
that at standard temperature and pressure (STP), a differential
pressure results in no medication that is drawn upward through the
primary suction line 70 for atomization, and none discharged
through the nebulizer outlet, until a negative inspiratory pressure
is created from inhalation by a user.
[0077] As explained below, nebulization begins at a negative
expiratory pressure from about -3 cmH.sub.2O to about -52
cmH.sub.2O. The venturi nozzle 52 is positioned at a location to be
placed within a patient's oral cavity when the nebulizer in use and
received in the mouth of the user. As illustrated, a rainfall
chamber 76 is formed within the body 51 at the air channel section
54 into which the venturi nozzle 52 and low pressure mixing chamber
are formed. As further illustrated, a diffuser 78 acts an impactor
upon which the nebulized medication and air exiting the venturi
nozzle and low pressure mixing chamber impacts to aid in
nebulization. A secondary suction line 80 is formed within the
rainfall chamber 76 and draws nebulized medication that had dropped
down after impacting the diffuser or impactor. A better view of the
secondary suction line is shown in FIGS. 2 and 3. In another
example, an airflow sensor 82 can be positioned within the air
channel section at the nebulizer outlet and configured to generate
signals 83 indicative of air flow generated by a patient's
involuntary cough event occurring at nebulization. A processor 84
could be associated with the nebulizer or a separate unit such as a
handheld unit as shown in FIG. 26. This processor can receive
signals and evaluate the involuntary cough event as explained in
greater detail below.
[0078] The dashed lines in FIG. 1 show that the nebulizer outlet
can be configured as a infant pacifier and be formed as a housing
or lollipop. In another example, it is possible for a housing to
enclose the body and have an end adjacent to the nebulizer outlet
configured as an infant pacifier such as shown relative to FIGS. 21
and 22.
[0079] When the nebulizer is operating at a flow condition and at
standard atmospheric pressure (STP), the differential pressures
cause no fluid flow from the medication reservoir upward through
the primary suction line into the low pressure mixing chamber. As
the pressure decreases within the nebulizer due to inhalation,
i.e., resulting from the negative inspiratory pressure, the
differential pressure results in medication flowing up into the low
pressure mixing chamber and air flowing through the venturi
nozzle.
[0080] There is illustrated the medication reservoir 58 that
includes the primary suction line where the medication is drawn up
into the low pressure mixing chamber and air flows through the
venturi nozzle. The nebulizer includes a breath activated venturi.
Although the venturi is positioned for intra-oral use, it is not
necessary to be in that position and can be located outside the
oral cavity. The medication is released during breath activation as
a horizontal nebulizer compared to an updraft style. Various
medications could be mixed during the intake cycle. The nebulizer
in accordance with a non-limiting example is an improvement over
those prior art nebulizers that are actuated by pressing a valve
for a user regulator while nebulizing.
[0081] In the nebulizer shown in FIG. 1, the flow through the
venturi nozzle 52 is not activated until there is a negative
inspiratory pressure, such as created from inhalation by the
patient. In this nebulizer, air pressure is continuous, but
nebulization is not. The rainfall chamber 76 is provided, but at
STP, there is no flow of medication. At about -3 cm negative
pressure, the negative suction actuates air flow and medication to
be drawn upward through the primary suction line. When this occurs,
the nebulized solution extends from the low pressure mixing chamber
68 and impacts the diffuser 78, i.e., impactor and some droplets
fall to be picked up by the secondary suction line 80. There are no
residual drops, condensation or agglomeration of nebulized
medication that forms in front of the rain chamber, which could
result in poor nebulization and air being drawn in by the patient.
It is recirculated as a true nebulized medication.
[0082] In one example, the average pressure begins nebulizer
operation at -52 cm with a 2 liter a minute flow rate. It is
possible to begin flow at -3 cm negative pressure, but that has
been found to be too sensitive. In another example, the nebulizer
is configured to begin flow at -15 cm corresponding to -1 bar. The
venturi nozzle and other components of the nebulizer as shown in
FIG. 1 can be designed to begin flow from -3 to -100 cm within the
venturi nozzle. The nebulizer is a jet nebulizer that requires the
negative inspiratory pressure to allow the venturi to begin
operating. The medicine fluid will not pass into the airstream
until the flow begins through the venturi nozzle. Air is blowing at
rest, but no venturi operation with flow occurs until a negative
inspiratory pressure is supplied in front of the venturi nozzle at
the air channel section to initiate the venturi effect and draw the
medication up into the jet stream at the low pressure mixing
chamber. As long as the negative inspiratory pressure is applied,
there will be flow. If the negative inspiratory pressure stops,
there is no flow. One nebulizer configuration is for a 5 liter per
minute air flow, but the nebulizer can be configured for 2 liter up
to 15 liter air flow. When the venturi nozzle begins operation, the
medication hits the diffuser or impactor and some droplets fall
downward and are drawn up by the secondary suction line.
[0083] The nebulizer shown in FIG. 1 operates when there is
negative inspiratory pressure that activates the air flow through
the venturi nozzle and into the low pressure mixing chamber. It
does not matter if the venturi nozzle is inside or outside the
mouth. It is also not a timed type of nebulizer such as with
processor monitored breathing or arranging nebulization based on
breathing cycles and valves. With the nebulizer shown in FIG. 1,
the patient inhales at a certain amount of pressure and the air
flow through the venturi nozzle. In one example, it is one bar
corresponding to -15 cm of water. The average may be -53 cm and the
first -15 cm could activates flow through the venturi nozzle. When
inhalation pressure drops below -15 cm, then flow through a venturi
nozzle ceases.
[0084] FIG. 17 is a chart showing respiratory pressures for
measured and predicted MIP (maximal inspiratory pressure) and MEP
(maximal expiratory pressure), as an example with the nebulizer
shown in FIG. 1.
[0085] FIGS. 2-16 are sectional views of the nebulizer of FIG. 1
and showing the air flow through the nebulizer of FIG. 1 at STP and
different pressures as showing the variations in pressure and air
flow. A flow of 2 L/min is illustrated in most of the diagrams and
pressure gradients are shown at STP and other pressures. These
figures also show the pressure gradients and medication flow upward
through the primary suction line at different inspiratory
pressures. As shown in the various FIGS. 2-16 and FIG. 35, the
primary suction line is also tapered as a venturi from the
medication reservoir upward to the venturi and low pressure mixing
chamber. The design and dimension of the venturi relative to the
venturi design of the primary suction line, together with the
configuration of the low pressure mixing chamber and air channel
section, are dimensioned and connected together such that at
standard temperature and pressure (STP), a differential pressure
results in no medication being drawn upward through the primary
suction line for nebulization and discharge through the nebulizer
outlet until a predetermined negative inspiratory pressure is
created from inhalation by a user. Upon user inhalation that
creates the negative inspiratory pressure, air flow begins through
the venturi nozzle and medication is drawn upward through the
primary suction line and nebulized by the air flowing through the
venturi nozzle to be discharged through the nebulizer outlet.
Further details regarding the vent configuration as shown in FIGS.
28-35 and other internal components are now illustrated and
explained.
[0086] FIGS. 28-35 are other views of the nebulizer 50 such as
described at FIGS. 1-16. FIG. 28 shows a side elevation view of the
nebulizer 50 with a top screw fitting 90 on the nebulizer body 51
that receives a medication reservoir such as a vial or medicine
container that may be screwed onto the fitting 90. Other types of
fittings may be used. An internal member (not shown) pierces any
medicine container to allow medication from the medicine container
to flow into the reservoir.
[0087] FIG. 29 is an end elevation view of the nebulizer 50 showing
the air line 66 and the vent 92 formed in the nebulizer body 51
that communicates with the air channel section 54 and medication
reservoir 58 to vent the air channel section 54 and medication
reservoir 58 to outside ambient air. The vent may be formed as a
valve. The air line 66 receives continuous pressurized air, but it
is low pressure. The vent allows balancing of pressures at STP and
with the pressurized air so that upon inhalation of the nebulizer,
medicine is nebulized.
[0088] FIG. 31 is a fragmentary phantom view of a portion of the
nebulizer body 51 showing the vent 92 formed in the nebulizer body
and communicating with the air channel section 54 and medication
reservoir 58 to vent the air channel section and medication
reservoir to outside ambient air. Different vent configurations may
be used besides the illustrated example. The communication between
the sections in the nebulizer body could be by air channels and
similar techniques.
[0089] FIG. 32 is a more detailed partial cut-away plan view of the
nebulizer body 51 showing the air line 66 extending through the air
channel section 54 and including the venturi nozzle 56 and its end
configured to form a low pressure mixing chamber 68 and the vent 92
formed in the body and communicating with the air channel section
54 and medication reservoir 58. The rainfall chamber 76 is
illustrated such that the vent 92 is configured to vent the air
channel section 54 and medication reservoir 58 to atmospheric
pressure such that at standard temperature and pressure, a
differential pressure results between the venturi nozzle 52 and
medication reservoir 58. No medication is drawn upward through the
primary suction line for nebulization and discharge through the
nebulizer outlet until a negative inspiratory pressure is created
from inhalation by a user. FIG. 32 also shows a diffuser or baffle
78 upon which the nebulized medication and air exiting the venturi
nozzle and low pressure mixing chamber impacts to aid nebulization
at the rainfall chamber. FIGS. 33 and 34 show greater details of
the internal structure.
[0090] FIG. 35 shows air flow such as the medication from a
medication container that may be screwed onto the fitting 90 and
passes into the reservoir where it is then drawn into the primary
suction line (although no arrows are illustrated in this example in
the primary suction line). FIG. 35 also shows the processor 84 that
may be used in conjunction with a valve (not shown) that may be
part of the air flow line and also to receive measurements from an
air flow sensor 82 such as positioned in the outlet. Based upon
these measurements, adjustments could be made to the pressure of
any gas flowing through the nebulizer from a source such as a
continuous air flow line or canister that may be connected such as
shown in an example of FIG. 46 and flow and pressure changes
made.
[0091] The nebulizer described in FIG. 1 can advantageously be used
for pediatric patients, such as young children and infants. FIGS.
18 and 19 show a nebulizer 100 in a pacifier configuration in which
a rainfall chamber design as disclosed in the commonly assigned and
incorporated by reference '306 patent includes an outer housing or
body 102 that is configured similar to a pacifier or can be
configured similar to a lollipop.
[0092] This nebulizer in one example could be designed similar to
the nebulizer show in FIG. 1 and be activated by negative
inspiratory pressure. In another example such as shown in FIG. 20
of the nebulizer, a pressure sensor 104 positioned at the nebulizer
outlet senses negative inspiratory pressure. Upon sensing the
negative inhibitory pressure, a signal is transferred back to a
processor or controller or switch to operate the nebulizer. In a
preferred example, however, the nebulizer shown in FIG. 1 is used,
and there is no need to use a sensor with the associated processor.
If the configuration of FIG. 1 is used, the negative inspiratory
pressure begins the flow through the venturi nozzle and initiates
medicine flow and nebulization.
[0093] The outer portion of the housing or body of the pacifier
section of the nebulizer such as shown in FIGS. 19 and 20 includes
a section that has a flavoring 106 and the position sensor 108 to
indicate the infant's mouth position. This flavoring section is
advantageous for sensor placement when an infant sucks on the
pacifier or lollipop configured nebulizer. The infant or child will
naturally suck on those areas of the pacifier that have the
flavoring, indicative that the infant has positioned the pacifier
nebulizer in its mouth in the proper position to allow nebulization
to occur. When the infant or child has received the pacifier
nebulizer in its the proper position as indicated by the sensor
indicating this position, the lips or other portion of the infant's
mouth covers the position sensor to indicate the proper mouth
position. The position sensor sends a signal back to a controller,
for example, to activate the nebulizer for operation. Operation in
one example occurs only when the pressure sensor senses the
negative inspiratory pressure. In the venturi nozzle design of FIG.
1, however, the negative inspiratory pressure itself begins the air
flow through the venturi nozzle and medication to be drawn upward.
The controller could actuate a valve to begin air flow, but
nebulization would begin only with the negative inspiratory
pressure, in one example.
[0094] As illustrated, if a nebulizer other than that shown in FIG.
1 is used, the flavoring on the outer portion of the pacifier
allows an infant or child to position the pacifier nebulizer in its
proper position in its mouth to allow nebulizer operation since the
infant or child will naturally position the pacifier in a position
where it can sense the flavor. A sugar-free flavoring can be
used.
[0095] When this occurs, the infant will activate the position
sensor that indicates the pacifier is in the proper position in the
mouth for full nebulization and it effects. This activates the
nebulizer for operation. The other pressure sensor within the
intake would sense the negative inspiratory pressure, which then
would send a signal back to a processor or controller or switch
that is connected to any valves and/or medicine reservoirs and air
lines to operate the nebulizer. Valves could open to allow
operation in this example.
[0096] FIG. 1B shows a configuration in which the pacifier is
received within an infant's mouth. The rainfall chamber portion is
contained within the nebulizer or lollipop configured body or
housing as a nebulizer suction member formed from a flexible
material, as shown in FIGS. 19 and 20, while the other sections of
the nebulizer such as in the '306 patent, e.g., the medicine
reservoir and any other type of medicine containers are contained
in a separate housing or body that could be configured similar to a
choo-choo train or other infant toy.
[0097] Also, the use of more than one medicine container with
different medicines can allow simultaneous treatment or delivery of
different medicines, actually creating a new drug based upon the
combination. It is possible to change the combination depending on
infant and child needs. Thus, with the configuration of FIG. 1 an
infant can inhale creating the negative inspiratory force to
activate the nebulizer, which becomes breath activated in this
example. Other configurations can be used where inhalation can
cause the nebulizer to open with different valves depending on the
design.
[0098] FIG. 20 shows a nebulizer configuration such as described in
the incorporated by reference '306 patent in which the nebulizer
includes the rainfall chamber 110 and venturi 112 and medicine feed
lines 114. Although not illustrated, the nebulizer could include a
reservoir of medicine and would include at a distal end beyond a
medicine port an air intake for an air line feeding the venturi
inside the nebulization rainfall chamber. The medicine for the
nebulizer can be filled directly into the reservoir or the
nebulizer can come preloaded with the medicine. A venturi air line
116 could include a patient air intake port that allows air to be
taken in at that port and fed through the body of the nebulizer. A
cap could cover a medicine reservoir and be screwed on, snapped on,
or otherwise locked on. The cap could be constructed so medicine
could be injected into the reservoir through the cap.
[0099] FIG. 20 shows the side sectional view of the end of the
pediatric nebulizer that engages the patient's mouth in accordance
with one aspect of the invention, showing in more detail the
rainfall chamber 110 and the venturi 112 and medicine feed lines
114. The venturi nozzle is approximately in the center of the
illustration. Right beneath the venturi nozzle is a chamber which
is fed by a venturi air line, indicated at the lower portion of the
figure to the left of the venturi chamber. Parallel to the venturi
air line and located somewhat displaced above the venturi air line
is the medicine feed line 114. Medicine from the reservoir flows
through the medicine feed line and through a relatively small
opening just prior to the venturi in order to dispense medication
into the air flow of the venturi. The venturi effect causes a
reduction in pressure which causes the medicine to flow from the
reservoir through the medicine feed line and into the venturi space
where it is mixed with the air in traditional venturi fashion. The
medicine that is nebulized by action of the venturi is expelled
from the venturi port in an upward direction toward the diffuser
120. The diffuser in this case, is shown as textured. It is not
necessary that it be textured but texturing may facilitate the
break up of the droplets from the venturi into smaller sizes. As
the droplets from the venturi bounce off the diffuser and break up,
the sizes may not be totally uniform. The air pressure, the feed
rate, the velocity with which droplets impact the diffuser and
other well known factors can facilitate production of droplets of
desired sizes. In fact, droplets can be generated utilizing this
arrangement in sizes less than 0.1 microns. Nevertheless, larger
droplets may coalesce as they diffuse throughout the rainfall
chamber space. As droplets coalesce, they become larger and fall
toward the bottom of the chamber where medication that is not
utilized is gathered in a recycle sump 122. Medication found in the
recycle sump, is recycled through the recycle venturi port 124 to
the proximity with the venturi intake to be reutilized. In this
manner, very little medication is wasted and the amount of
medication delivered to the patient can be tightly controlled.
[0100] When the infant places his mouth on the patient inhale port,
air from the infant inhale air path will circulate over the
rainfall chamber and around the diffuser causing the extraction of
droplets from the rainfall chamber for delivery to the patient. The
patient inhale air path may go not only over the rainfall chamber
but around it to either side with the actual sizing depending upon
the need for the amount of air flow to be delivered to the patient
during administration of medication.
[0101] Dose reliability and reproducibility is enhanced by using
unit dose medicine containers. High lung-deposition efficiency is
vastly improved over the prior art because the venturi is located
near or preferably inside the oral cavity. Very fine particles can
be produced in accordance with the invention.
[0102] FIG. 20A shows a more complete view of the nebulizer as
shown in FIG. 20, which also includes an air flow sensor 130 within
the patient air flow channel. The pediatric nebulizer that
incorporates this design could include air flow sensing ability to
determine the capabilities of the infant as to one capacity and
other details, but also give an indication of response, if
necessary, to an involuntary reflex cough test. The air flow sensor
could be connected by a wireless interface with a processor and
transceiver such as shown in FIG. 23 and described below. Thus,
functional components as shown relative to FIG. 23 can also be
included in the nebulizer such as shown at FIG. 20A.
[0103] FIGS. 21 and 22 show other nebulizers configured for
pediatric use. The venturi can be designed for breath activation as
described before. Although the suction line is illustrated as a
primary suction line, it should be understood that a secondary
suction line can be used. FIG. 21 shows a nipple configuration and
FIG. 22 shows a lollipop configuration.
[0104] FIG. 21 shows a different configuration for the nebulizer
100 that includes a mouth guard 110 and a suction line with the air
line attachment. A different type of impactor/fractionator is
disclosed and the nebulized medicine will impact against the
impactor/fractionator and be discharged though the orifice at the
nipple. The drops are spread throughout the open area defined by
the pacifier housing. In another example, the nebulizer can operate
in timed sequence to permit nebulization at specified times. A
mouth guard is also illustrated.
[0105] FIG. 22 shows a modified lollipop configuration in which the
air line attachment is shown in the primary suction line with the
interior surface of the lollipop housing forming the
impactor/fractionators to create greater fractionation. It is
possible to insert a flow meter device such as a fan wheel that can
operate to determine air flow for testing purposes. The air flow
sensor could be connected to a small processor or communicate with
a plug-in in which a handheld device such as shown in FIG. 26 can
be plugged into the rear of the lollipop configured nebulizer.
[0106] It should also be understood that new medicines can be
designed by use of the venturi system. It is possible to preload
the drug and form a new drug as a method. The nebulizer could
operate as a trihaler or quadhaler. It can be placed in a solution
in one container as a new drug and combined with a delivery system.
It is possible to form the nebulizer and preload with the drug.
Blow, fill and seal technology could be used to form a throw away
nebulizer that is used one time. It could be filled and sealed at
the manufacturing line. There could be a prefill port of any
different shape or form and different types of medication delivery
configurations. An example of different configurations for medicine
supply as shown in FIGS. 15 and 16 of the commonly assigned U.S.
Pat. No. 8,109,266.
[0107] The use of a second nozzle or secondary suction line 80 can
be advantageous because when condensation or agglomeration occurs,
a drug will drop down through gravity feed and be redrawn to aid in
mixing especially with preloaded medicine. Thus, the nebulizer
shown in FIG. 1 can be formed as a sterile preloaded medicated
nebulizer as a throw away device. Multiple new drugs can be
developed through mixing with the nebulization and a venturi
action.
[0108] It is also desirable to incorporate a flow meter function as
described in the commonly assigned U.S. Pat. No. 8,109,266. This
incorporated by reference patent application shows two types of
flow meter designs that could operate as a clip-on device onto the
various nebulizers disclosed and incorporated by referenced patents
identified above. Other designs are in-line and are the preferred
design with the nebulizer configurations shown in FIG. 1 or any
pediatric nebulizers. In one desired design, a spinning wheel is
used instead of the designs shown in the incorporated by reference
application. In the embodiments described in the instant
application, the nebulizer can be used to measure involuntary cough
and measure the expiatory flow for the voluntary cough and what is
the response. This could be beneficial with the pediatric nebulizer
using the pediatric nebulizer for diagnoses. A spinning wheel for
some type of spirometers could be incorporated into the nebulizers
and used with the C5 stimulus, in which the involuntary cough
occurs on the average of 4.8 times (average of 5 times) or 4.8
seconds on an average. The spinning wheel can calibrate a processor
to measure peak flow and time over the inspiration and expiration
and form a graph. It is possible to form the nebulizer where a
button is pressed to activate the nebulizer, resulting in the
involuntary cough. A flow sensor can be integrated with the
nebulizer measures air flow at the time of the involuntary cough or
at the time the button is hit. It is possible to plug the hand held
device into the nebulizer as illustrated. The nebulizer device can
perform the pulmonary function test (PFT) that is adequate for use
with kids, such as using the lollipop nebulizer as shown in FIG.
21. It is possible to measure the velocity of the airflow and draw
a graph of the inspiration and expiration over time. The system can
draw loop interfaces to the processor or other PC and be compared
relative to voluntary cough. During the C5 event it is possible to
establish the normal versus the abnormal range.
[0109] Reference is made to the commonly assigned and incorporated
by reference to U.S. Pat. No. 8,597,184 and U.S. Patent Publication
Nos. 2011/0046653 and 2011/0040211, the disclosures which are
hereby incorporated by reference in their entirety. It is possible
to diagnose GERD and perform other analysis as explained in those
incorporated by reference patent applications, including diagnosing
stress urinary incontinence and problems with the lower esophageal
sphincter.
[0110] The flow meter could be formed within an extension as a
collar or molded into the nebulizer itself.
[0111] There is now described the nebulizers and flow meter sensor
relative to FIGS. 23-27, similar to the description taken from the
incorporated by reference U.S. Pat. No. 8,109,266.
[0112] FIG. 23 shows a nebulizer 204 that includes the main body
200 having an air channel section 201 that is formed by the air
line intake 300 and fluid/air channel section 230 and related
sections of the main body as illustrated and including a mixing
chamber 330 and venturi 310 positioned to be placed within close
proximity or within the patient's oral cavity in this non-limiting
example and configured to receive medicine and air and mix the
medicine and air within the mixing chamber and receive the air flow
through the venturi and cause the medicine entering the mixing
chamber to be atomized by the action of air flowing through the
venturi. In this embodiment, an air flow sensor 280 is associated
with the main body, and in this example at diffuser 250, and
configured to measure the air flow created by the patient's one of
at least inhaling and exhaling air. In this example, the air flow
sensor 280 is positioned within the air channel section 330 and as
illustrated at the exit side of the mixing chamber within the
diffuser such that air flow is measured when the patient is at
least one of inhaling and exhaling air through the diffuser in this
example.
[0113] The air flow sensor 280 senses and measures the air flow and
sends a signal through communications signal lines 282 (shown in
FIG. 24) back to a wireless module 284 positioned in the main body
200. The wireless module 284 in this example includes a processor
286 and wireless transceiver 288 such that the signals from the air
flow sensor 280 are processed and in this example wirelessly
transmitted through an antenna 289 (which could be a conformal
antenna positioned on the main body 200) to a handheld processing
device 560 such as shown in FIG. 26 and with its processing
capability illustrated in block diagram at FIG. 27. The outlet at
the diffuser on the exit side of the mixing chamber in this example
chamber includes an air flow metering valve 290 positioned within
the air flow channel and configured to adjust the resistance to air
flow to a predetermined level for respiratory exercise training and
incentive spirometry use. In this example, the air flow metering
valve 290 is formed as a baffle or similar mechanism that can be
adjusted to vary the amount of air flow resistance. The adjustment
can be indexed such that any adjustment and air flow resistance can
be predetermined, for example, using a manual adjustment or servo
drive (actuator) for adjusting the valve. The air flow sensor 280
in this non-limiting example is shown as paddle wheel type sensor
or could be a flap with actuators, such as MEMS actuator, which
inter-operate with a processor to determine air flow adjacent the
air flow metering valve 290. The air flow metering valve 290 in an
example includes a small drive mechanism such as an actuator
attached thereto, allowing adjustments to be made based upon a
signal such as from the processor 286 and feedback signal from the
air flow sensor to adjust and vary the amount of resistance to air
flow for respiratory exercise training and incentive spirometry
use. The valve 290 can also in one example be manually adjusted by
a patient and include settings to aid in adjustment as noted
before.
[0114] In a non-limiting example, the handheld processing device
560 is configured to process the measured air flow over time to
determine a respiratory function of the patient. This device 560 is
also configured in another example to process measured air flow
over time to determine a neurological deficiency in a patient based
on air flow measurements derived from an involuntary reflex cough.
For example, the analysis of the voluntary cough and involuntary
reflex cough test is disclosed in commonly assigned U.S. Patent
Publication Nos. 2007/0135736; 2007/0255090; 2011/0046653; and
2011/0040211; and U.S. Pat. Nos. 8,597,183; 8,602,987; and
8,597,184, the disclosures which are hereby incorporated by
reference in their entirety. These commonly assigned published
patent applications and issued patents set forth details of the
voluntary cough testing and involuntary reflex cough testing in
which the nebulizer as described in the instant application can be
used to aid in the type of testing as set forth in those
incorporated by reference applications. Such testing is
advantageously used to diagnose stress urinary incontinence or
problems in the lower-esophageal sphincter as a non-limiting
example.
[0115] FIG. 25 shows a modified nebulizer such as the type
disclosed in commonly assigned U.S. Publication No. 2007/0137648,
the disclosure which is hereby incorporated by reference in its
entirety. This application shows air curtain inlets created by air
curtain conduits 404 that are used to supply a curtain of air above
and below the nebulized medicine and air passing through medication
conduit 400 and to enhance penetration of nebulized medicine into
the airway of the patient. The air flow sensor 280 as a paddle
wheel type device is positioned at the exit end of the nebulizer
204 as illustrated and in this example includes the air flow
metering valve 290 as illustrated and incorporates a manual or
automatic adjustment mechanism such as an actuator as may be
needed.
[0116] It should be understood that different types of air flow
sensors 280 can be used besides the illustrated spinning wheel
configuration. As disclosed in the incorporated by reference U.S.
Pat. No. 8,109,266, it is possible to design the air flow sensor
280 as a mass air flow sensor that converts the amount of air drawn
or expelled into and out of the nebulizer into a voltage signal.
Different types of mass air flow sensors could be used such as a
vane air flow meter, including using any necessary MEMS technology
or using a Karmen vortex or a semiconductor based MAF sensor. It is
possible to use a hot wire MAF sensor such as a thermistor,
platinum hot wire or other electronic control circuit to measure
temperature of incoming air, which is maintained at a constant
temperature in relation to the thermistor by an electronic control
circuit. As heat is lost, electronic control circuitry can
compensate by sending more current through the wire. This is only
one example. The wire typically will be kept cool enough such that
the temperature does not impact a patient. The hot wire can be
placed further into the diffuser and/or main body within the air
channel. It is also possible to use an Intake Air Temperature (IAT)
sensor.
[0117] Another possible air flow sensor is a vane air flow meter
that includes basic measuring and compensation plates and other
potentiometer circuits. In another example, the air flow sensor
uses a "cold wire" system where an inductance of a tiny sensor
changes with the air mass flow over that sensor as part of an
oscillator circuit whose oscillation frequency changes with sensor
inductance. In another example, the flow sensor is an electronic
membrane placed in the air stream that has a thin film temperature
sensor such as printed on an upstream side and another on the
downstream side and a heater in the center of the membrane that
maintains a constant temperature similar to the hot-wire. Any air
flow causes the membrane to cool differently at the upstream side
from the downstream side and this difference indicates the mass air
flow. MEMS technology can be used such as MEMS sensors. In this
type of sensor, a MEMS sensor has a silicon structure and sometimes
combined with analog amplification on a microchip. It includes an
analog-to-digital converter on a chip in another example and can be
fused with analog amplification and the analog-to-digital
converters and digital intelligence for linearization and
temperature compensation. The MEMS testing in one example is used
for an actuator to control the valve 290.
[0118] It should be understood that although the air flow sensor is
shown located at the discharge end of the nebulizer at the diffuser
on the exit side of the mixing chamber, other locations and
positions for the air flow sensor or number of air flow sensor
members are possible as well as the valve 290.
[0119] It should also be understood that the nebulizer using the
waterfall chamber as described in incorporated by reference patent
publications also in an example has the flow meter function as
described and includes the air flow sensor and wireless module as
illustrated in FIGS. 23 and 24 and can be positioned in different
locations within that device. The air flow sensor can be located at
the discharge end on the exit side of the rainfall chamber or other
locations in which the air flow can be measured. The valve 290 is
also included in another embodiment and includes an actuator in yet
another embodiment.
[0120] Air flow can be measured in pounds per second (lbs./sec.)
and operate for pulmonary function testing calculations and
incentive spirometry use. The nebulizer in this example can work as
a differential pressure transducer and connect to a
pneumotachygraph (or have a self-contained chip with such function)
to record the velocity of respired air. It is possible to process
associated data as air flow, air pressure, air resistance, and
other Pulmonary Function Testing (PFT) results for respired air and
data results from voluntary cough (VC) and involuntary reflex cough
testing (iRCT). The pulmonary function testing can use spirometry
to assess the integrated mechanical function of the lungs, chest
wall and respiratory muscles and measure the total volume of air
exhaled from a full lung for total lung capacity and empty lungs as
residual volume. The Forced Vital Capacity (FVC) can be measured
and a forceful exhalation (FEV.sub.1) can be repeated. Spirometry
can be used to establish baseline lung function, evaluate dyspnia,
detect pulmonary disease and monitor effects of therapies used to
treat respiratory disease and evaluate respiratory impairment and
evaluate the operative risk and perform surveillance for
occupational-related lung disease. Pulmonary function testing can
be used to determine how much air volume is moved in and out of the
lungs and how fast the air in the lungs is moved in and out. This
testing can determine the stiffness of the lungs and chest wall for
compliance. The flow meter function using the air flow sensor and
the associated air flow metering valve together with any processing
capability can be used for Inspiratory Muscle Training (IMT) to
provide consistent and specific pressures for inspiratory muscle
strength and endurance training. The adjustable valve or other
adjustable mechanism can ensure consistent resistance and be
adjustable such as manually or through microprocessor control for
specific pressure settings. It is possible to use the same
nebulizer for exercise treatments and therapy and spirometer
treatments. The handheld processing device 560 captures the data
and can be marketed together with the nebulizer and any necessary
catheters for reflex cough testing as a kit. The pneumotachygraph
function can be placed in a single chip within the nebulizer or as
a separate flow meter device explained below relative to FIG. 25
and connected to the nebulizer. Data containing air flow
measurement results can be wirelessly transmitted to the handheld
processing device or other processor.
[0121] The nebulizer also operates in a non-limiting example as a
differential pressure transducer. If the nebulizer is to measure
voluntary cough or the involuntary reflex cough, an air channel can
be connected to the medicine and gas canister (for tartaric acid in
one example) and measure the voluntary cough and involuntary reflex
cough for in-phase duration from the time from onset to peak and
expulsive phase and in-phase volume such as the duration of the
glottic closure as explained in greater detail below. It is also
possible to measure in-phase peak flow and the expulsive phase peak
flow using such device.
[0122] A patient (or clinician or physician) can perform a medical
treatment with the nebulizer. It is also possible to operate the
flow meter after nebulization to determine if the patient has
improved due to the use and administration of the drug such as the
tartaric acid. It is possible to measure and graph results through
an air flow sensor as part of the flow meter device and transfer
data to the handheld device (or other processing device) and
measure flow and pressure over time.
[0123] FIG. 26 is an illustration of an exemplary handheld
processing device 560. More particularly, it should be understood
that this handheld processing device 560 can be used by a nurse
practitioner or doctor and receive input as wireless signals for
flow meter testing as described above. Also, this handheld
processing device 560 can incorporate the circuit and functions as
disclosed in the various copending and commonly assigned
applications identified above. Catheters and other inputs can be
connected to this handheld processing device 560 as explained in
the above-identified and incorporated by reference patent
applications.
[0124] FIG. 27 is a block diagram that illustrates a computer
system 500 for the handheld processing device 560. Computer system
500 includes a bus 502 or other communication mechanism for
communicating information, and a processor 504 coupled with bus 502
for processing information. Computer system 500 also includes a
main memory 506, such as a random access memory (RAM) or other
dynamic storage device, coupled to bus 502 for storing information
and instructions to be executed by processor 504. Main memory 506
also may be used for storing temporary variables or other
intermediate information during execution of instructions to be
executed by processor 504. Computer system 500 further includes a
read only memory (ROM) 508 or other static storage device coupled
to bus 502 for storing static information and instructions for
processor 504.
[0125] Computer system 500 may be coupled via bus 502 to a display
512, such as a LCD, or TFT matrix, for displaying information to a
computer user. An input device 514, for example buttons and/or
keyboard, is coupled to bus 502 for communicating information and
command selections to processor 504. Another type of user input
device is cursor control, such as a mouse, a trackball, or cursor
direction keys for communicating direction information and command
selections to processor 504 and for controlling cursor movement on
display 512. This input device typically has two degrees of freedom
in two axes, a first axis (e.g., x) and a second axis (e.g., y),
that allows the device to specify positions in a plane.
[0126] Computer system 500 operates in response to processor 504
executing one or more sequences of instruction. Execution of the
sequences of instructions causes processor 504 to perform the
process steps described herein. In alternative embodiments,
hard-wired circuitry may be used in place of or in combination with
software instructions to implement the invention. Thus, embodiments
of the invention are not limited to any specific combination of
hardware circuitry and software.
[0127] The term "computer-readable medium" as used herein refers to
any medium that participates in providing instructions to processor
504 for execution. Such a medium may take many forms, including but
not limited to, non-volatile media, volatile media, and
transmission media. Non-volatile media includes, for example,
optical or magnetic disks. Volatile media includes dynamic memory,
such as main memory 506. Transmission media includes coaxial
cables, copper wire and fiber optics, including the wires that
comprise bus 502. Transmission media can also take the form of
acoustic or light waves, such as those generated during radio wave
and infrared data communications.
[0128] Common forms of computer-readable media include, for
example, a floppy disk, a flexible disk, hard disk, magnetic tape,
or any other magnetic medium, a CD-ROM, any other optical medium, a
RAM, a PROM, and EPROM, a FLASH-EPROM, any other memory chip or
cartridge, a carrier wave as described hereinafter, or any other
medium from which a computer can read.
[0129] Various forms of computer readable media may be involved in
carrying one or more sequences of one or more instructions to
processor 504 for execution. For example, the instructions may
initially be carried on a magnetic disk of a remote computer. The
remote computer can load the instructions into its dynamic memory
and send the instructions over a telephone line using a modem. A
modem local to computer system 500 can receive the data on the
telephone line and use an infrared transmitter to convert the data
to an infrared signal. An infrared detector can receive the data
carried in the infrared signal and appropriate circuitry can place
the data on bus 502. Bus 502 carries the data to main memory 506,
from which processor 504 retrieves and executes the instructions.
The instructions received by main memory 506 may optionally be
stored on storage device 510 either before or after execution by
processor 504.
[0130] The handheld device 560 preferably uses wireless technology
that could include infrared (IR), Bluetooth, or RFID technology for
communicating with the wireless transceiver in the wireless module
of the nebulizer or a separate wireless interface as illustrated.
It can be connected directly also. The handheld processing device
560 includes a wireless module 580 that works in conjunction with
the pressure transducer interface and controller 518 and the
respiratory air flow sensor (flow meter) interface 581 and sends
and receives readings through the antenna 582 or other system that
could be used. The wireless module 580 could be located at
different locations.
[0131] There now follows details regarding a particle
characterization when the nebulizer as described with FIGS. 1-16
before is used relative to FIGS. 36A-41 and a test set-up and
results for nebulizer performance under pulsed flow conditions in
FIGS. 42-45S and using the modified nebulizer such as shown in FIG.
46. A description of a metered dose nebulizer is described relative
to FIGS. 47-53 and a metered dose atomizer as a modified form of
the metered dose nebulizer is shown in FIG. 54. FIG. 55 shows an
infant pacifier nebulizer with SNIP capability.
[0132] FIG. 36A shows an anatomical cut-away view with the
intra-oral nebulizer 50 such as shown in previous figures in
accordance with a non-limiting example and positioned within the
oral cavity and showing how aerosol generation occurs in the mouth.
Use of the horizontal venturi nozzle allows nebulized medication to
travel less distance to the deposition area and permits little
condensation, while achieving a targeted Mean Mass Aerodynamic
Diameter (MMAD) with a low Geometric Standard Deviation (GSD) such
as about 1.5 to about 2.0 at a low residual volume. A mouthpiece
from a standard jet nebulizer such as a vertical nebulizer is shown
as received in the oral cavity in a comparison anatomical sectional
view of FIG. 36B. The drawbacks of such a prior art device are
evident and requires significant more surface area and distance to
travel to the target with increased flow rates that are required to
compensate for this loss. The nebulizer 50 as described is
advantageous and allows a shortened drug and device development
time and can be used for matched drug and device and novel drug
delivery for insulin, HIV, cancer treatments, pulmonary treatment,
and pain medications.
[0133] Turbulent flows at the orifice intersection as described
before cause high aerodynamic shear stress on the medicine and the
catastrophic break-up occurs at the primary droplet formation
region. Additional impaction may occur within the nozzle prior to
exiting towards the baffle or diffuser such as the diffuser 78
shown in FIG. 1 and subsequent drawings. There is a secondary
droplet formation as described before and the reduced primary
droplet formation decreases the required energy to create a desired
particle size after impaction. A large portion of particles will
travel past the baffle or diffuser 78 without impaction. Remaining
particles will impact the baffle and the velocity of particles will
exceed the critical velocity required for splashing to occur.
[0134] FIG. 37 shows a graph of the critical diameter for splashing
to occur on the baffle. For example, the horizontal nebulizer 50 as
described in accordance with a non-limiting examples in FIG. 1 and
subsequent drawings causes additional non-uniform turbulence during
the primary droplet formation and allows for the decreased droplet
size as compared to more traditional vertical nebulizers such as
shown in FIG. 36B that use significant more surface area and
require greater distance to travel to the target.
[0135] The described nebulizer 50 in accordance with a non-limiting
example may operate at lower flow rates of 2-4 liters per minute as
compared to 6-8 liters per minute for traditional nebulizers such
as the vertical nebulizer example shown in FIG. 36B. The low flow
rates offer a small MMAD and GSD (Geometric Standard Deviation)
with an equivalent deposition in the lungs with reduced use of
medication and less ambient medication exposure. For example, a low
density nebulized medication dose allows 70 mg per minute as a
non-limiting example. A Design of Experiments (DOE) for the
nebulizer 50 was conducted using different nebulizer parameters and
the test set-up as shown in FIG. 38 to determine particle size
distribution and calculate an average MMAD and GSD during the
trials, and show changes in MMAD and GSD during the nebulization
process. There was analysis downstream with 47 mm glass fiber
filter for the total mass of nebulized albuterol. The testing
occurred with different nebulizer configurations and two nozzle
variations using a smaller and large diameter and an albuterol
sulfate respule (2.5 mg/2.5 ml) and a 500 UL fill for the nebulizer
test. The flow rate varied between 2, 3, and 4 liters per minute
(LPM), and with the sample of the APS at 12 centimeters distance
from the output of the nebulizer. The test was based on the ISO
13320 standard. The MMAD and Particle Size Distribution (PSD) and
the test distance were taken into account with intra-oral operation
of the nebulizer and USP 90 bend with the Andersen cascade impactor
at 12 cm distance. During testing, the delivered medication dosage
varied and two nozzle variants as a larger diameter feed orifice
and smaller diameter feed orifice were used with the results shown
graphically in FIGS. 39 and 40.
[0136] FIG. 38 shows the test set-up 600 and shows a Hepa filter
602 and a vacuum pump 604, flow control valve 606, 47 millimeter
filter 608, the nebulizer 50 in-line with a flow regulator 610 and
a variable supply flow rate of 2, 3 or 4 liters per minute from
canister 612. Entrainment air passes through the Hepa filter with a
constant total flow of 28.3 liters per minute as drawn by the
vacuum pump and controlled by the flow control valve. The
Aerodynamic Particle Sizer (APS) 616 flow was 1 liter per minute
and provided by TSI Group with data logging 618. Compressed oxygen
from the canister 612 provided the air flow through the flow
regulator 610. The air flow rate was held constant for all trials
at 28.3 liters per minute. The nebulizer air feed from the canister
612 was a research grade oxygen. The Aerodynamic Particle Sizer 616
was an APS Model 3321 to obtain the particle size data with a
capture filter used for total aerosol output. The filter was
analyzed via a Beckman Coulter DU800 scanning UV spectrophotometer
with a four point calibration standard for albuterol. The results
are shown in the graphs of FIGS. 39-41.
[0137] FIG. 39 shows a particle size distribution by mass for a
larger diameter feed orifice nebulizer listed as the ION-19: A
example nebulizer and showing results for flows of 2, 3 and 4
liters per minute. FIG. 40 is another example similar to that shown
in FIG. 39, but for a smaller diameter feed orifice nebulizer
listed as the ION 19.1B example nebulizer. FIG. 41 shows a change
in nebulizer MMAD during nebulization with the various nebulizers
at 3 liters per minute for different configurations with A
configuration corresponding to the larger diameter feed orifice and
B configuration corresponding to the smaller diameter feed orifice.
This graph in FIG. 41 shows that the general trend of the MMAD
during nebulization is a slow decrease in particle size such as
resulting from changes in flow with sputtering or inadequate fluid
pool of fluid through the venturi nozzle.
[0138] As indicated from the test results, as the nebulizer flow
increases, larger particles escape. Traditionally, as nebulizer
flow increases, the shear forces increase and thus produce smaller
particles. This is most likely caused by increased turbulence
within the nebulizer body allowing larger particles to escape
rather than impacting on internal surfaces. The impactions on the
wall or flow patterns are most likely reducing a respirable mass
output. The results also show that the MMAD increases as flow rate
to the nebulizer increases and the MMAD decreases as a function of
nebulization time. The GSD increases as the nebulizer flow
increases and the GSD increases as a function of nebulization time.
The mass output increases with nebulizer flow. In some tested
nebulizer variants, the increase in mass from 3 liters per minute
to 4 liters per minute is minimal possibly because the nebulizer
begins to sputter because of a lack of nebulization fluid. An
interpretation is the MMAD increases with nebulizer flow and the
particle size data shows that there are larger particles being
produced but only at higher flow rates as they are able to escape.
Testing with water when the APS sample nozzle is placed in the
opening/inside of the nebulizer shows a MMAD of around 4
micrometers and the APS suction is pulling out the particle that
normally gets trapped. It is possible to change the impaction plate
(diffuser) within the nebulizer, which may increase the total mass
output. Adding a larger drug reservoir will also increase mass
output and should prevent the nebulizer from sputtering in a
three-minute treatment.
[0139] FIG. 42 is another test set-up 630 to determine the
nebulizer 50 performance under pulsed flow conditions using
albuterol sulfate. The pulse duration and pulse feed pressure are
varied and particle size characterization is obtained for each
trial condition. FIG. 42 shows the test set-up similar to that
shown in FIG. 38 with common elements of the data logging computer
632, TSI APS 634 and a vacuum pump 636 and compressed air source
638 into the pressure regulator 640. What is different is the
location of the vacuum pump 636 as connected to the 47 mm filter
640 into a flow tube 642 with a gauge 644 and the nebulizer
connected into the other end of the flow tube from the 47 mm
filter. A hand actuated solenoid controller 646 is operatively
connected to the solenoid 648 and extends between the nebulizer 50
and pressure regulator 640. The nebulizer 50 was tested with two
different pressures at 7.2 PSI and 15.5 PSI and a pulse duration of
0.5 second, 1.0 second, and 2.0 seconds. Albuterol sulfate respules
were 2.5 mg/2.5 ml and a 500 UL fill. Data collection occurred and
the particle size data was obtained using the TSI aerodynamic
particle sizer model 3321 with a sample port 12 cm downstream of
the nebulizer. The 47 millimeter absolute filter used for the total
drug delivery and analysis occurred via HPLC with a thermo ultimate
3000 nano-HPLC. The test set-up tested multiple feed pressure and
pulse durations with the flow tube of approximately 28.3 liters per
minute.
[0140] FIG. 45B shows a chart of the total delivered drug results
and the feed pressures selected based on the equivalent steady
state flow at 2 and 3 liters per minute for the nebulizer at 7.2
and 15.5 PSI. Pulse duration as shown in the chart was for 0.5, 1.0
and 2.0 seconds per actuation for the nebulizer with 10 or 20 total
actuations depending on the trial and averaged for the nebulizer.
In one example, the nebulizer was hand actuated with a metronome
used as the timing aid and 0.5 ml (500 MCG) fill of albuterol
sulfate per trial for the nebulizer.
[0141] FIG. 43 shows the average peak particle size distribution
for all trials and FIG. 44 shows the average peak particle size
distribution for the mass concentration and average for each
pressure. FIG. 45A shows a bar chart of the delivered drug per
actuation. FIG. 45B is a chart showing the total delivered drug
results with the nebulizer total delivery having an average total
dose of 0.5 to 6.0 micrograms per actuation depending on the
pressure and actuation duration. Higher drug concentrations yield
the higher dose/actuation values with the albuterol sulfate respule
of 1 mg/ml.
[0142] FIG. 46 is a modified nebulizer 50' similar to that shown in
the side elevation view of FIG. 28, but modified to include a
canister 94' as a source of compressed air that connects into a
valve 95' to permit pulsed or continuous air flow. Other elements
shown in FIG. 46 are common to FIG. 28, but illustrated with a
prime notation such as the nebulizer outlet 60', nebulizer body
51', and screw fitting 90'. Different types of valve systems 95'
may be used as known to those skilled in the art to provide the
pulsed or continuous air. For example, the valve 95' may be
adjusted to provide for the range of pressures as described in the
total delivered drug results shown in FIG. 45B. Manual or automatic
adjustment can be accomplished via manually adjustable controls 96'
positioned at the back of the valve as illustrated or such valve
95' can be electronically controlled or pneumatically controlled
and use different technologies including a pneumatic or air pulse
valve.
[0143] FIGS. 47-51 show a non-limiting example of a metered dose
nebulizer (MDN) 700 in accordance with a non-limiting example. This
nebulizer 700 provides a metered flow of gas at a predetermined
pressure and time to provide timed release of gas that may be
variable per drug. It still uses a horizontal nebulizer outlet
configuration and a horizontal venturi nozzle as best shown in the
sectional view of FIG. 50 and the larger exploded, perspective view
of FIG. 51, showing the outlet of the nebulizer.
[0144] FIG. 47 shows the nebulizer 700 that includes a nebulizer
body 702 that is substantially L-shaped and has an air channel
section 704, a nebulizer outlet 706 and medication receiver 708
received at the lower or horizontal portion 702a of the L-shaped
nebulizer body as best shown in the sectional view of FIG. 50. An
air line 710 extends through the air channel section and has an
inlet 710a and an outlet 710b and a venturi nozzle 714 positioned
at the outlet end 710b of the air line. A medication container 720
is received within the medicine receiver 708 at the lower,
horizontal portion 702a as shown in FIGS. 51 and 53. A canister
port 722 is positioned at the inlet end 710a of the air line and
receives a gas canister 724 as shown in the figures. A valve 725 is
positioned at the canister port 722 and actuable to allow a metered
flow of compressed gas at a predetermined pressure and time to flow
from the gas canister through the air line and venturi nozzle
714.
[0145] It should be understood that the valve 725 can be formed
similar to the valve shown and described relative to that of FIG.
46 and allow for a pulsed air delivery. A cylindrical receiving
sleeve 730 is received within the nebulizer body 702 on the
vertical portion 702b formed by the vertically extending portion of
the L to securely receive the gas canister in a vertical
configuration. The sleeve 730 is dimensioned to allow the gas
canister to be slidable therein and includes a bottom sleeve member
732 that engages slidably against the valve 725 via a plunger 732a.
As shown in the sectional view of FIG. 50 and the cut-away
sectional and perspective view of FIG. 52, a suction line 736
extends from the medication receiver 708 to the venturi nozzle 714
and draws medication upward and mixes it with air passing through
the venturi nozzle 714 and nebulizes the medication for discharge
through the nebulizer outlet 706.
[0146] As best shown in FIG. 52, the venturi nozzle 714 and suction
line 736 are formed together and replaceable within the nebulizer
body as one unit. For example, the venturi nozzle 714 and suction
line 736 may be injection molded to form an integral nozzle and
suction line unit as illustrated. The medication receiver 708
includes a top support surface 709. The suction line 736 includes a
flange 737 that is seated on the top support surface 709 to support
the venturi nozzle and suction line in position within the
nebulizer body. The combination venturi nozzle 714 and suction line
736 are received in the outlet and the suction line 736 pressed
downward through the top support surface of the medication
receiver.
[0147] In one example, the medication container 720 is snapped and
twisted into place and the gas receiving end of the venturi nozzle
received into communication with the air line outlet end 710b as
illustrated. As shown in FIG. 50, the gas receiving end of the
venturi nozzle 714 is received over the outlet end of the air line
710b in a press fit while the suction line snaps downward into the
medication container 720, which includes knob extensions 720a to
lock it into place (FIG. 51).
[0148] The various components of the nebulizer can be made from
injection molded plastic or other materials. The medication
container 720 snaps and twist locks into the medicine receiver and
snaps into connection with the bottom of the suction line 736 to
allow communication with the medication container and draw
medication upward through the suction line 736 to the venturi 714.
No impactor or diffuser is used in this example since the suction
line and venturi are dimensioned and formed together to include
respective tapers as illustrated to allow the desired flow of air
and medication whether using a continuous or pulsed flow. Because
no impactor is required and thus a rainfall chamber is not
required. The medication container 720 can be designed to hold a
one day, a one month or longer medication supply depending on end
user requirements. A secondary suction line is not required with no
baffle or impactor.
[0149] The nebulizer embodiment shown in FIGS. 47-51 may be press
activated by pressing the portable gas canister 724 downward to
activate gas flow from the canister through the gas line 710. In
the example shown in FIG. 51, the canister is inserted within the
sleeve and the bottom sleeve member 732 slid and locked into place.
It is also possible to modify a nebulizer to be breath actuated as
in the previous examples of the nebulizer described relative to
FIGS. 1-18 as long as the valve allows the flow of air where the
venturi and nebulizer can be breath actuated. Variable timing is
supplied by the valve that extends between the air canister and the
air line as best shown in FIG. 50 and described before.
[0150] The medicine container 720 may accept liquid solution as
opposed to dry powder. The venturi nozzle 714 is interchangeable
together with the suction line 736 and can be configured into
different designs so that in conjunction with the controlled
pressure and velocity of air released through the valve 725, a
different nebulized gas is created based upon the timed release of
gas, which may be variable for a specific drug. The medicine
container that is inserted from the bottom may contain a month's
supply of albuterol or just a single dosage depending on the design
as an example. It is possible to have a pacifier design as in FIG.
48 (dashed line) with the valve 725 actuated by SNIP.
[0151] FIG. 54 is a modified structure of that nebulizer shown in
FIG. 51, but formed as a metered dose atomizer in which the front
portion corresponding to the horizontal portion of the "L" is
modified as an atomizer. A venturi nozzle is still used. The
atomizer is formed to allow a mist of medication to be formed as is
typical with an atomizer. The valve may also be modified to permit
a more variable, metered dose that enhances the atomization of the
medication and gas. Many of the other components may remain similar
as in the nebulizer embodiment.
[0152] The atomizer 800 shown in FIG. 54 is described by using the
same reference numerals for common components as in the nebulizer
embodiment of FIGS. 47-53, except using the 800 series. The venturi
nozzle 814 is positioned at the outlet end 810b at the air line 810
and has a venturi discharge that is oriented horizontally when in
use and forms a mixing chamber 811 at its discharge end as
illustrated in FIG. 54. A medication receiver 808 is carried by the
atomizer body 802 proximal to the venturi nozzle 814 and mixing
chamber 811. A suction line 836 extends from the venturi nozzle 814
and mixing chamber 811 to the medication receiver 808 that draws
medication upward from the medication container 820 received within
the medication receiver and mixes it with gas passing through the
venturi nozzle into the mixing chamber and atomizes the medication
into a mist. Similar in design to the nebulizer, the atomizer
includes an atomizer body 802 that includes the air channel section
804 and atomizer outlet 806. The atomizer outlet 806 is formed as a
flared extension 807 in this example.
[0153] The atomizer 800 also includes at the mixing chamber 811a
diffuser 813 upon which the gas that is mixed with medication in
the mixing chamber 811 impacts to aid in forming the mist. As in
the nebulizer, a canister port 822 is positioned at the inlet end
810a of the air line 810 and receives a gas canister 824. A valve
825 is positioned at the canister port and actuable to allow a
metered flow of gas at a predetermined pressure and time to flow
from the gas canister through the air line 810 and venturi nozzle
814. The valve 825 is actuated to deliver gas when pressure is
applied downward on the gas canister similar to the nebulizer
design. A medication container 820 is received within the
medication receiver 808 and the suction line 836 connects into the
medication container. The valve actuates a pulsed and metered flow
of gas during atomization.
[0154] As in the nebulizer 700 embodiment, the atomizer 800
includes a substantially L-shaped atomizer body 802 forming a
vertical portion 802b and a horizontal portion 802a. The venturi
nozzle 814, mixing chamber 811 and suction line 836 are formed
together and replaceable as one unit and supported by the
medication receiver 808. The suction line 836 extends through the
top support surface 809 of the medication receiver and connects
into the medication container received within the medication
receiver such as by a snap fit similar to the nebulizer embodiment.
The suction line includes its flange 837 that is seated on the top
support surface 809 of the medication receiver to support the
venturi nozzle 814, mixing chamber 811 and suction line 836 and
positioned within the atomizer body. The combination of the
integrally formed unit of the venturi nozzle, mixing chamber and
suction line can be removed and a different design employed that
will generate a different mist and determine what type of mist and
particle size could be produced.
[0155] It is also possible to use the pediatric nebulizer as
disclosed at FIGS. 18 and 19 with SNIP (Sniff Nasal Inspiratory
Pressure) as shown in FIG. 55, which interoperates with the
nasopharyngeal airstream, which prevents or discourages the drug
from hitting the posterior pharynx when released with breath
activation. A SNIP sensor could be located in the nose and have
feedback to a valve or other mechanism in the nebulizer to allow
activation of air flow, such as for later activation by inhalation.
The nasopharyngeal airway (NPA) and its oral air flow also aid to
pull the drug into the lungs. For example, it may be possible for
micro dosages of medicine to be given with nasal respiratory rates
in 60's/minute. The pediatric nebulizer could be designed to
release every third SNIP. The pressure from the NPA may be used to
activate the pediatric pacifier nebulizer to release medicine. The
SNIP inspiration pressure may be an aid in medicine delivery. A
cough depresses the tongue, which is in the way with medicine
inspiration delivery. The nebulizer as disclosed in accordance with
a non-limiting example will bypass that obstacle. The SNIP
inspiration pressure could activate the release of nebulized
medicine.
[0156] When using SNIP in a pediatric nebulizer, the frequency
modulation of a motor pattern may occur as part of a sensory
feedback loop and provide the central pattern generator (sCPG) with
information about the phase of the motor behavior. The
non-nutritive suck occurs and the SNIP follows, which releases the
medicine. The SNIP activation of the pacifier nebulizer is
advantageous and confirms the nasopharyngeal airstream significance
and when used intranasally with the nozzle/venturi and with a micro
feedline. SNIP could activate from the back of the nose and could
be advantageous over use of a face mask.
[0157] For purpose of technical instruction, there now follows a
general description of physiology for the involuntary reflex cough
test (iRCT), which activates the Nucleus Ambiguus, which is also
disclosed in some of the incorporated by reference patent
applications. The nebulizer with the flow sensing function is
adapted for measuring both voluntary cough and involuntary reflex
cough, such as explained in the incorporated by reference patent
applications. The iRCT selectively activates the Medial Motor Cell
Column (MMCC) of the spinal cord rather than the (Lateral) LMCC to
fire muscles embryologically predetermined to be involuntary cough
activated muscles in the pelvis. In the past, urologists did not
selectively activate MMCC without overtly activating the LMCC.
Magnetic stimulation or electrical spinal cord stimulation activate
both cell columns and thus it is not possible to sort out pathology
with these. Magnetic stimulation or other approaches from CNS
activation set off both columns.
[0158] The pelvic muscles that typically are activated with MMCC
cough activation include the lumbar-sacral L5/S1 paraspinal axial
musculature, which facilitates inpatient continence screening. An
example is through MMCC iRCT muscle activation, obtaining L5/S1
paraspinal firing but not L5/S1 lateral gastrocnemius activation
because the gastroc muscles are limb muscles activated primarily
through the LMCC.
[0159] The L-S paraspinals are easier to access with a large pad
placed above the sacrum on the midline that contains active,
reference and ground combined. It is not important to determine
lateralization of the activity like needle EMG for radiculopathy,
but only if activation occurs reflexively where the onset latency
is under the pressure activation of the abdomen such as the Levator
Ani. This is a poor muscle for these purposes because people train
it to activate and set their pelvis if the person senses any
intra-abdominal pressure elevation. Also, it is difficult to get
pads to stick to that area with hair, perspiration, fungal
infections or bowel/bladder incontinence present, and other
factors.
[0160] Some examples have been developed and studied, including a
normal CNS patient with Lumax bladder and bowel catheters and pads
at L5/S1 paraspinals and a separate EMG machine and electrodes at
the pelvic floor in a standard 3:00 and 9:00 o'clock set-up to
demonstrate simultaneous involuntary activation with iRCT. This
sets off the pelvic floor muscles. Thus, normal airway protection
data is obtained and normal CNS data to L1 (where spinal cord
ends). The set-up includes a complete T12 that cannot void and
needs intermittent catheterization with the same set up, thus
demonstrating data for normal airway but no L5/S1 EMG activation by
MMCC with all the other data necessary to prove an unsafe bladder
by the algorithm. A quadriplegic can demonstrate abnormal airway
protection and abnormal EMG activation at both paraspinal and
pelvic floor muscles with unsafe bladder measurements that follow
the algorithm.
[0161] It should be understood that iRCT is an involuntary maneuver
that activates embryologically predetermined muscles for airway
protection and continence that travel primarily through the MMCC in
the spinal cord. Different varieties of lesions are captured and
determined with summated interval data approach for general
screening purposes.
[0162] It is known that the laryngeal cough reflex (LCR) is a
strong brainstem-mediated reflex that protects the upper airway by
preventing aspiration, or the entrance of secretions, food, and/or
fluid into the airway below the level of the true vocal cords (rima
glottidis), through elicitation of an involuntary cough. The LCR is
activated through the stimulation of cough receptors in the
vestibule of the larynx. One way this is achieved is through the
inhalation of chemostimulants, such as tartaric acid. Studies have
shown that if the LCR is intact, the subject will involuntarily
cough (normal LCR) upon inhaling a solution containing TA.
[0163] In one non-limiting example, the iRCT involves the
inhalation of a nebulized 20% normal saline solution of L-TA
(Tartaric Acid). Subjects are asked to perform 1 to 3 effective,
full inhalations (about 15-20 second exposure by mouth for tidal
breathing wearing a nose clip) from a standard jet nebulizer with
at least 50 psi from an oxygen wall unit or tank that produces an
average droplet diameter of 1 to 2 microns or less. The nebulizer
output is 0.58 mL/min. The initiation of an involuntary cough
reflex after any one of the inhalations is the end point of the
procedure.
[0164] Nebulized TA is a chemical tussive that stimulates irritant
receptors in the mucosa of the laryngeal aditus. Mild irritation of
these receptors results in nerve impulses being conveyed by the
internal branch of the superior laryngeal nerve (ibSLN) to bulbar
centers of the brainstem. This nerve constitutes the afferent
sensory component of the LCR arc. The efferent component of the LCR
is mediated through the vagus, phrenic, intercostals and
thoracoabdominal nerves.
[0165] Inhaled TA is selective in stimulating rapidly adapting
("irritant") receptors (RARs), in the supraglottic region. In
humans, bilateral anesthesia of the ibSLN abolishes TA-induced
cough and permits tidal breathing of the nebulized vapor without
coughing, supporting the idea that the RARs are responsible for
TA-induced cough.
[0166] The physiological response from inhalation of TA in a normal
subject is abrupt, forceful coughing of short duration. Using a 20%
solution of inhaled nebulized TA is a safe, reliable way to assess
the sensation in the supraglottic laryngeal region and subsequently
the neurologic circuitry of the LCR. In addition, the ability of
the iRCT to predict the integrity of the protective LCR in subjects
with stroke has been studied.
[0167] A 20% solution of TA as an aerosol causes cough by
stimulating sensory nerves in and under the laryngeal epithelium.
These nerves have been identified histologically, and the reflexes
they cause have been identified. The sensory nerves can be
stimulated by both non-isosmolar and acid solutions. Tartaric acid
may act in both ways, but the balance between them is
uncertain.
[0168] The nerves are stimulated by the opening of membrane
channels in the nerve terminals. More than 20 categories of
channels have now been identified, the opening of which will allow
calcium flow into the nerve (and also sodium, with exit of
potassium), with the result that an action potential is set up,
which travels to the brainstem in the central nervous system (CNS),
and reflexively induces cough.
[0169] Several different types of sensory nerve ending in the
larynx have been identified that may mediate cough and other
defensive reflexes. They have been extensively studied, mainly in
experimental animals by recording the action potentials in their
nerve fibers. The probable candidates for cough are the RARs or
`irritant` receptors. These are highly sensitive to mechanical
stimuli, to hyperosmolar solutions, and to acids.
[0170] Once stimulated, the sensory nerves will induce a variety of
defensive reflexes, which protect the lungs from invasion of
harmful material. These include cough (an inspiration, followed by
a forced expiration against a closed glottis, followed by opening
of the glottis with an expiratory blast); the laryngeal cough
expiratory reflex (LCER, a powerful expiratory effort with the
glottis open); and the glottal closure reflex. In some instances a
reflex apnea can be produced. The balance of these reflexes may
depend on the nature and the strength of the stimulus. In the case
of TA, the LCER seems to be dominant, possibly followed by glottal
closure, and the pathophysiological advantage of this response in
preventing aspiration is obvious.
[0171] There now follows an analysis and test results in greater
detail that explain the advantageous use of the involuntary reflex
cough test (iRCT) for investigating and diagnosing not only SUI,
but also physiological abnormalities such as neurologic
deficiencies. The nebulizer as described can be used in conjunction
with testing. It should be understood that there are differences
between normal and neurological patients.
[0172] The EMG from the parineal muscles respond almost
simultaneously to the onset of the voluntary cough because the
patient does not want to leak. With the involuntary reflex cough
test, on the other hand, the fast fibers that are set off reach the
abdominal muscles quickly, such as in 17 milliseconds as an
example. The patient is not able to set their pelvis. In some of
the graphs reflecting urodynamic testing as will be described, it
is evident that the onset of the EMG activity does not happen at
the same time the pressure rises. Some people that have neuropathy,
for example, spinal stenosis or nerve injury (even if it is mild),
have a situation that prevents the reflexes from closing before the
pressure has changed to push on the bladder. It is not possible to
obtain this diagnostic tool methodology unless the involuntary
cough reflex test is accomplished. When the involuntary reflex
cough test is accomplished, it is possible to demonstrate a latency
delay and show that the pathophysiology is a neuropathic problem
rather than a structural problem. It is possible to separate the
pathophysiology using the involuntary reflex cough test and
methodology as described.
[0173] In one example, a female patient could have a weak spinal
cord and her physiology is normal. This patient may not leak during
the test, but the patient cannot protect her airway. Thus, using
the methodology apparatus and system associated with the
involuntary reflex cough test, in accordance with non-limiting
examples, it is possible not only to diagnose an unprotected
airway, but also to diagnose normal bladder physiology, including
the neurophysiology to the patient's sphincter closure process.
This is advantageous because it is then possible to determine when
someone cannot protect their airway, even though they may have a
normal bladder. Conversely, there are patients with a normal
airway, but cannot control their bladder. This process and system
as described is able to make that diagnosis and thus the
involuntary reflex cough test is an advantageous medical diagnostic
tool. For example, it is possible to have a patient with a poorly
functioning bladder and normal airway and use of the test allows a
doctor to find lower urinary tract symptoms and neuropathology. It
becomes possible to diagnose a level of lesion in a patient with a
full comprehensive neurologic examination using the involuntary
reflex cough test, methodology and apparatus as described.
[0174] As will be described in detail later, the various components
such as the nebulizer, one or more catheters, any pads for the
paraspinal muscles when EMG is used, and drug as part of the
nebulizer are inserted in a kit for use at the clinic, hospital or
setting. Those components can be discarded after use. The handheld
device, of course, will be used again. Use of the kit provides a
clinician, doctor or other medical professional the readily
available diagnostic tool to determine if a patient has a
questionable airway and determine bladder physiology at the same
time, all with the use of the one kit.
[0175] A kit that is marketed for the iRCT diagnostic tool could
include the nebulizer and its drug as TA in one example and one or
more pads for the electrodes at the paraspinal and use with EMG.
The pad may only be necessary for stress incontinence
determinations. A catheter is included in another kit example for
use in measuring airway and intra-abdominal pressure. In one
non-limiting example, a pad can be placed on a catheter to
determine urine leakage and aid in determining stress incontinence.
Pressure data is sent to the handheld device in some examples.
Obtaining any EMG values from the paraspinal in conjunction with
the urology analysis is advantageous. It is possible in one example
to measure pressure from a bladder catheter and determine at the
same time EMG signals using the EMG electrodes at the L5/S1 in
conjunction with the measured involuntary reflex cough test and
urology catheter sensing. This is advantageous compared to placing
electrodes at the perineal muscles on each side of the
sphincter.
[0176] It has been found that EMG signals obtained from the
perineal muscles have EMG activity from the non-involuntary
muscles, i.e., the voluntary muscles blacking out and making
analysis difficult because of the signal interference. When the
electrodes are placed at the back at the L5/S1 junction, on the
other hand, there is nothing else but the paraspinal muscles. It is
bone below on each side at the L5/S1 junction. The electrical
impulses can be obtained that determine the number of cough
impulses coming down through the patient. This is accomplished even
if a person has much adipose. The electrode pad used at the L5/S1
junction, in one non-limiting example, typically has an active
reference and ground. A pad holds this active reference and ground
and the leads as the active reference and ground are plugged into
the handheld device (or wireless sensing device in another example)
and transmit data to the processor. At least one catheter is also
plugged into the handheld device (or wireless sensing device) and
measures bladder pressures. A rectal catheter can also be used in
some examples. The processor receives EMG signals and determines
when the cough event is over.
[0177] The involuntary coughs are not hidden by interference when
measured from the lower back at the paraspinals as described. This
allows a clinician to determine coughs from the bladder when the
EMG located at the L5/S1. In one aspect, the area under curve and
the average pressure is determined for the cough event
corresponding to the involuntary reflex cough test. When this
involuntary component of the cough ends, in one example, it becomes
silent EMG activity for a period of time. The pressures are at
baseline for a period of time, which corresponds in one example to
an inhalation. The involuntary component is over.
[0178] Sometimes with the involuntary reflex cough test, the cough
occurs six times without breathing, but when the patient stops to
breathe, the event is over. Using the programming applied with the
processor in the handheld device, it is possible to calculate the
variables inside the wave as to the involuntary cough and determine
airway protection capability. Thus, it is possible to determine and
measure cough by defining through appropriate data processing the
involuntary cough event compared to the whole cough epoch. For
example, a patient could cough ten times, but only the first four
are part of the involuntary cough event. The coughs after that
event are not part of the epoch.
[0179] The programming includes algorithm branches resulting in a
conclusion of unsafe bladder based on the data analysis. It is
possible to calculate from the waveforms information necessary for
assessing airway protection ability. It should be understood that
taking the EMG from the L5/S1 is also a better situation for the
doctor or clinician, and the patient, since it is more acceptable
in a hospital, outpatient or inpatient setting. The doctor or
clinician does not have to bend down or stoop and look near the
crotch area and place pads since the EMG can now be taken from the
paraspinals. Also, the placement of pads and electrodes at the
paraspinals is advantageous when patients are standing. If pads are
placed at the perineal area, sweat and other problems could cause
those pads to become loose and good signals may not be obtained.
Also, it should be understood that the perineal muscles do not fire
involuntarily. The sphincter may fire involuntarily, but that would
create more noise as noted before. Electrodes are not placed at the
vagina, but are placed at the paraspinal area instead.
[0180] This information obtained from iRct and the EMG taken at the
paraspinals allows the doctor or clinician to obtain data leading
directly to a diagnosis. For example, some patients that have
urinary stress incontinence may have a normal airway in this
analysis. It has been found by experimentation that the normal
airway is about 50 centimeters water average intra-abdominal
pressure. It should be understood that the vesicular pressure
(bladder pressure) can track intra-abdominal pressure and terms are
often similar and used together. "Bladder" or intravesicular
pressure is often used to determine and equate with intra-abdominal
pressure. The two are sometimes used interchangeably. Stress
urinary incontinence and/or bladder physiology can be diagnosed.
The system and method as described leads directly to diagnosis.
Fifty centimeters average intra-abdominal pressure over time has
been found to correspond to an involuntary reflex cough test normal
airway. Thus, the standard deviations or other percentages from
that value are used in one non-limiting example to determine an
abnormal airway. In a conducted study, the actual value is
determined to be about 50.6 centimeters water as compared to
voluntary cough values of about 48 centimeters of water. In an
outpatient setting, it is possible to have the nebulizer (and drug)
and only a pad and test SUI. In hospitalized patients or inpatient
settings, this combination is used to measure airway and bladder
physiology and the test combination includes a catheter.
[0181] It should be understood that the involuntary cough reflex
test (iRCT) gives a higher pressure average than obtained using a
voluntary cough test. The involuntary cough reflex test is thus a
valuable medical diagnostic tool. In one example, four variables
are significant in this analysis. These variables include: (1)
duration of the event; (2) average intra-abdominal pressure of the
event; (3) peak intra-abdominal pressure (max) of the event; and
(4) area under the curve. Using these four variables, it is
possible to process the received data and obtain a specific
diagnosis that could not otherwise be obtained without the use of
the involuntary reflex cough test. Individual deficits in a
specific variable or combination of variables are used to
characterize specific diseases and problems and useful as a medical
diagnostic tool.
[0182] This application is related to copending patent applications
entitled, "METERED DOSE NEBULIZER," and "METERED DOSE ATOMIZER,"
which are filed on the same date and by the same assignee and
inventors, the disclosures which are hereby incorporated by
reference.
[0183] Many modifications and other embodiments of the invention
will come to the mind of one skilled in the art having the benefit
of the teachings presented in the foregoing descriptions and the
associated drawings. Therefore, it is understood that the invention
is not to be limited to the specific embodiments disclosed, and
that modifications and embodiments are intended to be included
within the scope of the appended claims.
* * * * *