U.S. patent application number 14/147111 was filed with the patent office on 2014-06-26 for ventilator apparatus.
This patent application is currently assigned to Allied Healthcare Products, Inc.. The applicant listed for this patent is Allied Healthcare Products, Inc.. Invention is credited to Kevin D. Kroupa.
Application Number | 20140174443 14/147111 |
Document ID | / |
Family ID | 40094717 |
Filed Date | 2014-06-26 |
United States Patent
Application |
20140174443 |
Kind Code |
A1 |
Kroupa; Kevin D. |
June 26, 2014 |
VENTILATOR APPARATUS
Abstract
One or more embodiments of the presently described invention
provides a ventilator including a timing device, an electric power
source and a flow control device. The timing device is
electronically controlled and is capable of controlling a period of
time that a fluid is delivered to a patient. The timing device can
control this period of time using a solenoid. The flow control
device controls a rate of flow that the fluid is delivered to the
patient. The flow control device can control the rate of flow using
a plurality of orifices. The timing device and flow control device
are separate from one another and each is capable of being operated
independent of the other.
Inventors: |
Kroupa; Kevin D.; (Ballwin,
MO) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Allied Healthcare Products, Inc. |
St. Louis |
MO |
US |
|
|
Assignee: |
Allied Healthcare Products,
Inc.
St. Louis
MO
|
Family ID: |
40094717 |
Appl. No.: |
14/147111 |
Filed: |
January 3, 2014 |
Related U.S. Patent Documents
|
|
|
|
|
|
Application
Number |
Filing Date |
Patent Number |
|
|
11810214 |
Jun 5, 2007 |
8656913 |
|
|
14147111 |
|
|
|
|
Current U.S.
Class: |
128/204.21 |
Current CPC
Class: |
A61M 16/0858 20140204;
A61M 16/107 20140204; A61M 16/209 20140204; A61M 2205/18 20130101;
A61M 16/0051 20130101; A61M 16/024 20170801; A61M 2205/581
20130101; A61M 16/206 20140204; A61M 2205/3331 20130101; A61M
16/204 20140204; A61M 16/202 20140204; A61M 2205/502 20130101; A61M
2016/0027 20130101; A61M 2016/0039 20130101; A61M 16/208 20130101;
A61M 2205/8206 20130101; A61M 2205/583 20130101 |
Class at
Publication: |
128/204.21 |
International
Class: |
A61M 16/20 20060101
A61M016/20; A61M 16/00 20060101 A61M016/00 |
Claims
1. A ventilator apparatus comprising: an electrically powered
timing control device configured to control a period of time that a
fluid is delivered to a patient during inspiratory time periods,
the timing control device including a solenoid and an outlet, the
timing control device configured to be adjusted to change the
inspiratory time periods that the fluid is delivered to the
patient, the timing device configured to move the solenoid to a
position to block flow of the fluid to the patient during times
between the inspiratory time periods; and a flow control device
configured to control a rate of flow that the fluid is delivered to
the patient, the flow control device including plural orifices
configured to be adjusted to change the rate of the flow that the
fluid is delivered to the patient during the inspiratory time
periods.
2. The ventilator apparatus of claim 1, wherein the timing control
device is disposed upstream of the flow control device along a
pathway that the fluid flows to the patient.
3. The ventilator apparatus of claim 1, wherein the timing control
device is configured to control durations of the inspiratory time
periods by actuating the solenoid to an open position or a closed
position, the inspiratory time periods beginning when the solenoid
is actuated to the open position and ending when the solenoid is
actuated to the closed position, the solenoid configured to permit
flow of the fluid to the patient when the solenoid is at the open
position and to prevent the flow of the fluid when in the closed
position.
4. The ventilator apparatus of claim 1, wherein orifices have
different diameters.
5. The ventilator apparatus of claim 1, wherein a volume of the
fluid provided to the patient by the timing control device and the
flow control device is capable of being altered by manually
adjusting one or more of the inspiratory time periods using the
timing control device or by manually adjusting the rate of flow
using the flow control device.
6. The ventilator apparatus of claim 1, wherein the flow control
device includes an inlet that is configured to be fluidly coupled
with the timing control device to receive the fluid from the timing
control device, a first outlet fluidly configured to be fluidly
coupled with the patient to deliver the fluid to the patient, and a
different second outlet, and further comprising a patient airway
pressure sensor configured to be fluidly coupled with the second
outlet of the flow control device, the pressure sensor configured
to measure a pressure of the fluid delivered to the patient through
the first outlet of the flow control device based on at least some
of the fluid that flows to the pressure sensor through the second
outlet of the flow control device.
7. The ventilator apparatus of claim 6, further including at least
one alarm communicatively coupled with the pressure sensor and
configured to provide at least one of a visual notification or an
audible notification when at least one of several alarm events
occurs.
8. The ventilator apparatus of claim 7, wherein the alarm events
include one or more of: the pressure of the fluid exceeding an
upper airway pressure threshold; the pressure of the fluid falling
below a lower airway pressure threshold for at least a
predetermined period of time; or the pressure at which the fluid is
supplied by the fluid source falling below a source pressure
threshold.
9. The ventilator apparatus of claim 6, wherein the second outlet
of the flow control device does not direct the fluid to the
patient.
10. A ventilator apparatus comprising: an inspiratory timing
control device configured to be fluidly coupled with a patient
airway connection that delivers a fluid to a patient, the timing
control device configured to start and stop a flow of the fluid to
the patient through the patient airway connection, the timing
control device configured to receive manual input from an operator
that directs the timing control device when to start or stop the
flow of the fluid to the patient; a flow control device configured
to be fluidly coupled with the timing control device and with the
patient airway connection, the flow control device having a first
outlet configured to be fluidly coupled with the patient airway
connection, plural orifices having different sizes, and a different
second outlet, the flow control device configured to receive the
fluid from the timing control device and control a rate of the flow
of the fluid to the patient through the first outlet and the
patient airway connection; and a patient airway pressure sensor
fluidly coupled with the second outlet of the flow control device,
the patient airway sensor configured to receive at least some of
the fluid passing through one or more of the orifices of the flow
control device and exiting the flow control device through the
second outlet, the pressure sensor configured to measure a pressure
of the fluid delivered to the patient based on the fluid received
from the second outlet.
11. The ventilator apparatus of claim 10, wherein the timing
control device is configured to calculate a time period required to
deliver a desired tidal volume of the fluid to the patient at a
manually selected rate of fluid flow based on the manual input.
12. The ventilator apparatus of claim 10, wherein the timing
control device is powered by one or more replaceable batteries.
13. The ventilator apparatus of claim 10, wherein the timing
control device is configured to start and stop the flow of the
fluid to the flow control device at a point upstream from the
orifices in the flow control device.
14. The ventilator apparatus of claim 10, wherein the timing
control device includes a solenoid and an outlet, the timing
control device configured to move the solenoid to a position to
block flow of the fluid to the patient with the fluid flowing
through the timing control device directed away from the patient
and out of the timing control device through the outlet of the
timing control device when the solenoid blocks the flow of the
fluid.
15. A method of providing a ventilator apparatus, the method
comprising: fluidly coupling an inspiratory timing control device
with a patient airway connection that delivers a fluid to a
patient, the control device configured to start and stop a flow of
the fluid to the patient through the patient airway connection;
fluidly coupling a flow control device with the timing control
device and with the patient airway connection, the flow control
device having a first outlet configured to be coupled with the
patient airway connection and plural orifices having different
sizes, the flow control device configured to receive the fluid from
the timing control device and control a rate of the flow of the
fluid to the patient through the first outlet and the patient
airway connection; and fluidly coupling a patient airway pressure
sensor with the flow control device, the patient airway sensor
configured to receive at least some of the fluid passing through
one or more of the orifices of the flow control device and exiting
the flow control device, the pressure sensor measuring a pressure
of the fluid delivered to the patient based on the fluid received
from the second outlet.
16. The method of claim 15, wherein the timing control device is
fluidly coupled with the patient airway connection such that at
least some of the fluid is directed out of the timing control
device and away from the patient through an outlet in the timing
control device when the timing control device stops the flow of the
fluid to the patient through the patient airway connection.
17. The method of claim 15, wherein fluidly coupling the flow
control device includes fluidly coupling the flow control device
such that a desired tidal volume is delivered to the patient at a
selected rate of fluid flow through the flow control device, the
flow control device configured to calculate a time period required
to deliver the desired tidal volume at the selected rate of fluid
flow based on the manual input and controlling a start and end to
the time period by moving a solenoid between first and second
positions.
18. The method of claim 15, wherein fluidly coupling the flow
control device includes fluidly coupling the flow control device
downstream of the timing control device such that the timing
control device is configured to start and stop the flow of the
fluid at a point upstream from the plurality of orifices in the
flow of the fluid through the flow control device.
19. The method of claim 15, further including providing at least
one of a visual and audible notification when at least one of
plural alarm events occurs, the alarm events including: the
pressure in the patient airway connection exceeding an upper airway
pressure threshold, the pressure in the patient airway connection
falling below a lower airway pressure threshold, the pressure at
which the fluid is supplied by the fluid source falling below a
source pressure threshold, a level of a power source of the timing
control device falling below a power source threshold.
20. The method of claim 15, wherein further comprising
electronically controlling a period of time that the fluid is
supplied to the patient using the timing control device by moving a
solenoid between an open position and a closed position.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation of U.S. patent
application Ser. No. 11/810,214, which was filed on 5 Jun. 2007,
and is entitled "Ventilator Apparatus" (the "'214 application").
The entire disclosure of the '214 application is incorporated by
reference.
BACKGROUND
[0002] The presently described invention generally relates to
artificial breathing devices. More specifically, embodiments of the
presently described technology provide an improved ventilator
apparatus.
[0003] Emergency ventilators are devices that can partially or
entirely replace bag mask resuscitation devices as a manner of
providing mechanical ventilation in an emergency environment.
Existing devices can permit the user, such as an EMT or paramedic,
to set a tidal volume ("V.sub.T") and breaths per minute ("BPM")
and little more, if anything. These existing devices are usually
driven or powered by oxygen under pressure flowing from portable
compressed oxygen cylinders.
[0004] Existing hospital ventilators can be difficult to use by
individuals who are not as highly trained as respiratory
therapists. In addition, existing ventilators can be very
expensive. Given new requirements on hospitals to prepare for
events such as terrorist attacks, natural disasters or an outbreak
of disease such as avian flu adding large numbers of ventilators
can be a large financial burden and having adequate trained
staffing during such a crisis can be a bigger problem.
[0005] Existing ventilators typically are controlled by a complex
electronic system ("electric-only ventilators") or by a complex
system of pneumatics ("pneumatically-only ventilators"). With
respect to the electric-only ventilators, these devices suffer from
many drawbacks. For example, electric-only ventilators usually
include a fragile electronic system of circuits used to control
inspiration time and fluid flow through the ventilator. As a
result, these types of ventilators tend to be relatively fragile
when compared to pneumatically controlled ventilators. As emergency
ventilators are typically used in emergency situations, the
durability of the ventilators is of considerable importance.
[0006] Electric-only ventilators also usually include electronic
circuits to control and drive a complex proportioning valve to set
the fluid flow through the ventilator. Controlling such a valve
typically requires a considerable amount of electric power. As a
result, electric-only ventilators are usually powered by a lead
acid or lithium ion battery. These types of batteries are
relatively heavy and are not easily accessible during emergency
situations. That is, in an emergency situation, a supply of lead
acid or lithium ion batteries may not be readily available.
Moreover, existing electric-only ventilators can deplete a lead
acid or lithium ion battery fairly quickly. Many ventilators can
deplete such a battery in under eight hours.
[0007] In addition, use of such a valve typically requires one or
more position feedback circuits to achieve the accuracy required of
a ventilator. The added complexity of position feedback circuits
only adds to the cost of these types of ventilators.
[0008] With respect to pneumatic-only ventilators, these devices
tend to be more durable than electric-only ventilators (most likely
because they do not include the complex circuitry of electric-only
ventilators). But, pneumatic-only ventilators usually must be very
closely monitored during operation. These ventilators use a system
of pneumatics powered by the fluid being delivered to the patient
to control timing and flow of the fluid through the ventilator.
That is, the ventilators use a build up of pressure in the device
as a timing function. With small leaks and/or changes in the source
fluid pressure, the timing function and thus the ventilator can
suffer from poor precision and/or accuracy. Pneumatic ventilators
cost less than complex electronic ventilators but still cost
several thousand dollars due to the pneumatic components
required.
[0009] While some more inexpensive ventilators have been introduced
into the market, these ventilators also suffer from drawbacks. For
example, one or more of these ventilators do not include any
feedback to a user of the ventilator. That is, a user cannot
determine the BPM or volume of fluid being delivered to a patient.
The user must externally calculate such information using, for
example, a stopwatch to determine the total time of inspiration.
With such ventilators, a single user cannot assist more than one
person in emergency situations. The user must stay with a
ventilator to continually monitor its delivery of fluid to a
user.
[0010] Thus, a need exists for an improved ventilator that is
cheaper to manufacture, more durable, more precise and more
accurate.
BRIEF DESCRIPTION
[0011] One or more embodiments of the presently described invention
provides a ventilator including a timing device, an electric power
source and a flow control device. The timing device is capable of
controlling a period of time that a fluid is delivered to a
patient. The timing device can control this period of time using a
solenoid. The flow control device controls a rate of flow that the
fluid is delivered to the patient. The flow control device can
control the rate of flow using a plurality of orifices.
[0012] One or more embodiments of the presently described invention
also provides a method for providing improved control of a
ventilator. The method includes the steps of electronically
controlling a period of time that a fluid is delivered to a patient
using a solenoid, controlling a rate of flow that the fluid is
delivered to the patient by directing the fluid through at least
one of a plurality of orifices having a plurality of different
diameters, and providing a volume of the fluid to the patient by
permitting the fluid to pass through the ventilator at the rate of
flow for the period of time.
[0013] One or more embodiments of the presently described invention
also provide a ventilator including an inspiratory timing control
device and a plurality of orifices. The timing control device is
configured to start and stop a flow of fluid through the ventilator
and is powered by at least one battery. The orifices include
different diameters and are configured to control a rate of fluid
flow through the ventilator.
BRIEF DESCRIPTION OF THE DRAWINGS
[0014] FIG. 1 illustrates a diagram of a ventilator system in
accordance with an embodiment of the presently described
invention.
[0015] FIG. 2 illustrates a view of the ventilator in accordance
with an embodiment of the presently described invention.
[0016] FIG. 3 illustrates a view of the power source chamber of the
ventilator device in accordance with an embodiment of the presently
described invention.
[0017] FIG. 4 illustrates a view of inside the ventilator in
accordance with an embodiment of the presently described
invention.
[0018] FIG. 4A illustrates a view of one half of the inside of the
ventilator in accordance with an embodiment of the presently
described invention.
[0019] FIG. 4B illustrates a view of the other half of the inside
of the ventilator in accordance with an embodiment of the presently
described invention.
[0020] FIG. 5A illustrates a perspective view of a back side and a
top of a flow control device in accordance with an embodiment of
the presently described invention.
[0021] FIG. 5B illustrates a perspective view of a front side and a
top of a flow control device in accordance with an embodiment of
the presently described invention.
[0022] FIG. 5C illustrates a plan view of a side of a flow control
device in accordance with an embodiment of the presently described
invention.
[0023] FIG. 5D illustrates a plan view of the back side of a flow
control device in accordance with an embodiment of the presently
described invention.
[0024] FIG. 6 illustrates a cross-sectional view of the flow
control device in accordance with an embodiment of the presently
described invention.
[0025] FIG. 7 illustrates a schematic diagram of a solenoid in an
open position in accordance with an embodiment of the presently
described invention.
[0026] FIG. 8 illustrates a schematic diagram of a solenoid in a
closed position in accordance with an embodiment of the presently
described invention.
[0027] FIG. 9 illustrates a flowchart of a method for using an
improved ventilator in accordance with an embodiment of the
presently described invention.
[0028] FIG. 10A illustrates a view of tubing capable of being used
as a patient circuit connection in accordance with an embodiment of
the presently described invention.
[0029] FIG. 10B illustrates a view of a plurality of tubing
sections forming a continuous connection in accordance with an
embodiment of the presently described invention.
[0030] FIG. 11 illustrates an orifice plate in accordance with an
embodiment of the presently described invention.
[0031] FIG. 12 illustrates an exploded view of the ventilator in
accordance with an embodiment of the presently described
invention.
[0032] FIG. 13 illustrates a cross-section view of the flow control
device in accordance with an embodiment of the presently described
invention.
[0033] The foregoing summary, as well as the following detailed
description of certain embodiments of the presently described
technology, will be better understood when read in conjunction with
the appended drawings. For the purpose of illustrating the
presently described technology, certain embodiments are shown in
the drawings. It should be understood, however, that the presently
described technology is not limited to the arrangements and
instrumentality shown in the attached drawings.
DETAILED DESCRIPTION
[0034] FIG. 1 illustrates a diagram of a ventilator system 100 in
accordance with an embodiment of the presently described invention.
Ventilator system 100 includes a ventilator device 110, a fluid
source 120, a fluid source connection 130, a patient circuit
connection 140, a delivery device 150, an output valve 170 and an
input or inlet valve 180. As shown in FIG. 1, ventilator system 100
is connected to a patient 160.
[0035] Fluid source 120 is connected to ventilator 110 by way of
fluid source connection 130. Ventilator 110 is connected with
delivery device 150 by way of patient circuit connection 140.
Delivery device 150 is connected to patient 160. In an embodiment,
delivery device 150 includes an exhalation port 155 and/or a
one-way valve 157. One-way valve 157 can include a valve that only
permits the flow of fluid in one direction through valve 157 and,
once the pressure of the fluid flowing through valve 157 drops a
sufficient amount, valve 157 closes. For example, one-way valve 157
can comprise a duck valve or duck bill valve.
[0036] Fluid source 120 can include any container holding a fluid
that is to be delivered to patient 160 using ventilator 110. For
example, fluid source 120 can include a canister of pressurized
gas. In an embodiment, fluid source 120 includes a pressurized
canister of oxygen. In another embodiment, fluid source 120
includes a 280 kPa (40.6 psi) to 600 kPa (87.0 psi) oxygen
canister. In another embodiment, fluid source 120 includes a 344
kPa (50.0 psi oxygen canister with a minimum of 40 liters per
minute flow capacity. In another embodiment, fluid source 120
includes a high flow air and oxygen blender. In an embodiment,
fluid source 120 includes a diameter index safety system ("DISS")
fitting. The fluid canisters may contain gas at high pressures such
as 2000 or higher and deliver gas at 280 kPa (40.6 psi) to 600 kpa
(87.0 psi) by using a fluid regulator to reduce the pressure.
[0037] Fluid source connection 130, or patient airway connection
130, includes any tube or hose capable of connecting to fluid
source 120 and inlet valve 180. For example, fluid source
connection 130 can include a supply hose made of polyvinyl chloride
("PVC"). In another example, fluid source connection 130 can
include a supply hose made of rubber.
[0038] Patient circuit connection 140 includes any tube or hose
capable of connecting to output valve 170 and delivery device 150.
For example, patent circuit connection 140 can include corrugated
tubing. The tubing can be manufactured from a material such as
ethylene-vinyl acetate ("EVA").
[0039] In an embodiment, the tubing used for patient circuit
connection 160 is a continuous piece that includes sections capable
of being separated from one another to form shorter pieces. For
example, patient circuit connection 160 can be separated at any
point approximately 6'' from any other point so that any length
that is an increment of 6'' can be made from the continuous
tube.
[0040] FIG. 10A illustrates a view of sectional tubing 930 capable
of being used as patient circuit connection 160 in accordance with
an embodiment of the presently described invention. FIG. 10B
illustrates a plurality of tubing sections 930 forming a longer,
continuous connection 160.
[0041] Delivery device 150 includes any apparatus, device or system
capable of receiving fluid from ventilator 110 via patient
connection circuit 140 and delivering or providing the fluid to
patient 160. For example, delivery device 150 can include an oxygen
mask or endotracheal tube. In an embodiment, delivery device 150
includes an oxygen mask with a 22 mm inside diameter. In another
embodiment, delivery device 150 includes an endotracheal tube with
a 15 mm outside diameter.
[0042] Output valve 170 includes any outlet, valve, connection or
opening capable of providing fluid communication between ventilator
110 and patient communication circuit 140. For example, output
valve 170 can include a valve providing a connection between
ventilator 110 and patient connection circuit 140 that permits
fluid to flow from ventilator 110 to patient connection circuit
140. In an embodiment, output valve 170 includes a 22 mm connection
valve. In an embodiment, output valve 170 includes an
anti-suffocation valve.
[0043] Input valve 180 includes any outlet, valve, connection or
opening capable of providing fluid communication between fluid
source connection 130 and ventilator 110. For example, input valve
180 can include a valve providing a connection between fluid source
connection 130 and ventilator 110 that permits fluid to flow from
fluid source connection 130 to ventilator 110. In an embodiment,
input valve 180 includes a DISS fitting. In an embodiment, input
valve 180 includes a filter. For example, input valve 180 can
include a 65 micron sintered bronze filter.
[0044] In operation, fluid source 120 and ventilator 110 are
connected to opposing ends of fluid source connection 130. Fluid
source connection 130 can be connected to input valve 180 attached
to ventilator 110.
[0045] Ventilator 110 and delivery device 150 are connected to
opposing ends of patient circuit connection 140. Patient circuit
connection 140 can connect to output valve 170 attached to
ventilator 110.
[0046] A user selects an inspiratory time ("I.sub.t"). The details
of how a user selects the inspiratory time are described below. In
short, a user employs one or more buttons on ventilator 110 to
select one of a plurality of inspiratory times. In an embodiment, a
user selects a one or two second inspiratory time. For example, a
user can select a one second inspiratory time for using ventilator
110 on a child or adult with a tidal volume requirement of 600 mL
or less. In another example, a user can select a two second
inspiratory time for using ventilator 110 on an adult with a tidal
volume requirement of more than 400 mL.
[0047] A user also selects breaths per minute ("BPM"). The details
of how a user selects the BPM are described below. In short, a user
employs one or more buttons on ventilator 110 to select one of a
plurality of BPMs. In an embodiment, a user selects a BPM from
eight to thirty. In an embodiment, the range of available BPMs can
be limited based on the inspiratory time selected by the user. For
example, for a one second inspiratory time, the range of available
BPMs can be eight to thirty or twelve to twenty. In another
example, for a two second inspiratory time, the range of available
BPMs can be eight to twenty or eight to twelve.
[0048] A user also selects a tidal volume ("T.sub.v"). The selected
tidal volume determines a rate of flow of fluid through ventilator
110 and/or delivered to patient 150. The details of how a user
selects the tidal volume are described below. In short, a user
employs a knob of ventilator 110 to select one of a plurality of
tidal volumes. In an embodiment, the available tidal volumes and
corresponding rate of flow is limited based on the selected
inspiratory time. For example, the tidal volume settings available
for a user to select and the corresponding rate of flow can be
limited to those shown in the below table:
TABLE-US-00001 Tidal Volume Setting ("T.sub.v") in mL Rate of Flow
in Liters per I.sub.t = 1 second I.sub.t = 2 seconds Minute ("LPM")
200 400 12 240 480 14.4 280 560 16.8 320 640 19.2 360 720 21.6 400
800 24 440 880 26.4 480 960 28.8 520 1040 31.2 560 1120 33.6 600
1200 36
[0049] The user then connects ventilator 110 to patient 160 using
patient connection circuit 140 and delivery device 150. Ventilator
110 then provides tidal volumes to patient 160 at the selected
BPMs. In an embodiment, if patient 160 begins to breathe
spontaneously or on his or her own, the anti-suffocation valve
included in output valve 170 permits ambient air to be pulled in
through valve 170. In another embodiment, a sensor capable of
detecting a spontaneous patient breath can be added to output valve
170. Such a sensor can detect a spontaneous breath by detecting
negative pressure in output valve 170. When negative pressure is so
detected, ventilator 110 then provides the selected tidal volumes
to patient 160 and adjusts the timing to continue at the selected
BPMs after the spontaneous breath is delivered.
[0050] In an embodiment, ventilator 110 includes a plurality of
alarms. For example, ventilator 110 can include one or more alarms
that become activated when a fluid or gas pressure in patient
connection circuit 130 (or patient airway connection 130) exceeds a
threshold (or upper airway pressure threshold), fluid or gas
pressure in patient connection circuit 130 (or patient airway
connection 130) falls below a threshold (or lower airway pressure
threshold), the pressure of the fluid or gas supplied by source 120
falls below a threshold (or source pressure threshold), and/or a
level of the power source for ventilator 110 falls below a
threshold (or power source threshold). Two or more of these
thresholds can be the same numeric value or can be different from
the other thresholds. The details on how these alarms function is
described in more detail below. Each alarm can include a visual
and/or audible notification such as a light and/or a buzzer. In an
embodiment, ventilator 110 can include a button or switch on
control panel 210 or an alarm panel 220 that stops one or more
activated alarms. For example, a button or switch similar to time
control buttons 216 or BPM control buttons 218 can be pressed to
dim a light or end a buzzer that is activated as an alarm. In an
embodiment, pressing the button or switch to stop the alarm
temporarily stops the alarm for a given time period. After the
given time period, the alarm will resume if the event for which the
alarm was first activated has not been remedied. In another
embodiment, pressing the button or switch to stop the alarm only
stops an audible alarm but does not stop any visual alarm.
[0051] In an embodiment, the threshold or upper airway pressure
threshold for the fluid or gas pressure in patient connection
circuit 130 is less than or equal to 52 cm H.sub.2O (5.1 kPa). That
is, the upper airway pressure threshold is no more than 52 cm
H.sub.2O (5.1 kPa). For example, the threshold can be 52 cm
H.sub.2O (5.1 kPa).
[0052] In an embodiment, ventilator 110 can include a safety
pressure relief mechanism. This mechanism can relieve pressure in
ventilator 110 when the internal pressure exceeds the upper airway
pressure threshold. The safety pressure relief mechanism can be
embodied in a pressure relief plate, spring and outlet port. For
example, the safety pressure relief mechanism can be embodied in
pressure relief plate 630, spring 635 and outlet port 640 described
below with respect to device 434 and FIG. 6.
[0053] In an embodiment, an alarm that occurs when the pressure in
patient airway connection 130 exceeds a threshold ends or is
cleared when a predetermined amount of time passes with the upper
airway pressure being lower than the threshold. In other words,
after the pressure in connection 130 exceeds the upper airway
pressure threshold, the alarm is activated and stays active (that
is, continues with an audible and/or visual notification to a
user). The alarm continues in its active state until the pressure
drops below the upper airway pressure threshold and stays below the
threshold for a predetermined amount of time. For example, if the
pressure drops below a threshold of 52 cm H.sub.2O (5.1 kPa) for at
25 seconds, the alarm ends or becomes cleared.
[0054] In an embodiment, the lower airway pressure threshold for
the fluid or gas pressure in patient connection circuit 130 is 5 cm
H.sub.2O (493 Pa). In addition, there can be a minimum time span at
which the fluid pressure in the patient connection circuit 130 must
be at or below the threshold before the alarm is activated. For
example, the alarm can be set not to activate unless the pressure
in patient connection circuit 130 is at or below 5 cm H.sub.2O (493
Pa) for at least 15 seconds.
[0055] In an embodiment, the alarm that is activated when the
pressure of the fluid or gas supplied by source 120 falls below a
threshold of 40 psi (275 kPa). In another embodiment, this
threshold is 38 psi (262 kPa). In addition, the alarm can remain
activated until this pressure rises above the predetermined
threshold for a predetermined amount of time. In an embodiment,
this amount of time is 15 seconds.
[0056] In an embodiment, the alarm that is activated when the level
of the power source for ventilator 110 falls below a threshold
becomes activated when a minimum amount of time of power is left in
the source. That is, the alarm is triggered when the power source
can only power ventilator 110 for a minimum amount of time. The
minimum amount of time can be calculated by determining the voltage
level remaining in the power source capable of operating ventilator
110 for the minimum amount of time. In an embodiment, this minimum
amount of time is two hours. In other words, this alarm is
activated when only two hours of battery power remains to power
ventilator 110. In another embodiment, the alarm is triggered when
the voltage remaining in the power source falls below a threshold.
For example, the alarm can be triggered when a predetermined amount
of voltage remains in one or more battery power sources. These
power source alarms can be deactivated or cleared when the power
source is replenished so that more than the predetermined minimum
amount of time or voltage remains in the power source.
[0057] In an embodiment, one or more of these alarms is a visual
indicator, such as a light. For example, an alarm can be a light
emitting diode ("LED") that is illuminated when the alarm is
activated and is not illuminated when the alarm is not activated.
In another embodiment, one or more of these alarms is an audible
notification. For example, an alarm can be a beep or repeated
beeping sound that occurs when the alarm is activated and is silent
when the alarm is not activated.
[0058] FIG. 2 illustrates a view of ventilator 110 in accordance
with an embodiment of the presently described invention. Ventilator
110 includes a control panel 210, an alarm panel 220, an on/off
switch 230, a tidal volume control knob 240 and a power source door
250.
[0059] Control panel 210 includes a BPM display window 212, an
airway pressure window 214, inspiratory time control buttons 216
(also referred to as inspiratory buttons 216) and BPM control
buttons 218 (also referred to as BPM buttons 218). While only two
buttons are shown for each of inspiratory buttons 216 and BPM
buttons 218, a larger number of buttons can be used for either set
of buttons in accordance with an embodiment of the presently
described invention.
[0060] Alarm panel 220 includes one or more visual indicators of
one or more alarms. In the embodiment shown in FIG. 2, alarm panel
220 includes three LEDs, one for each of the high airway pressure
alarm, the low source gas (or fluid pressure) alarm and the low
battery (or power source) alarm. In addition, one or more of the
LEDs can flash to indicate a low pressure alarm (such as when the
fluid or gas pressure in patient airway connection 130 falls and
stays below a threshold for a given amount of time. For example,
this time can be 15 seconds, but other times can be used.
[0061] FIG. 3 illustrates a view of a power source chamber 310 of
ventilator 110 in accordance with an embodiment of the presently
described invention. Power source chamber 310 is a recessed area of
ventilator 110 that is configured to hold and electrically connect
an electric power source to ventilator 110. In an embodiment,
chamber 310 can be accessed by removing power source door 250. For
example, power source chamber 310 can include a recess with
electrical connections or wires 520 for one or more power sources
320, as shown in FIG. 3.
[0062] In an embodiment, device 110 includes an electrical timing
system or device (described in more detail below) that is capable
of operating off of a relatively small amount of voltage or
current. For example, the electrical timing device can operate off
of 3.0 volts or less of direct current.
[0063] In an embodiment, power sources 320 include alkaline
batteries. For example, the electrical timing device can operate
off of the voltage or current supplied by two size "D" alkaline
batteries. By enabling the timing device to operate off of common
alkaline batteries, is becomes considerably more simple to find a
power source 320 for ventilator device 110 in an emergency
situation. In addition, existing ventilators use lead acid
batteries as electrical power sources. These batteries are large,
heavy and difficult to find when compared to alkaline batteries.
While two size "D" alkaline batteries can be used, other types and
combination of batteries can also be used. For example, a single
alkaline or lithium battery (or any other battery capable of
providing voltage), or any combination of batteries capable of
providing the minimum voltage required to operate ventilator 110
can be used. In an embodiment, ventilator 110 can be supplied with
three or less volts by one or more batteries. These volts can be
stepped up by a voltage step-up circuit. Alternatively, ventilator
110 can be supplied with more than three volts by one or more
batteries and not require any voltage step-up circuitry.
[0064] In an embodiment, power source(s) 320 enables the timing
device of ventilator 110 to operate for at least eight hours at
room temperature, assuming that a fluid source 120 does not expire
before the eight hours is completed. In a preferred embodiment,
power source(s) 320 enable the timing device to operate
continuously for at least eight hours at room temperature (again,
assuming fluid source 120 does not become depleted before then). In
a more preferred embodiment, two alkaline batteries (such as size
"D" alkaline batteries, for example) acting as power sources 320
enable the timing device to operate continuously for at least eight
hours at room temperature (again, assuming fluid source 120 does
not become depleted before then).
[0065] In an embodiment, power source(s) 320 enables the timing
device of ventilator 110 to operate for at least twelve hours at
room temperature, assuming that a fluid source 120 does not expire
before the twelve hours is completed. In a preferred embodiment,
power source(s) 320 enable the timing device to operate
continuously for at least twelve hours at room temperature (again,
assuming fluid source 120 does not become depleted before then). In
a more preferred embodiment, two alkaline batteries (such as size
"D" alkaline batteries, for example) acting as power sources 320
enable the timing device to operate continuously for at least
twelve hours at room temperature (again, assuming fluid source 120
does not become depleted before then).
[0066] In an even more preferred embodiment, power source(s) 320
enable the timing device to operate for at least forty-eight hours
at room temperature (again, assuming fluid source 120 does not
become depleted before then). In an even more preferred embodiment,
power source(s) 320 enable the timing device to operate
continuously for at least forty-eight hours at room temperature
(again, assuming fluid source 120 does not become depleted before
then). In an even more preferred embodiment, two alkaline batteries
(such as size "D" alkaline batteries, for example) acting as power
sources 320 enable the timing device to operate continuously for at
least forty-eight hours at room temperature (again, assuming fluid
source 120 does not become depleted before then). By "operating"
and "operate," it is meant that power source 320 provides
sufficient power to ventilator 110 so that ventilator 110 can
deliver one or more breaths to a patient 160.
[0067] In an embodiment, on/off switch 230 is used to activate or
deactivate circuit 514. That is, when switch 230 is pressed so as
to turn ventilator 110 "on," power is supplied to circuit 514 from
power source 320. Conversely, when switch 230 is pressed so as to
turn ventilator 110 "off," power is no longer supplied to circuit
514 from power source 320.
[0068] FIG. 12 illustrates an exploded view of ventilator 110 in
accordance with an embodiment of the presently described invention.
Ventilator 110 includes a plurality of panels 1210, 1220 and 1230,
a plurality of screws 1240, power source 320, a plurality of
electrical contacts 1250, two halves 400 and 500 of ventilator 11
housing, a plurality of clips 1260, output valve 170, an
anti-suffocation valve 1270, a plurality of washers 1280, a
pressure relief valve 1290, a screw cover 1212, an elbow fitting
1214, a ball and spring combination 435, a regulator connector
1216, circuit 514, flow control device 434, regulator 414,
input/inlet valve 180, solenoid 416, Y-connector 420, solenoid barb
436, a decal 1218, knob 240, control panel 210, alarm panel 220 and
an o-ring 1282. Ventilator 110 also can include one or more filters
1284 and/or nuts 1286. Filters 1284 can be inserted into an input
or output orifice of ventilator 10. For example, a filter 1284 can
be inserted into input valve 180 to filter out some or all
impurities in the fluid supplied to ventilator 110 through input
valve 180.
[0069] Panels 1210, 1220 and 1230 can be combined to form power
source door 250.
[0070] Subsets of plurality of screws 1240 are configured to
perform several functions. For example, screws 1240 can be used to:
(a) hold panels 1210, 1120 and 1230 together and to enclose power
source chamber 310, (b) hold ventilator halves 400, 500 together
using clips 1260, (c) hold solenoid 416 in place in one half of
ventilator housing 400, (d) connect knob 240 with protrusion 610
and/or (e) mount flow control device 434 to housing 400. As shown
in FIG. 12, different sizes and lengths of screws 1240 can be used
to achieve the various functions listed above, as well as other
functions. Additionally, one or more screws 1240 can be used in
combination with one or more nuts 1286 in order to provide a more
secure connection, as shown in FIG. 12.
[0071] Electrical contacts 1250 are each configured (or configured
to operate together) to permit power to be transferred from power
source 320 to wires 520. For example, electrical contacts 1250 can
be sections of an electrically-conductive material (such as a
metal) connected to poles of batteries as power source 320 and to
wires 520.
[0072] Various ones of the plurality of washers 1280 are configured
and placed to provide an improved seal around the components each
is placed around or against, as shown in FIG. 12, and/or to hold
one or more screws 1240 in place. Also as shown in FIG. 12, washers
1280 can be different sizes in order to accommodate different sized
components, openings or screws 1240 in ventilator 110.
[0073] O-ring 1282 is placed to create a partial or complete seal
around knob 240. By placing o-ring 1280 as shown in FIG. 12, o-ring
1282 can impede and/or prevent water or other fluids from entering
ventilator 110 near knob 240.
[0074] Screw cover 1212 is configured to be placed over screws 1240
that hold solenoid 416 in place. Cover 1212 can cover these screws
1240 for protection of screws 1240 from static discharge and/or
tampering, and for a more aesthetically pleasing appearance.
[0075] Regulator connector 1216 is configured to provide a fluid
communication path from regulator 414 to tube 426. Fitting 1214 is
another connector that is similar to connector 1216. Fitting 1214
comprises an elbow with a barb on one end and a thread on the other
end. Fitting 1214 can be identical to connector 1216 with a
different thread size. The barb includes an outlet such as a tube
or other opening in fitting 1214.
[0076] Decal 1218 is configured to provide visual reference marks
so a user can know which direction to rotate knob 240 and how far
to rotate knob 240 to obtain a desired flow rate through device
434. In other words, decal 1218 can include markings of flow rates
that correspond to an orifice 622 selected by rotating knob 240 to
a given position, as shown in FIGS. 1 and 2.
[0077] Anti-suffocation valve 1270 is a valve capable of opening to
allow outside atmosphere (for example, air) to patient 160 via
connection circuit 140. Valve 1270 can be configured so as to only
provide outside atmosphere to patient 166 if patient 160 attempts
to breathe on his or her own and ventilator 110 is off or otherwise
unable to deliver a breath to patient 160 at that time.
[0078] Valve 1290 is a valve capable of impeding or preventing a
buildup of pressure inside ventilator 110. For example, the fluid
provided to patient 160 by ventilator 110 can leak into the inside
of ventilator 110. When this occurs, the fluid pressure inside
ventilator 110 can buildup. In order to prevent this buildup of
pressure from damaging ventilator 110 or any components of
ventilator 110, valve 1290 can open when the fluid pressure exceeds
a predetermined threshold and permit the fluid inside ventilator
110 to escape to the surrounding atmosphere.
[0079] Ball and spring combination 435 includes a ball connected to
one end of a spring. Combination 435 is inserted in flow control
device 434 so that the ball of combination 435 sticks out of device
434. Knob 240 can include a plurality of indentations on the back
side of knob 240. These indentations are preferably located to
match up with each of a plurality of markings 242 on knob 240
(described in more detail below). By rotating knob 240, ball and
spring combination 435 push a ball against the indentations in knob
240. As the indentations pass by combination 435, a user who is
rotating knob 240 can feel and/or hear the ball as it is pressed in
each of the indentations. In addition, the ball and spring
combination 435 can hold knob 240 in place when it is rotated into
a desired position.
[0080] The function and location of the remaining components in
FIG. 12 are described below and/or shown in the attached
Figures.
[0081] FIG. 4 illustrates a view of inside ventilator 110 in
accordance with an embodiment of the presently described invention.
FIG. 4A illustrates a view of one half of ventilator 110 housing
400 and of the insides of ventilator device 110 in accordance with
an embodiment of the presently described invention. FIG. 4B
illustrates a view of the other half of ventilator 110 housing 500
and of the insides of ventilator device 110 in accordance with an
embodiment of the presently described invention.
[0082] Insides 400, 500 of ventilator device 110 include a pressure
regulator 414, a solenoid 416, a plurality of tubes (referred to as
first tube 418, second tube 422, third tube 424, fourth tube 426,
fifth tube 518, sixth tube 432 and seventh tube 415), a tube
connector 420, one or more solenoid 416 control wires 428, a flow
control device 434, one or more power source 320 wires 520, one or
more electrical circuits 514, holes 172, 512, a plurality of
sensors (referred to as first sensor 516 and second sensor 522),
and a plurality of clips 1260. Circuit(s) 514 is/are referred to as
circuit 514, regardless of whether circuit 514 comprises one or
more electrical circuits.
[0083] First sensor 516 can include a pressure switch configured to
close when the measured pressure falls within a particular range.
For example, first sensor 516 can include a pressure switch that
closes when the measured pressure is between 38 and 40 psi (262 and
275 kPa). First sensor 516 can be monitored for the low source
pressure alarm described above. In an embodiment, first sensor 516
can include a printed circuit board mount pressure and vacuum
switch, such as the switch manufactured by Presairtrol and
designated by part number CSPEGA-10PR(60 4).
[0084] Second sensor 522 can include a pressure sensor capable of
measuring a range of pressures and providing a voltage signal as
output. For example, sensor 522 can measure a range of pressures
from 0 to 60 cm H.sub.2O (0 to 5.9 kPa). In an embodiment, second
sensor 522 can include an integrated silicon pressure sensor, such
as the sensor manufactured by Freescale Semiconductor, Inc. with
the series number MPXV4006G.
[0085] As described above, a fluid source 120 is connected to
ventilator 110 via fluid source connection 130 and inlet valve
connection 180. Regulator 414 is connected to inlet valve 180.
Regulator 414 is also connected to solenoid 416 and fourth tube
426. Regulator 414 is connected to sensor 516 via tube 426.
[0086] Solenoid 416 is connected to regulator 414 using tube 415,
one or more wires 428 and first tube 418. Solenoid 416 is
electrically connected to circuit 514 via wire(s) 428. Solenoid 416
is connected to flow control device 434 via first tube 418,
connector 420, second tube 422 and third tube 424.
[0087] Connector 420 connects first tube 418 with second and third
tubes 422, 424. In an embodiment, connector 420 is a
Y-connector.
[0088] Flow control device 434 is connected to tidal volume control
knob 240, second tube 422, third tube 424, sixth tube 432 and
output valve 170. Flow control device 434 is connected to solenoid
416 via tubes 418, 422 and 424 and connector 420. Flow control
device 434 is connected to circuit 514 and sensor 516 via tube 432.
Flow control device 434 is also connected to patient 160 via output
valve 170, patient circuit connection 140 and delivery device
150.
[0089] FIG. 5A illustrates a perspective view of a back side and a
top of flow control device 434. FIG. 5B illustrates a perspective
view of a front side and a top of device 434. FIG. 5C illustrates a
plan view of a side of device 434. FIG. 5D illustrates a plan view
of the back side of device 434.
[0090] FIG. 6 illustrates a cross-sectional view of flow control
device 434 in accordance with an embodiment of the presently
described invention. Flow control device 434 includes a knob
connector 610, an orifice control tube 615, an orifice plate 620,
an orifice connection 625, a pressure relief plate 630, a spring
635, a pressure relief outlet port 640, a diaphragm valve 645, an
exhalation port 650, an input port 655 and an output port 660. An
interior of device 434 also includes a plurality of chambers and
tubes through which pressurized fluid can pass through. These
chambers and tubes include an entry chamber 665, a first tube 670,
a middle chamber 675, a second tube 680 and a third tube 685.
[0091] In an embodiment, orifice connection 625 is sealed by one or
more O-rings surrounding connection 625. These o-rings can prevent
or impede fluid from passing around, rather than through,
connection 625.
[0092] Knob connector 610 includes any object or protrusion capable
of interfacing with knob 240. For example, connector 610 can
include an object that fits inside of knob 240 so that rotating
knob 240 also causes connector 610 to rotate.
[0093] Knob connector 610 is connected to tube 615. Tube 615 is
also connected to orifice plate 620. In this way, tube 615 connects
knob connector 610 to orifice plate 620. By turning knob 240 when
it is connected to connector 610, connector 610, tube 615 and
orifice plate 620 also rotate. In an embodiment, a plurality of
connector 610, tube 615 and orifice plate 620 are integrally formed
of the same material. That is, a plurality of these components is
part of a single object and cannot be separated from one another
without damaging or destroying the object.
[0094] Input port 655 is in fluid communication with first chamber
665. By "fluid communication" or "fluidly connected," it is meant
that a fluid can pass from the components, chambers and/or tubes
that are so connected. Therefore, a fluid such as pressurized 02
can pass from input port 655 to first chamber 665. In an
embodiment, input port 655 is capable of being connected to tube
422. In this way, fluid traveling through tube 422 can enter into
first chamber 665.
[0095] First chamber 665 is in fluid communication with first tube
670 via orifice connection 625. Orifice connection 625 includes an
orifice selected by rotating orifice plate 620 to a given position.
As described in more detail below, orifice plate 620 includes a
plurality of orifices 622 having a plurality of different
diameters.
[0096] First tube 670 is in fluid communication with middle chamber
675. In an embodiment, device 434 includes a pressure relief
apparatus. The pressure relief apparatus includes pressure relief
plate 630, spring 635 and pressure relief outlet port 640. The
pressure relief apparatus acts to relieve a build up of pressure in
device 434. The pressure of the fluid traveling through device 434
can build up and push plate 630 against spring 635. If the fluid
pressure becomes large enough to overcome the force of spring 635
pushing plate 630 against the fluid pressure, plate 630 moves
towards outlet port 640. When outlet port 640 is moved far enough
so that the fluid in middle chamber 675 can travel out of outlet
port 640, the pressure in device 434 can decrease. The fluid
pressure in middle chamber 675 continues to decrease until the
force of spring 635 pushing plate 630 against the fluid pressure
overcomes the fluid pressure. At that point, plate 630 closes the
path of the fluid from middle chamber 675 to outlet port 640 and
the fluid travels from middle chamber 675 to second tube 680.
[0097] The fluid travels from second tube 680 to third tube 685 and
outlet port 660. Outlet port 660 is configured to connect to valve
170. The fluid can travel into outlet port 660, through valve 170
and into patient connection circuit 140.
[0098] FIG. 11 illustrates orifice plate. 620 in accordance with an
embodiment of the presently described invention. As shown in FIG.
11, orifice plate 620 includes a plurality of orifices 622 each
having a different diameter. As the diameter of each orifice 622
can affect the rate of fluid flow through orifice plate 620, by
changing which orifice 622 the fluid passes through device 434, the
rate of flow of the fluid delivered to patient 160 can be varied.
That is, by rotating plate 620 to each of a plurality of positions,
each of the plurality of orifices can be placed in a position to
provide a connection (or orifice connection 625) between chamber
665 and tube 670. As the diameter of the orifice used in connection
625 changes by a user rotating knob 240, the rate of flow of the
fluid passing through device 434 and ventilator 110 can be varied.
In an embodiment, orifice plate 620 can include one or more
locations on plate 620 where no orifices 622 exist. That is,
instead of having an orifice 622 in a location where one would
normally be located, plate 620 can be solid in that location. When
this location is lined up with orifice connection 625, flow of the
fluid through device 434 can be impeded or blocked.
[0099] In an embodiment of the presently described invention,
device 434 includes an outlet port 690 useful for measuring a
pressure of the fluid passing through device 434. As shown in FIG.
10A and FIG. 10B, outlet port 690 is in fluid communication with
tube 680. Fluid traveling through tube 680 can also pass through
outlet port 690. As described below, fluid traveling through outlet
port 690 passes into tube 432, which is configured to direct
sufficient fluid in device 434 and/or patient connection circuit
(or patient airway connection) 140 to sensor 522 so that sensor 522
can measure the fluid pressure in connection circuit 140 and/or
device 434.
[0100] As shown in FIGS. 4, 4A, 4B and 5, ports 650, 655 and 690
can be connected to tubes 424, 422 and 432, respectively. That is,
tube 424 can be placed onto port 650 to establish fluid
communication between port 650 and at least connector 420. Tube 422
can likewise be placed onto port 655 to establish fluid
communication between port 655 and at least connector 420. Tube 432
can also be placed onto port 690 to establish fluid communication
between port 690 and sensor 522. By making these connections, fluid
travel throughout ventilator 110. For example, fluid can exit
solenoid 416 and travel through tube 422. As tube 422 connects to
port 655, the fluid can enter device 434 via port 655.
[0101] In an embodiment, pressure relief outlet port 640 does not
connect to any tube or connector. Outlet port 640 can instead
direct fluid traveling through it into interior of ventilator 110
or outside of ventilator 110 via one or more holes or other
outlet(s) lined up with port 640.
[0102] Knob 240 and hole 512 are configured so that when the two
halves 400, 500 of ventilator 110 are combined together, or closed
together, to form ventilator 110 as shown in FIG. 1. Knob 240 can
be accessible through hole 512.
[0103] Valve 170 and hole 172 are configured so that when the two
halves 400, 500 of ventilator 110 are combined together, or closed
together, to form ventilator 110 as shown in FIG. 1. Valve 170 can
be accessible through hole 172.
[0104] Wires 520 connect one or more power sources 320 to circuit
514. Sensors 516, 522 are each connected to or a part of circuit
514. In an embodiment, circuit 514 is a printed circuit board
("PCB") housing one or more electrical circuits. Using a PCB for
circuit 514 makes the electrical components of ventilator 110 more
durable than existing ventilators that include non-PCB based
electrical components. In addition, the PCB can be sprayed or
otherwise coated with an epoxy to add further strength and
durability to circuit 514 and therefore ventilator 110.
[0105] In an embodiment, circuit 514 is capable of comparing one or
more measured quantities to one or more thresholds to determine if
any of the alarms described above need to be activated. For
example, circuit 514 is connected to power source 320 by wires 520.
From this connection, circuit 514 can obtain electrical power and
measure the voltage, current or time remaining in power source 320.
In an embodiment, circuit 514 can calculate the amount of time
remaining by comparing a remaining amount of voltage in power
source 320 and comparing this voltage to previous testing results.
The previous testing results can include tests on how long
ventilator 110 was able to run on a given amount of remaining
voltage. For example, during testing a given voltage remaining in
power source 320 can yield two hours of operation by ventilator
110. Circuit 514 can calculate the amount of time remaining by
comparing the existing amount of voltage in power source 320 and
comparing it to the minimum voltage required for two hours of
operation.
[0106] In another example, one or more of sensors 516, 522 can
determine or measure a fluid pressure and communicate the pressure
to circuit 514. Circuit 514 can then compare the pressure to one or
more thresholds (described above) and activate one or more
alarms.
[0107] In an embodiment, circuit 514 includes a voltage step up
circuit. The voltage step up circuit can increase the supplied
voltage to circuit 514 from power source 320. For example, circuit
514 can include a voltage step up circuit that increases a voltage
of 3.0 volts supplied by two size "D" alkaline batteries to 5.0
volts. The 5.0 volts can then be applied to selected electrical
components.
[0108] In addition, in an embodiment circuit 514 is in
communication with BPM buttons 218 and inspiratory buttons 216. For
example, electrical contacts or connections between circuit 514 and
buttons 216, 218 can provide such communication. Circuit 514 can
include programmable logic functionality that is capable of being
simply programmed by a user. For example, circuit 514 can include
one or more processors or microprocessors.
[0109] Circuit 514 can be capable of being controlled by a user
pushing buttons 216 and/or 218. As described in more detail below,
a user can increase and/or decrease the BPM administered to a
patient 160 using buttons 218. When either of buttons 218 is
depressed, circuit 514 changes the BPM, or frequency, of the fluid
supplied to patient 160. In an embodiment, circuit 514 is also
capable of illuminating or displaying the selected BPM in display
window 212.
[0110] A user can also control the inspiratory time administered by
ventilator 110 to patient 160 using inspiratory buttons 216. By
selecting one or the other of buttons 216, a user can select
whether a longer inspiratory time is required for an adult or
adult-sized patient 160 or a shorter inspiratory time is required
for a child or child-sized patient 160, for example. When a user
selects one of buttons 216, circuit 514 changes the inspiratory
time of the fluid administered to patient 160 by ventilator 110. In
addition, ventilator 110 can display the selected inspiratory time.
For example, circuit 514 can cause a light or LED next to one or
more of buttons 216 to become illuminated when that button 216 is
selected.
[0111] In operation, a fluid source 120 is connected to ventilator
110 as described above. Fluid source 120 is opened or otherwise
enabled to supply fluid, such as a pressurized gas, to ventilator
110 via inlet valve 180. Once the fluid enters ventilator 110, the
fluid is directed to regulator 414. Regulator 414 regulates the
input fluid pressure for ventilator 110. In an embodiment,
regulator 414 decreases the pressure of the input fluid. For
example, regulator 414 can step down the input fluid pressure to 40
psi (275 kPa). In addition, regulator 414 can serve to provide a
more uniform pressure to orifice plate 622. By providing a more
uniform pressure on orifice plate 622, the rate of fluid flow
through ventilator 110 can be more consistent if the pressure of
the fluid supplied by source 120 varies.
[0112] A portion of the fluid passes from regulator 414 to sensor
516. In an embodiment, sensor 516 measures or otherwise determines
the pressure of the fluid input to ventilator 110. Sensor 516 can
measure this pressure to determine if pressure of the fluid
supplied by source 120 falls below the source pressure threshold
described above. In an embodiment, sensor 516 is powered by power
source 320. If the pressure does fall below this threshold, sensor
516 can communicate this event with circuit 514, which can then
activate an alarm. For example, the light next to the "low source
gas alarm" on alarm panel 220 can be illuminated if the pressure of
the source fluid drops below 40 psi (275 kPa).
[0113] A portion of the fluid also passes from regulator 414 to
solenoid 416. Solenoid 416 acts as a valve that is capable of
stopping or allowing the flow of the fluid to pass through
ventilator 110. For example, solenoid 416 includes a piston capable
of moving between as least two positions. In an embodiment, one
position of the piston permits the fluid to pass through solenoid
416 and on through tube 418 while another position of the piston
impedes this fluid flow or stops the flow completely.
[0114] FIGS. 7 and 8 illustrate schematic diagrams of solenoid 416
in accordance with an embodiment of the presently described
invention. FIGS. 7 and 8 illustrate simplified views of one
embodiment of the operation of solenoid 416. Other manners of
operation of solenoid 416 that achieve the same start/stop
functionality (with respect to the flow of the fluid through
ventilator 110) are also within the scope of embodiments of the
presently described invention.
[0115] Solenoid 416 includes a piston 610, a fluid flow path 620
and a piston travel path 630. In an embodiment, piston 610 is
capable of moving between a first position (shown in FIG. 7 and
referred to as an "open" position) and a second position (shown in
FIG. 8 and referred to as a "closed" position). Piston 610 can be
moved between first and second positions using a voltage difference
supplied by power source 320 and/or circuitry 514. In an
embodiment, a 1.5 volt differential moves piston 610 between first
and second, or open and closed, positions. The voltage
differential, and therefore control of solenoid 416, can be
provided via wire 418 connected to circuitry 514.
[0116] While piston 610 is in the open position, fluid is delivered
to a patient 160 from ventilator 110. The fluid passes through
solenoid 416 via the fluid flow path 620 with piston 610 being
generally out of flow path 620.
[0117] When piston 610 is in the closed position, fluid is not
being delivered to patient 160 or the fluid flow is greatly
impeded. That is, fluid flow path 620 is partially to completely
blocked by piston 610. In other words, while the closed position
may not completely block the flow of all fluid from source 120 to
patient 160, the closed position causes solenoid 416 to prevent a
majority of fluid flow from reaching patient 160. In an embodiment,
all fluid flow through path 620 is blocked by solenoid 416 when it
is in the closed position. In such an embodiment, solenoid 416
includes a barb 436, as shown in FIGS. 4 and 4A. Barb 436 is an
outlet such as a tube or other opening in solenoid 416. Barb 436
provides an outlet port that can vent the pressure in connection
140 and permit delivery device 150 to open and permit patient 160
to exhale.
[0118] In an embodiment, piston 610 is capable of only being in the
open or closed position. That is, piston 610 is incapable of being
halfway between the open and closed positions. In such an
embodiment, solenoid 416 is only capable of permitting or
blocking/impeding fluid flow through ventilator 110. In other
words, solenoid 416 cannot be at a position other than the open or
closed position.
[0119] Once fluid passes through solenoid 416 (assuming solenoid
416 is in an open position), the fluid travels through tube 418 to
connector 420. Once fluid reaches connector 420, the fluid passes
through connector 420 into tubes 422 and 424. From tubes 422, 424,
the fluid travels into flow control device 434. In doing so, the
path of the fluid travels first through solenoid 416 and then
through flow control device 434. In other words, solenoid 416 is
"upstream" from flow control device 434 and flow control device 434
is "downstream" from solenoid 416.
[0120] Solenoid 416 and flow control device 434 can operate
together to make it easier for patient 160 to exhale. FIG. 13
illustrates a cross-section view of flow control device 434 in
accordance with an embodiment of the presently described invention.
Device 434 as illustrate in FIG. 13 is similar to the embodiment
illustrated in FIGS. 5 and 6. One difference is that device 434 in
FIG. 13 includes a hole 647 connecting a chamber surrounding
diaphragm valve 645 with the atmosphere surrounding flow control
device 434. Hole 647 can assist in opening and/or closing diaphragm
valve 645. In combination, hole 647 and diaphragm valve 645 can
work together to vent patient connection circuit 140 and thus make
it easier for patient 160 to exhale.
[0121] In operation, when solenoid 416 is in the open position,
fluid flows from solenoid 416 into ports 650 and 655. As fluid
flows into port 650, the fluid pushes diaphragm valve 645 to close.
When diaphragm valve 645 is closed, fluid cannot pass or is impeded
from passing from port 650 to tube 685 and hole 647. Instead, fluid
passes from tube 685 into outlet port 660 and then into patient
connection circuit 140. As fluid passes into connection circuit
140, one-way valve 157 remains open so that the fluid can be
provided to patient 160 via patient connection circuit 140 and
delivery device 150.
[0122] When solenoid 416 is in the closed position, fluid flows out
of barb 436 of solenoid 416 and does not pass into port 650. When
fluid does not flow into port 650, the fluid pressure forcing
diaphragm valve 645 closed decreases or no longer exists. If the
fluid pressure forcing diaphragm valve 645 drops to a sufficiently
low level, diaphragm valve 645 opens. Once diaphragm valve 645
opens, hole 647 can provide a path of fluid communication between
the atmosphere surrounding flow control device 434 and tube 685
(and therefore output port 660 and patient connection circuit 140,
as each of tube 685, port 660 and circuit 140 are connected). The
fluid pressure in patient connection circuit 140 is then vented
through outlet port 660, tube 685 and hole 647 into the atmosphere
surrounding flow control device 434. Once the fluid pressure in
patient connection circuit 140 decreases a sufficient amount,
one-way valve 157 closes. When valve 157 closes, patient 160 can
exhale through exhalation port 155.
[0123] In an embodiment, tube 432 is in communication with patient
connection circuit 140 via flow control device 434. Tube 432 is
also connected to sensor 522. Tube 432 is configured to direct
sufficient fluid in patient connection circuit (or patient airway
connection) 140 and/or in device 434 to sensor 522 so that sensor
522 can measure the corresponding fluid pressure. Once sensor 522
measures or otherwise determines the fluid pressure, circuit 514
can compare this pressure to a threshold, such as the upper airway
pressure threshold and/or the lower airway pressure threshold
described above. If the fluid pressure in connection circuit or
airway connection 140 exceeds the upper airway pressure threshold,
for example, circuit 514 activates one or more alarms, as described
above. If the fluid pressure in airway connection 140 is lower than
the lower airway pressure threshold, for example, circuit 514
activates one or more alarms, also as described above. In an
embodiment, an alarm includes illuminating the light next to the
text "HIGH AIRWAY PRESSURE ALARM" on alarm control panel 220.
[0124] In addition, circuit 514 can cause the fluid pressure in
airway connection 140 to be displayed to a user in window 214 of
ventilator 110.
[0125] In an embodiment, a timing control device of ventilator
includes solenoid 416, at least a functional portion of circuit 514
and power source 320. By "functional portion," it is meant that the
part(s) or portion(s) of circuit 514 that controls whether solenoid
416 is in an open or closed position is the functional portion of
the timing control device.
[0126] The timing control device controls the frequency (or BPM)
and duration (or inspiratory time) of breaths administered by
ventilator 110 using an electrical power source 320 and solenoid
416. In this manner, the timing control for ventilator 110 is
electronically controlled. The functional portion of circuit 514
related to the timing control device determines, based on user
input, the selected BPM and/or inspiratory time to be used in
supplying the fluid to patient 160. As described above, this user
input can be a user pushing BPM buttons 218 and/or inspiratory
buttons 216.
[0127] Based on the BPM and/or inspiratory time selected by the
user, circuit 514 determines the rate, or frequency, at which
solenoid 416 should switch between open and closed positions. As
described above, when solenoid 416 is in an open position, fluid is
being delivered to patient 160. Conversely, when solenoid 416 is in
a closed position, fluid is not being delivered to patient 160.
Circuit 514 can control whether solenoid 416 is in an open or
closed position by varying a voltage differential across solenoid
416. For example, by varying the voltage supplied to solenoid 416
using wire(s) 428 by 1.5 volts, circuit 514 can cause solenoid 416
to change between open and closed positions.
[0128] For example, if a BPM of ten is selected by a user
(indicating ten breaths per minute), then circuit 514 can determine
that solenoid 416 should open and close once every six seconds to
cause ventilator 110 to deliver ten breaths in a minute. If a BPM
of thirty is selected, circuit 514 can determine that solenoid 416
should open and close once every two seconds to cause ventilator
110 to deliver thirty breaths in a minute, for example. If a BPM of
five is selected, circuit 514 can determine that solenoid 416
should open and close once every twelve seconds to cause ventilator
110 to deliver five breaths in a minute, for example.
[0129] In another set of examples, if an inspiratory time of one
second is selected by a user (indicating that the inspiratory time,
or fluid delivery time, should last for one second), then circuit
514 can determine that solenoid 416 should open and remain open for
one second before closing at each breath delivered by ventilator
110. If an inspiratory time of two seconds is selected, circuit 514
can determine that solenoid 416 should open and remain open for two
seconds before closing at each breath delivered by ventilator 110,
for example.
[0130] Thus, circuit 514 can electrically control solenoid 416 to
vary the frequency and duration of breaths supplied to patient 160
by ventilator. For example, with a BPM of ten and an inspiratory
time of two seconds selected, circuit 514 can cause solenoid 416 to
open and close ten times per minute and remain in an open position
each time it opens for two seconds. By providing electronic control
of the timing of breaths provided by ventilator 110, the timing
control device of ventilator 110 provides a more accurate and
precise manner of controlling the BPM and inspiratory time. As the
timing control device does not rely on source 120 fluid pressure to
operate (as some existing ventilators do), but instead rely on
relatively long-lasting power source(s) 230, the timing control
device has a greater accuracy and precision as long as an adequate
power source 230 remains. That is, as the pressure of a source 120
fluid can vary to a greater extent than the voltage supplied by
alkaline battery power sources 230, for example, ventilators that
rely on source fluid pressure can experience greater fluctuations
in their breath timing control (such as BPM and inspiratory time)
than ventilator 110.
[0131] Another component of ventilator 110 is flow control device
434. Flow control device 434 enables a user to control and vary the
rate at which the fluid is supplied to a patient 160 during the
inspiratory time (or time at which solenoid 416 is in an open
position). As described above, flow control device 434 controls the
rate at which the fluid is delivered to a patient 160 using a
plurality of orifices of different diameters. A user selects which
orifice is to be used by turning knob 240 to a desired tidal volume
(as shown in FIGS. 1 and 2). Markings on an outside surface of
ventilator 110 can indicate which orifice is selected. A marking
242 on knob 240 can be employed by a user to select the desired
orifice and tidal volume. In general, selecting a larger tidal
volume causes a greater rate of fluid flow through flow control
device 434 and to patient 160.
[0132] As described above, flow control device 434 does not rely on
any electricity, electric power source or electrical circuits.
Thus, device 434 does not rely on, and is not controlled or
otherwise dependent upon power source 230 and circuit 514. As a
result, device 434 is essentially a pneumatic flow control of
ventilator 110, and is generally more robust and durable than
electrically controlled flow controls in existing ventilators.
[0133] Using flow control device and the timing control device, a
user can very accurately and precisely control the volume of fluid
delivered to a patient by ventilator 110. That is, the user can
control the BPM and inspiratory time that a selected rate of fluid
is provided to a patient 160. As a result, the separate timing
control device and flow control devices of ventilator 110 permit a
user to electronically control a time period at which a selected
rate of fluid flow is provided to patient 160.
[0134] As described above, ventilator 110 includes a timing control
device that operates off a low voltage power circuit. This timing
control device can be powered by relatively longer lasting, light,
small, inexpensive and readily available alkaline batteries, for
example. This improves over existing ventilators that rely on
relatively heavy, large and expensive lead acid batteries that have
a relatively shorter life and are relatively difficult to find
(especially in emergency situations). This design of ventilator 110
can reduce its overall weight compared to existing ventilators and
can increase the operating time of ventilator 110 over existing
ventilators.
[0135] Moreover, by separating the timing control device and flow
control device 434 into separately controlled devices operated
electrically and pneumatically, respectively, ventilator 110 can
provide increased accuracy and precision in BPM and inspiratory
times for fluids provided to patients 160. Existing ventilators may
include all pneumatic systems to control fluid flow and timing.
Such ventilators typically include complex pneumatic systems that
rely on the build up of source fluid pressure as a timing function
(or as a timing control device). But, small leaks and slight
variations common in these ventilators can affect the performance,
accuracy and precision of the ventilators.
[0136] In addition, some existing ventilators are entirely
electronically controlled. Such ventilators use electronic circuits
to control the timing and to control and drive a complex
proportioning valve to establish flow control of fluid through the
ventilator. Such ventilators typically require more power or
voltage than embodiments of ventilator 110. In addition, these
ventilators typically require additional hardware such as position
feedback circuits to obtain improved accuracy in their timing.
[0137] FIG. 9 illustrates a flowchart of a method 900 for using an
improved ventilator 110 in accordance with an embodiment of the
presently described invention. Method 900 begins at step 905, where
a fluid source is connected to the ventilator. For example, a
source 120 can be connected to ventilator 110 as described
above.
[0138] Next, at step 910 a patient airway connection is connected
to the ventilator and to a patient. For example, patient airway
connection 140 can be connected to ventilator 110 and patient 160
as described above.
[0139] Next, at step 915, a BPM, inspiratory time and rate of fluid
flow are selected. For example, a user can select a desired BPM and
inspiratory time using buttons 216, 218 and can select a rate of
fluid flow by turning knob 240 to a desired tidal volume, as
described above.
[0140] Next, at step 920, the fluid flows from the fluid source
into a timing control device of the ventilator. For example, the
fluid can flow from source 120 into solenoid 416, as described
above. In an embodiment, the fluid can flow into a pressure
regulator, such as regulator 414, prior to flowing into the timing
control device.
[0141] Next, at step 925, method 900 proceeds to either step 930 or
step 935 depending on whether the timing control device is open or
in an opened state. If the timing control device is open, then
method 900 proceeds from step 925 to step 935. If the timing
control device is closed, then method 900 proceeds from step 925 to
step 930. For example, if solenoid 416 is in an open state or
position, method 900 can proceed from step 925 to step 935. If
solenoid 416 is in a closed state or position, method 900 can
proceed from step 925 to step 930.
[0142] At step 930, the fluid does not pass through the timing
control device. That is, the timing control device blocks or at
least impedes a majority of the fluid flow through the timing
control device. For example, solenoid 416 can block or impede the
flow of the fluid through solenoid 416. Method 900 proceeds from
step 930 back to step 925, where it is determined whether the
timing control device is open. In doing so, method 900 proceeds in
a loop including steps 925 and 930 until the timing control device
is in an open position or state.
[0143] At step 935, the fluid passes through the timing control
device and into the flow control device. For example, as described
above, the fluid can pass into flow control device 434 after
passing through an open solenoid 416.
[0144] Next, at step 940, the flow control device varies the rate
of fluid flow. That is, the flow control device can increase or
decrease the rate of fluid flow. In an example, flow control device
434 includes a plurality of orifices having different diameters.
Flow control device 434 can direct the flow of fluid through one or
more of these orifices to change the rate of fluid flow, as
described above.
[0145] Next, at step 945, the fluid is supplied to a patent. For
example, the fluid can be supplied to a patient 160 after passing
through flow control device 434 via a patient airway connection
140.
[0146] While particular elements, embodiments and applications of
the presently described invention have been shown and described, it
is understood that the presently described invention is not limited
thereto since modifications may be made by those skilled in the
technology, particularly in light of the foregoing teaching. It is
therefore contemplated by the appended claims to cover such
modifications and incorporate those features that come within the
spirit and scope of the presently described invention
* * * * *